CN114916908A - Tissue component measuring method and device based on Raman spectrum and wearable equipment - Google Patents

Abstract

Embodiments of the present disclosure provide a Raman spectroscopy-based tissue composition measurement method, device, and wearable device. The method includes: irradiating a measurement area with incident light of a first preset wavelength, and the incident light of the first preset wavelength passes through the measurement area and then exits from an exit position to form at least one beam of Raman scattered light of a second preset wavelength, wherein, The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift; the Raman intensity corresponding to each Raman scattered light collected by the measurement probe is acquired, wherein a measurement The tissue component measuring device of the probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in tissue component concentration; the concentration of the measured tissue component is determined according to at least one Raman intensity corresponding to the second preset wavelength.

Description

Tissue composition measurement method, device and wearable device based on Raman spectroscopy

technical field

The present disclosure relates to the technical field of spectral measurement, and more particularly, to a Raman spectroscopy-based tissue composition measurement method, device, and wearable device.

Background technique

Since the energy change of photons in Raman scattering usually originates from the superposition of molecular vibrational energy and incident photon energy, the Raman scattered light contains abundant information of molecular vibrational structure. Since the spectral characteristics of Raman spectra of different molecules are different, they can be used as fingerprint spectra for molecular identification. Raman spectroscopy can determine the composition of different substances according to the difference in intermolecular vibrational frequencies, which makes it possible to measure tissue composition based on Raman spectroscopy. In addition, Raman spectroscopy is considered to be one of the most promising techniques for tissue composition measurement due to the advantages of clear and sharp characteristic peaks, not easy to overlap, and weak Raman intensity of water. Among them, tissue components may include blood sugar, hemoglobin, fat, and protein.

In the process of realizing the concept of the present disclosure, the inventors found that there are at least the following problems in the related art: it is difficult to obtain the real measured tissue component signal by using the related art.

SUMMARY OF THE INVENTION

In view of this, embodiments of the present disclosure provide a Raman spectroscopy-based tissue composition measurement method, device, and wearable device.

An aspect of the embodiments of the present disclosure provides a method for measuring tissue components based on Raman spectroscopy, the method comprising: irradiating a measurement area with incident light of a first preset wavelength, and the incident light of the first preset wavelength passes the above measurement After the region, at least one beam of Raman scattered light with a second preset wavelength is emitted from the exit position, wherein the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift Obtaining the Raman intensity corresponding to each beam of the Raman scattered light collected by the measuring probe, wherein the tissue component measuring device provided with the measuring probe has a signal-to-noise ratio level that satisfies the resolution of the expected tissue component concentration change; and, according to The concentration of the measured tissue component is determined by at least one Raman intensity corresponding to the second preset wavelength.

Another aspect of the embodiments of the present disclosure provides a Raman spectroscopy-based tissue composition measurement device, the device includes: a light source module configured to illuminate a measurement region with incident light of a first preset wavelength, the first preset wavelength The incident light passes through the measurement area and exits from the exit position to form at least one beam of Raman scattered light with a second preset wavelength, wherein the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset wavelength. Let the Raman displacement be determined; the acquisition module is used to acquire the Raman intensity corresponding to each beam of the Raman scattered light collected by the measurement probe, wherein the tissue composition measurement device provided with the above measurement probe has the ability to meet the requirements for resolving the expected tissue composition a signal-to-noise ratio level of the concentration change; and a processing module, configured to determine the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

Another aspect of the embodiments of the present disclosure provides a wearable device including the Raman spectroscopy-based tissue composition measurement device as described above.

According to an embodiment of the present disclosure, by irradiating the measurement area with incident light of the first preset wavelength, the incident light of the first preset wavelength passes through the measurement area and then exits from the exit position to form at least one beam of Raman scattering of the second preset wavelength For light, the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift, and the Raman intensity corresponding to each Raman scattered light collected by the measurement probe is obtained, and a measurement The tissue component measurement device of the probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in tissue component concentration, and determines the measured tissue component concentration according to at least one Raman intensity corresponding to the second preset wavelength. Since the adopted tissue composition measuring device provided with a measuring probe has a signal-to-noise ratio level that can distinguish the expected tissue composition concentration change, the ability to perceive the expected tissue composition concentration change is realized, thereby improving the acquisition of the real measured tissue composition. signal possibilities.

Description of drawings

The above and other objects, features and advantages of the present disclosure will become more apparent from the following description of embodiments of the present disclosure with reference to the accompanying drawings, in which:

FIG. 1 schematically shows a flowchart of a method for measuring tissue composition based on Raman scattering according to an embodiment of the present disclosure;

FIG. 2 schematically shows a schematic diagram of using a photosensitive surface with a small area to receive Raman scattered light when jitter occurs according to an embodiment of the present disclosure;

FIG. 3 schematically shows a schematic diagram of using a larger-area photosensitive surface to receive Raman scattered light when jitter occurs according to an embodiment of the present disclosure;

FIG. 4 is a schematic diagram of a measurement result obtained by a Monte Carlo simulation method according to an embodiment of the present disclosure;

FIG. 5 schematically shows a schematic diagram of a differential measurement according to an embodiment of the present disclosure;

FIG. 6 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure;

FIG. 7 schematically shows another schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure;

FIG. 8 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an image matching method according to an embodiment of the present disclosure;

FIG. 9 schematically shows a schematic diagram of realizing the positioning of the measurement area based on another image matching method according to an embodiment of the present disclosure;

FIG. 10 schematically shows a schematic diagram of realizing the positioning of the measurement area by an imaging method according to an embodiment of the present disclosure;

FIG. 11 schematically shows a schematic diagram of implementing positioning of a measurement area based on another imaging method according to an embodiment of the present disclosure;

FIG. 12 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure;

FIG. 13 schematically shows a schematic diagram of realizing the positioning of the measurement posture by an image matching method according to an embodiment of the present disclosure;

FIG. 14 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an imaging method according to an embodiment of the present disclosure;

15 schematically shows a schematic diagram of setting a mask plate on an initial photosensitive surface to obtain a photosensitive surface according to an embodiment of the present disclosure;

16 schematically shows a block diagram of a Raman scattering-based tissue composition measurement device according to an embodiment of the present disclosure;

FIG. 17 schematically shows a schematic diagram of a diffusion measurement according to an embodiment of the present disclosure;

FIG. 18 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a glove according to an embodiment of the present disclosure;

FIG. 19 schematically shows a schematic diagram of another stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure;

20 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a wristband according to an embodiment of the present disclosure;

FIG. 21 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of another wristband according to an embodiment of the present disclosure;

FIG. 22 schematically shows a schematic diagram of a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure;

FIG. 23 schematically shows a schematic diagram of anode electrical connection of different photosensitive surfaces according to an embodiment of the present disclosure;

FIG. 24 schematically shows a schematic diagram of the positional relationship between a fixing part and a measuring probe according to an embodiment of the present disclosure;

FIG. 25 schematically shows a schematic structural diagram of a fixing part according to an embodiment of the present disclosure;

Fig. 26 schematically shows a schematic diagram of a first fitting according to an embodiment of the present disclosure;

FIG. 27 schematically shows a schematic diagram of another first fitting according to an embodiment of the present disclosure;

Fig. 28 schematically shows a schematic diagram of a region positioning part according to an embodiment of the present disclosure;

FIG. 29 schematically shows a schematic diagram of another area positioning part according to an embodiment of the present disclosure;

FIG. 30 schematically shows a schematic diagram of a first image acquisition part according to an embodiment of the present disclosure;

FIG. 31 schematically shows a schematic diagram of a first posture positioning part according to an embodiment of the present disclosure;

FIG. 32 schematically shows a schematic diagram of a third image acquisition part according to an embodiment of the present disclosure;

Fig. 33 schematically shows a schematic diagram of a measurement posture and measurement area positioning according to an embodiment of the present disclosure;

FIG. 34 schematically shows another schematic diagram of measurement posture and measurement area positioning according to an embodiment of the present disclosure;

FIG. 35 schematically shows a schematic diagram of setting a first sleeve on a measuring probe according to an embodiment of the present disclosure;

36 schematically shows a schematic diagram of disposing a second sleeve outside the target area of a first sleeve according to an embodiment of the present disclosure;

FIG. 37 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light without filling with an index matching material according to an embodiment of the present disclosure;

FIG. 38 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light under the condition of filling with an index matching material according to an embodiment of the present disclosure;

FIG. 39 schematically shows another schematic diagram of the photosensitive surface receiving outgoing light under the condition of filling with an index matching material according to an embodiment of the present disclosure;

FIG. 40 schematically shows a schematic diagram of a wearable device according to an embodiment of the present disclosure;

FIG. 41 schematically shows a schematic diagram of an assembling process of a wearable device according to an embodiment of the present disclosure;

Fig. 42 schematically shows a method according to an embodiment of the present disclosure, under the condition that the wearable device is consistent with the skin shaking law, the average optical length of the outgoing light received by the measurement probe is kept at a preset optical length during the skin shaking process a schematic diagram of the scope; and

FIG. 43 schematically shows the average optical path length of the outgoing light received by the measurement probe in the case where the wearable device makes the movement amplitude of the skin at the measurement area less than or equal to the movement amplitude threshold value in the skin jitter according to an embodiment of the present disclosure. Schematic diagram of staying within the preset optical path range during the process.

Detailed ways

Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. It should be understood, however, that these descriptions are exemplary only, and are not intended to limit the scope of the present disclosure. In the following detailed description, for convenience of explanation, numerous specific details are set forth in order to provide a thorough understanding of the embodiments of the present disclosure. It will be apparent, however, that one or more embodiments may be practiced without these specific details. Also, in the following description, descriptions of well-known structures and techniques are omitted to avoid unnecessarily obscuring the concepts of the present disclosure.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the present disclosure. The terms "comprising", "comprising" and the like as used herein indicate the presence of stated features, steps, operations and/or components, but do not preclude the presence or addition of one or more other features, steps, operations or components.

All terms (including technical and scientific terms) used herein have the meaning as commonly understood by one of ordinary skill in the art, unless otherwise defined. It should be noted that terms used herein should be construed to have meanings consistent with the context of the present specification and should not be construed in an idealized or overly rigid manner.

Where expressions like "in A, B, and C, etc.," are used, they should generally be interpreted in accordance with the meaning of the expressions commonly understood by those skilled in the art (for example, "with the "System" shall include, but is not limited to, systems with A alone, B alone, C alone, A and B, A and C, B and C, and/or A, B, C, etc.). Where expressions like "in A, B, or C, etc.," are used, they should generally be interpreted according to the meaning of the expression as commonly understood by those skilled in the art (for example, "with A, B, or C in "System" shall include, but is not limited to, systems with A alone, B alone, C alone, A and B, A and C, B and C, and/or A, B, C, etc.).

When the incident light strikes the measured object, the measured object causes two types of scattering of the incident light, namely Rayleigh scattering and Raman scattering. Among them, Rayleigh scattering only changes the transmission direction of the incident light, but does not change the frequency of the incident light. Raman scattering not only changes the transmission direction of the incident light, but also changes the frequency of the Raman scattered light. The difference between the frequency of the Raman scattered light and the frequency of the incident light is called the Raman shift. Raman shift has nothing to do with the frequency of incident light, it is only related to the molecular structure of the measured tissue component itself, depending on the change of molecular vibrational energy level, different chemical bonds or groups in the molecule have molecular vibrations with different characteristics, which is the Mann spectroscopy can be used as a basis for analyzing different tissue components.

Since the absorption of the measured tissue component itself is usually weak, and the variation range of the measured tissue component concentration of the measured object itself is usually not large, the measured tissue component signal is usually weak. And the change of measurement conditions will easily drown the weak signal of the measured tissue composition. In addition, the intensity of the Raman scattered light of the measured tissue components that can be collected is also very weak, where the intensity of the Raman scattered light can be called Raman intensity. The measured tissue component signal represents the Raman intensity change caused by the concentration change of the measured tissue component.

In the process of realizing the concept of the present disclosure, the inventors found that the main reason why the related art does not achieve reliable Raman scattering-based tissue composition measurement is that.

First, the importance of directly obtaining the real measured tissue composition signal is not recognized, and it is not recognized as a prerequisite for non-invasive measurement of living tissue composition.

In the second aspect, no effective solution has been found to directly obtain the real measured tissue composition signal. Since it is a difficult problem to directly obtain the real measured tissue composition signal, even if the above-mentioned problems are recognized, no effective solution has been found to solve the above-mentioned problems.

The third aspect is over-confidence in the reliability of multivariate analysis methods. Since tissue components (such as hemoglobin, water, glucose, etc.) and physical states (such as temperature and pressure, etc.) have characteristic absorptions in preset frequency bands, multivariate analysis methods are generally considered to be potential tools for interference correction in in vivo tissue composition measurements , such as using multivariate analysis method to process multi-wavelength spectral data, that is, to establish a mathematical model between the optical signal and the true value of the measured tissue component concentration through multivariate analysis method, and use the established mathematical model to predict the measured tissue component concentration, Thus, the measured tissue component signal can be obtained indirectly. Wherein, the preset wavelength band may include visible-near infrared wavelength band.

Given the above-mentioned properties of multivariate analysis methods, some researchers have overconfidence in the reliability of multivariate analysis methods. However, since the signal changes caused by changes in measurement conditions are usually much larger than those caused by changes in the concentration of the measured tissue components, the measurement results obtained by the multivariate analysis method are likely to interfere with components other than the measured tissue components (such as physiological There is an accidental correlation between the signal changes caused by background interference), and the result obtained by this indirect method of extracting the signal of the measured tissue component may be a pseudo-correlation result.

In order to solve the above problems, the inventor believes that the primary condition for obtaining the real measured tissue component signal is that the measuring device for realizing the tissue component has the ability to sense the change of the expected tissue component concentration. Among them, the expected change in tissue component concentration can be understood as the limit measurement accuracy. The ultimate measurement accuracy can be understood as when the amount of light energy change (that is, the measurement value) caused by the change in the concentration of the measured tissue component is equivalent to the noise level of the instrument, the measurement value is difficult to extract from the noise, the smallest perceivable measured value. The change in tissue component concentration is called the limit measurement accuracy, and the device used for tissue component measurement is called a tissue component measurement device.

In order to realize the ability of the tissue composition measuring device to perceive the expected changes in the concentration of the tissue components, the inventor proposes a solution for measuring the tissue components using a tissue composition measuring device with a signal-to-noise ratio level that distinguishes the expected changes in the concentration of the tissue components. Among them, to realize that the tissue component measuring device has a signal-to-noise ratio level that can distinguish the concentration change of the expected tissue component, a method by improving the efficiency of Raman scattered light can be adopted. The following will be described with reference to specific embodiments.

FIG. 1 schematically shows a flow chart of a method for measuring tissue composition based on Raman scattering according to an embodiment of the present disclosure.

As shown in FIG. 1 , the method includes operations S110 to S130.

In operation S110, the measurement area is irradiated with the incident light of the first preset wavelength, and the incident light of the first preset wavelength passes through the measurement area and is emitted from the exit position to form at least one beam of Raman scattered light of the second preset wavelength, wherein, The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift.

According to an embodiment of the present disclosure, since different measurement sites have different skin properties, they may include smoothness, hair or not, flat state, skin thickness and softness, and the like. Therefore, it is necessary to select an appropriate measurement site according to the actual situation, such as the structure of the measurement probe. The measurement site may include at least one of fingers, palms, arms, foreheads, and earlobes. The measurement area may be an area on the measurement site.

When the measurement area is irradiated with the incident light of the first preset wavelength, Raman scattered light of the second preset wavelength will be generated, and the wavelength difference between the first preset wavelength and the second preset wavelength is the preset Raman shift It is determined that the preset Raman shift is determined according to the specific frequency shift of the incident light of the first preset wavelength for the measured tissue component.

According to an embodiment of the present disclosure, the second preset wavelength may be a wavelength sensitive to the measured tissue composition. The band to which the second preset wavelength belongs may include an ultraviolet band, a visible light band, a near-infrared band, a mid-infrared band, or a far-infrared band.

In operation S120, the Raman intensity corresponding to each Raman scattered light collected by the measurement probe is acquired, wherein the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that satisfies the resolution of expected tissue component concentration changes.

According to the embodiments of the present disclosure, the expected changes in the concentration of tissue components may be set according to actual conditions. A tissue component measurement device provided with a measurement probe having a signal-to-noise ratio level that resolves expected changes in tissue component concentration can be achieved as follows. The total area of the photosensitive surfaces of the same type set on the measuring probe is relatively large, and the area of each photosensitive surface of the same photosensitive surface is continuous, so that the efficiency of receiving Raman scattered light is improved.

In operation S130, the concentration of the measured tissue component is determined according to at least one Raman intensity corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, at least one Raman intensity corresponding to the second preset wavelength may be processed using an interference suppression method to determine the concentration of the measured tissue component. The interference suppression method may include a differential measurement method, and the differential measurement method may include a time differential measurement method or a position differential measurement method. Alternatively, at least one Raman intensity can also be processed using a non-differential measurement method to determine the concentration of the measured tissue component.

According to the technical solutions of the embodiments of the present disclosure, by irradiating the measurement area with the incident light of the first preset wavelength, the incident light of the first preset wavelength passes through the measurement area and then exits from the exit position to form at least one beam of the second preset wavelength. For the Raman scattered light, the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift, and the Raman intensity corresponding to each Raman scattered light collected by the measuring probe is obtained, and set The tissue component measuring device with the measuring probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in the concentration of the tissue component, and determines the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength. Since the adopted tissue composition measuring device provided with a measuring probe has a signal-to-noise ratio level that can distinguish the expected tissue composition concentration change, the ability to perceive the expected tissue composition concentration change is realized, thereby improving the acquisition of the real measured tissue composition. signal possibilities.

According to an embodiment of the present disclosure, acquiring the Raman intensity corresponding to each Raman scattered light collected by the measurement probe may include the following operations.

With the fluorescence interference shielded, the Raman intensity corresponding to each Raman scattered light collected by the measurement probe is acquired.

According to an embodiment of the present disclosure, if the object to be measured has a fluorescence effect, the incident light will generate fluorescence while generating Raman scattered light, and the fluorescence will adversely affect the measurement result.

In order to reduce the adverse effect of fluorescence on the measurement results, the method of shielding fluorescence interference can be used to shield the fluorescence. In the case of shielding the fluorescence interference, the Raman intensity corresponding to the Raman scattered light collected by the measurement probe is obtained. Methods for shielding fluorescence interference can include baseline correction methods based on mathematical algorithms, selection of appropriate preset wavelengths, surface-enhanced Raman spectroscopy, dual-wavelength excitation frequency-shifting methods, and time-gating-based methods.

According to an embodiment of the present disclosure, the method may further include the following operations.

Fluorescence interference is shielded based on a time-gated method.

According to the embodiments of the present disclosure, since the fluorescence is generated later than the Raman scattered light, a gating signal can be used to collect the Raman scattered light while shielding the fluorescence.

According to an embodiment of the present disclosure, the same incident light is irradiated to different incident positions by a spectroscopic method.

According to the embodiments of the present disclosure, in order to reduce the incident light intensity of the incident light per unit area, a multi-point incident manner may be adopted, that is, the same incident light is incident from at least two incident positions.

According to an embodiment of the present disclosure, the measurement probe includes M photosensitive surfaces. Obtaining the Raman intensity corresponding to each beam of Raman scattered light collected by the measurement probe, wherein the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in tissue component concentration, may include the following operations.

Obtain the light intensity values corresponding to each Raman scattered light collected by the M photosensitive surfaces, and obtain T Raman intensities, where each Raman intensity is the Raman scattered light collected from one or more photosensitive surfaces The total area of the same photosensitive surface is greater than or equal to the area threshold and the area of each photosensitive surface in the same photosensitive surface is continuous, the same photosensitive surface includes one or more photosensitive surfaces, and the same photosensitive surface is used to output a Raman intensity, 1≤T≤M, so that the tissue component measurement device has a level of signal-to-noise ratio that satisfies the resolution of expected changes in tissue component concentration.

According to an embodiment of the present disclosure, each of the M photosensitive surfaces may be used alone, partially combined, or used in full combination, and the combined use means outputting one Raman intensity. In the embodiments of the present disclosure, a photosensitive surface for outputting one Raman intensity is referred to as a similar photosensitive surface, and a similar photosensitive surface may include one or more photosensitive surfaces. Wherein, the condition for the combined use of different photosensitive surfaces may be that the average optical path of the Raman scattered light received by each photosensitive surface is within the range of the average optical path. The average optical path range may be a range consisting of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to the optical path average value and the optical path variation amplitude. The average optical path length is the average value calculated from the average optical path length of the Raman scattered light received by each photosensitive surface of the same type of photosensitive surface. Exemplarily, if the average optical path length is a, and the optical path variation range is ±30%, the first average optical path threshold may be 0.7a, and the second average optical path threshold may be 1.3a.

The average optical path length will be described below. The transmission path of light in the tissue can be represented by the optical path and the penetration depth, where the optical path is used to represent the total distance of light transmission in the tissue, and the penetration depth is used to represent the maximum longitudinal distance that the light can reach in the tissue . For a determined source-to-detection distance, the average optical path length is used to represent the average of the optical path lengths of light in the tissue. The probability distribution function of the optical path can be understood as a function of the source-detection distance and tissue optical parameters, wherein the source-detection distance represents the radial distance between the center of the incident light and the center of the photosensitive surface. Correspondingly, in mathematical expression, the average optical path can be understood as a function of the source-probe distance and tissue optical parameters, wherein the tissue optical parameters can include absorption coefficient, scattering coefficient and anisotropy factor. Factors affecting the average optical path may include absorption coefficient, scattering coefficient, anisotropy factor, and source-detection distance.

According to an embodiment of the present disclosure, each photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface. The non-ring photosensitive surface may include a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface or a polygonal photosensitive surface. The polygonal photosensitive surface may include a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

Similar photosensitive surfaces may be annular photosensitive surfaces or non-annular photosensitive surfaces. The same type of photosensitive surface is an annular photosensitive surface, which may be included in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, which may be included in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

In order to make the tissue component measurement device provided with the measurement probe to have a signal-to-noise ratio level that satisfies the expected changes in tissue component concentration, it can be achieved by improving the efficiency of the measurement probe to receive Raman scattered light.

In order to improve the efficiency of the measurement probe to receive Raman scattered light, a larger-area photosensitive surface (that is, a large-area photosensitive surface) can be used, that is, the total photosensitive surface area of the same photosensitive surface is greater than or equal to the area threshold, and the same photosensitive surface The area of each photosensitive surface is continuous, and the photosensitive surface is made of photosensitive material, which is different from single-point fiber receiving and multiple single fiber joint receiving. Since the large-area photosensitive surface can realize the reception of Raman scattered light in a wide range, the efficiency of receiving Raman scattered light can be improved. In addition, by disposing the photosensitive surface on the surface close to the measurement area, higher efficiency of Raman scattered light is achieved.

According to an embodiment of the present disclosure, the material of the photosensitive surface may be determined according to the second preset wavelength. Exemplarily, if the second preset wavelength belongs to the near-infrared band, the material of the photosensitive surface may be indium gallium arsenide.

According to the embodiment of the present disclosure, each photosensitive surface can collect the light intensity value of the Raman scattered light emitted from the emission position within the preset anti-shake range corresponding to the photosensitive surface.

According to the embodiments of the present disclosure, in the process of realizing the concept of the present disclosure, the inventor also found that if only the intensity distribution of the light spot irradiated by the incident light to the measurement area is changed under the condition that other conditions remain unchanged, the obtained measurement results will be different. . If the measurement results obtained by setting the photosensitive surface close to the blood vessel are compared with the measurement results obtained by setting the same photosensitive surface far away from the blood vessel under the condition that other conditions remain unchanged, the measurement results obtained by setting the photosensitive surface away from the blood vessel are better than those obtained by setting the photosensitive surface away from the blood vessel. Set the resulting measurement. The measurement result can be characterized by the relative variation of the light intensity value of the Raman scattered light received by the photosensitive surface or the standard deviation of the light intensity value. When studying the reasons for the different measurement results, it was found that changing the intensity distribution of the light spot irradiated by the incident light to the measurement area can reflect the randomness of the light source irradiation, the distance from the blood vessel can reflect the strength of the pulse beat, and the randomness of the light source irradiation and the pulse Jitter is a source of jitter. Thus, it was found that one of the reasons for the difficulty in obtaining reliable measurement results is jitter.

Based on the research on jitter, it is found that according to the source that causes jitter, it can be divided into internal sources and external sources. Among them, the internal source can include not only the pulse beat, but also the physiological background variation. In addition to the randomness of the illumination of the light source, the external source can also include the uncertainty of the transmission of the incident light itself. The randomness of the light source illumination can be reflected by the intensity distribution of the light spot illuminated by the incident light to the measurement area. It was found that whether jitter caused by internal sources or jitter caused by external sources would affect the transmission path of light in the tissue, which in turn affected the intensity distribution of Raman scattered light on the measurement area. In order to solve the problem that it is difficult to obtain the real measured tissue component signal caused by the jitter, the inventor found that the light intensity value of the Raman scattered light can be collected by using a photosensitive surface with a large area (that is, a large-area photosensitive surface). In order to effectively suppress the adverse effects of jitter on the measurement results. That is, the large-area photosensitive surface can effectively suppress the adverse effects caused by jitter. The so-called "large-area photosensitive surface" can be understood as the area of the photosensitive surface that enables the photosensitive surface to collect Raman scattering from the exit position within the preset anti-shake range. The light intensity value. The following will specifically explain why the scheme of collecting the Raman intensity of Raman scattered light with a large-area photosensitive surface can effectively suppress the adverse effects of jitter on the measurement results.

Since the large-area photosensitive surface can increase the ratio of the area of the photosensitive surface that can stably receive Raman scattered light to the area of the photosensitive surface, the stability of receiving Raman scattered light can be improved, and the Raman caused by jitter can be reduced. The detrimental effect of changes in the intensity distribution of scattered light, thereby increasing the likelihood of obtaining a true signal of the measured tissue composition. Among them, the stability can be characterized by the relative change of the light intensity value of the Raman scattered light received by the photosensitive surface or the standard deviation of the light intensity value. The smaller the relative change of the light intensity value, the higher the stability, and the standard of the light intensity value The smaller the difference, the higher the stability.

Illustratively, the jitter caused by pulse beating is taken as an example for description. Pulse beat can be reflected by the state of blood vessels. FIG. 2 schematically shows a schematic diagram of using a photosensitive surface with a small area to receive Raman scattered light when jitter occurs, according to an embodiment of the present disclosure. FIG. 3 schematically shows a schematic diagram of a photosensitive surface with a larger area to receive Raman scattered light when jitter occurs, according to an embodiment of the present disclosure. The same jitter occurs in Figures 2 and 3. Figures 2 and 3 are both square photosensitive surfaces. The area of the photosensitive surface A in FIG. 2 is smaller than the area of the photosensitive surface B in FIG. 3 . In FIGS. 2 and 3 , the vascular state 1 represents the vasoconstriction state, the vascular state 2 represents the vasodilation state, the skin state 1 represents the skin state corresponding to the vascular state 1 , and the skin state 2 represents the skin state corresponding to the vascular state 2 . Skin state 1 to skin state 2 embody jitter.

Compare measurements obtained with photosensitive surfaces of different areas under the same jitter. The measurement result is characterized by the relative variation of the light intensity value of the Raman scattered light received by the photosensitive surface within a preset time period or the standard deviation of the light intensity value. Wherein, the relative change of the light intensity value can be determined by the following methods: calculating the difference between the maximum light intensity value and the minimum light intensity value within the preset time period, calculating the average value of the outgoing values within the preset time period, and calculating the difference The ratio of the value to the average value, and the ratio is used as the relative change of the light intensity value. The preset time period may be a pulse period.

The measurement results also show that whether the relative change in the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result, or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result, which is obtained by using the photosensitive surface B. The measurement results of all are better than those obtained with the photosensitive surface A.

Since the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be explained that the large-area photosensitive surface can improve the stability of receiving Raman scattered light, thereby reducing the disadvantage of changes in the intensity distribution of Raman scattered light caused by jitter. impact, thereby increasing the likelihood of obtaining a true signal of the measured tissue composition.

It should be noted that the large-area photosensitive surface described in the embodiments of the present disclosure can achieve higher Raman scattering when the distance from the surface of the measurement area is small, that is, when it is close to the surface of the measurement area Light stability and efficiency. This cannot be achieved by single-point fiber receiving and multiple single-fiber joint receiving because, first, it is limited by the numerical aperture of the fiber; second, it is limited by the state change of the fiber. The state of the optical fiber is easily affected by the environment, and its change has a great influence on the stability of receiving Raman scattered light.

It should also be noted that, generally, in order to improve the signal-to-noise ratio of Raman intensity, a large-area photosensitive surface can be used. In other words, the large-area photosensitive surface can not only play a role in improving the efficiency of Raman intensity, but also play a role in effectively suppressing jitter.

In order to improve the reliability of the measurement results, it is necessary to ensure that each photosensitive surface can collect the light intensity value of the Raman scattered light emitted from the output position within the preset anti-shake range corresponding to the photosensitive surface. The surface area is as large as possible. Each photosensitive surface has a corresponding preset anti-shake range, and the preset anti-shake ranges of different photosensitive surfaces are the same or different. In the following, it will be explained from three aspects that the larger the area of the photosensitive surface, the better the effect of suppressing jitter. It is preset that the area of the photosensitive surface A is smaller than the area of the photosensitive surface B. Both the photosensitive surface A and the photosensitive surface B are square photosensitive surfaces.

One is to suppress the jitter caused by the pulse beat. The photosensitive surface A and the photosensitive surface B are respectively set at the same position on the measurement area, which is a position close to the blood vessel. Under other conditions being the same, compare the measurement results obtained with the photosensitive surface A and the photosensitive surface B, wherein the measurement results use the relative change in the light intensity value or the light intensity value of the Raman scattered light received by the photosensitive surface in one pulsation period. Standard deviation characterization of strong values. The calculation method of the relative change of the light intensity value is as described above, and will not be repeated here. It is found that the relative change of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the relative change of the light intensity value of the Raman scattered light received by the photosensitive surface A, and the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface B It is less than the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface A. From this, it can be concluded that whether the relative change of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result, or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result. The measurements obtained with B are all better than those obtained with the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than those obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be said that the larger the area of the photosensitive surface, the more effective it is to suppress the pulse beat. The better the dithering effect.

Second, the jitter caused by the change in the intensity distribution of the light spot irradiated to the measurement area by the incident light is suppressed. Under the condition that other conditions remain unchanged, only the intensity distribution of the light spot irradiated by the incident light to the measurement area is changed. The measurement results obtained by using the photosensitive surface A and the photosensitive surface B are compared, wherein the measurement results are characterized by the relative change of the light intensity value or the standard deviation of the light intensity value of the light intensity value received by the photosensitive surface within a preset time period. The calculation method of the relative change of the light intensity value is as described above, and will not be repeated here. It is found that the variation of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the variation of the light intensity value of the Raman scattered light received by the photosensitive surface A, and the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than that of the photosensitive surface A. The standard deviation of the light intensity values of the Raman scattered light received by face A. From this, it can be concluded that whether the relative change of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result, or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result. The measurements obtained with B are all better than those obtained with the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than those obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be said that the larger the area of the photosensitive surface, the inhibition of the incident light irradiation to the The better the effect of jitter caused by changes in the intensity distribution of the light spot in the measurement area.

Third, the jitter caused by the uncertainty of the transmission of the incident light itself is suppressed. The Monte Carlo simulation method was used. Taking the center of incident light with a photon number of 10 ¹⁵ incident, the photosensitive surface A and the photosensitive surface B are respectively set at 2.4 mm from the center of the incident light, and the number of simulations is 22. Compare the measurement results obtained with the photosensitive surface A and the photosensitive surface B. The measurement results are characterized by the standard deviation of the number of Raman scattered photons per unit area. The smaller the standard deviation of the number of Raman scattered photons per unit area, the better the suppression effect. FIG. 4 is a schematic diagram of a measurement result obtained by a Monte Carlo simulation method according to an embodiment of the present disclosure. It is found that the standard deviation of the number of Raman scattered photons per unit area corresponding to the photosensitive surface B is smaller than the standard deviation of the number of Raman scattered photons per unit area corresponding to the photosensitive surface A. That is, the measurement results obtained using the photosensitive surface B are better than the measurement results obtained using the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than the measurement results obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than that of the photosensitive surface A, it can be explained that the larger the area of the photosensitive surface is, the greater the area of the photosensitive surface can be The better the effect of jitter caused by the uncertainty of the transmission.

Through the examples of the above three aspects, it is explained that the larger the area of the photosensitive surface, the better the effect of suppressing the adverse effects of jitter on the measurement results.

According to an embodiment of the present disclosure, the ratio of the average optical path of the Raman scattered light received by each photosensitive surface in the target tissue layer to the total optical path is greater than or equal to the proportional threshold, wherein the total optical path is the Raman scattered light in the The total distance traveled within the measurement area.

According to the embodiment of the present disclosure, the tissue model of the measured object is usually a layered structure, that is, it can be divided into one or more layers. The information of the measured tissue components carried by different tissue layers is different. In order to improve the possibility of obtaining the real measured tissue component signals, it is necessary to make the transmission path of the Raman scattered light as much as possible to carry the information of the measured tissue components. Rich in layers of tissue. The target tissue layer can be understood as the tissue layer that carries the information of the measured tissue components, or the tissue layer that is the main source of the measured tissue components. In the following, the measured object is the human body, and the measured tissue component is blood glucose as an example for description.

The human skin tissue model can be understood as a three-layer model, from outside to inside are the epidermis, dermis and subcutaneous fat layer. Among them, the epidermis contains a small amount of tissue fluid and does not contain plasma and lymph. The dermis contains a large amount of tissue fluid, and because of the abundant capillaries, it also contains a large amount of plasma and a small amount of lymph. The subcutaneous fat layer contains a small amount of cellular fluid, and because of the existence of blood vessels such as veins and arteries, it contains a large amount of plasma and a small amount of lymph fluid. It can be seen that the information of the measured tissue components carried by different tissue layers is different.

Since the epidermis contains a small amount of tissue fluid, the epidermis is not a suitable source of blood glucose information. Although the subcutaneous fat layer contains a large amount of plasma and a relatively small amount of interstitial fluid, it is also not a suitable source of blood glucose information due to the limited depth of penetration of incident light. Since the dermis layer contains abundant capillaries and a large amount of tissue fluid, and incident light can easily reach the dermis layer, the dermis layer can be the main source of blood glucose information. Correspondingly, the target tissue layer may be the dermis layer.

According to the embodiments of the present disclosure, the average optical path length of the Raman scattered light in each tissue layer can be determined according to the optical path length and the penetration depth.

In order to ensure that the transmission path of the Raman scattered light is mainly the Raman scattered light passing through the target tissue layer, it is necessary to make the ratio of the average optical path of the Raman scattered light received by each photosensitive surface in the target tissue layer to the total optical path Greater than or equal to the proportional threshold, where the total optical path can be the total distance that Raman scattered light travels in the measurement area, that is, the total distance traveled by the incident light from entering the measurement area, traveling in the measurement area until reaching the exit position. Among them, the proportional threshold is related to the source-detection distance between the center of the photosensitive surface and the center of the incident light and the tissue optical parameters.

It should be noted that, since the embodiment of the present disclosure limits the ratio of the average optical path of the Raman scattered light received by the photosensitive surface in the target tissue layer to the total optical path, the area of the photosensitive surface of the embodiment of the present disclosure is limited Not too large, it is a large area within an area.

According to an embodiment of the present disclosure, the method may further include the following operations.

Determine the total area of the same type of photosensitive surface according to the tissue structure characteristics in the measurement area.

According to an embodiment of the present disclosure, the total area of the photosensitive surfaces of the same type may be determined according to the tissue structure characteristics in the measurement area. Among them, the organizational structure feature can be understood as the structural feature possessed by the measurement area.

Exemplarily, if the measurement area is the area where three blood vessels intersect, if the same photosensitive surface is set in the area where the three blood vessels intersect, the total area of the same photosensitive surface is limited by the area where the three blood vessels intersect, that is, the same photosensitive surface. The total area needs to be determined based on the area of the area where the three vessels intersect.

Another example is that the measurement area is the area where the finger is located. If the same photosensitive surface is set in the area where the finger is located, the total area of the same photosensitive surface is limited by the area where the finger is located, that is, the total area of the same photosensitive surface needs to be based on the area where the finger is located. area is determined.

It should be noted that, since the area of the photosensitive surface in the embodiment of the present disclosure can be determined according to the characteristics of the tissue structure, and generally the area determined according to the characteristics of the tissue structure cannot be too large, therefore, the area of the photosensitive surface in the embodiment of the present disclosure cannot be too large, It is a large area within an area.

According to an embodiment of the present disclosure, the ratio of the area of each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold.

According to the embodiments of the present disclosure, in order to reduce the influence of the uncertainty of incident light transmission, randomness of light source, physiological background variation, and jitter caused by pulse beating on the distribution of Raman scattered light on the measurement area, the photosensitive surface can be The reason is that the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is as large as possible.

For convenience of description, the photosensitive surface is divided into two parts, ie, an edge part and a non-edge part (or inner part). Usually, jitter mainly affects the Raman scattered light collected by the edge part, and the non-edge part is less affected, that is, the non-edge part can collect the Raman scattered light relatively stably. To understand from another angle, in the presence of jitter, since the intensity distribution of the Raman scattered light located at the edge part will change slightly, the light intensity value of the Raman scattered light received by the edge part will be higher. Since most of the Raman scattered light located in the non-edge part can be collected by the photosensitive surface relatively stably, the light intensity value of the Raman scattered light received by the non-edge part can remain relatively stable. Therefore, in order to effectively suppress the adverse effect of jitter on the measurement results, the ratio of the area corresponding to the non-edge portion to the area of the photosensitive surface can be made as large as possible, and the larger the ratio, the better the effect of weakening the adverse effect. The edge portion can be characterized by the photosensitive perimeter of the photosensitive surface, and the non-edge portion can be characterized by the area of the photosensitive surface. Thereby, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface can be made as large as possible.

Exemplarily, if the photosensitive surface 1 is a circular photosensitive surface, and the photosensitive surface 2 is a square photosensitive surface, in the case of the same photosensitive perimeter, since the area of the photosensitive surface 1 is larger than the area of the photosensitive surface 2, the photosensitive surface 1 The ratio of the area to the perimeter is greater than the ratio of the area to the perimeter of the photosensitive surface 2 . Therefore, the photosensitive surface 1 has a better effect of reducing adverse effects than the photosensitive surface 2 .

It should be noted that when the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the condition that the area of the photosensitive surface is greater than or equal to the area threshold is satisfied. For most shapes of photosensitive surfaces, if the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the size of the photosensitive surface is actually limited. This is because for most shapes of graphics, the ratio of the area to the perimeter of the graphic has a positive correlation with the size of the area, that is, the larger the ratio of the area to the perimeter of the graphic, the larger the area of the graphic.

Exemplarily, such as a circle, the area of the circle is πR ² , and the ratio of the area to the perimeter of the circle is R/2, where R represents the radius. Since the ratio of the area to the circumference of a circle is only related to the radius, and the size of the area of the circle is only related to the radius, therefore, the ratio of the area to the circumference of a circle has a positive correlation with the size of the area. The ratio of the area of a circle to its perimeter also defines the size of the area of the circle. Another example is a square, the area of the square is a ² , the ratio of the area of the square to the perimeter is a/4, and a represents the length of the side. Since the ratio of the area to the perimeter of a square is only related to the length of the side, and the size of the area of the square is only related to the length of the side, therefore, the ratio of the area to the perimeter of the square has a positive correlation with the size of the area, if the square is defined The ratio of the area to the perimeter also defines the size of the area of the square.

According to an embodiment of the present disclosure, the ratio threshold is greater than or equal to 0.04 mm.

According to the embodiments of the present disclosure, the area of the photosensitive surface of the present disclosure is a relatively large area, that is, the area of the photosensitive surface is a large area within an area range. This case will be described below.

First, the area of the photosensitive surface cannot be too small. Since the large-area photosensitive surface in the embodiment of the present disclosure refers to the area of the photosensitive surface that enables the photosensitive surface to collect the light intensity value of the Raman scattered light emitted from the exit position within the preset anti-shake range, the embodiment of the present disclosure The large area of the large-area photosensitive surface is the large area used to achieve anti-shake. At the same time, because the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface can be used to characterize the area of the photosensitive surface, the photosensitive surface can collect pre- The light intensity value of the Raman scattered light emitted from the output position within the anti-shake range is set. In general, the ratio of the area of the photosensitive surface to the perimeter has a positive correlation with the area of the photosensitive surface. Therefore, if the photosensitive surface is If the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the size of the area of the photosensitive surface is actually limited, that is, the ratio of the area to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold. The limited area of the photosensitive surface cannot be too small.

Second, the area of the photosensitive surface should not be too large. The embodiment of the present disclosure requires that the ratio of the average optical path length of the Raman scattered light received by the photosensitive surface to the total optical path in the target tissue layer is greater than or equal to the ratio threshold, and/or the area of the photosensitive surface is determined according to the characteristics of the tissue structure. The area of the photosensitive surface should not be too large.

From this, it can be explained that the area of the photosensitive surface of the embodiment of the present disclosure is a relatively large area, that is, a large area within an area range.

In addition, although the area of the photosensitive surface is large, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is not large due to the large perimeter of the photosensitive surface. The ratio of the perimeters of the surfaces is smaller than the ratio threshold. Therefore, it may be difficult for an absolutely large-area photosensitive surface to meet the requirements of anti-shake. There may also be cases where the area of the photosensitive surface is too small and the perimeter of the photosensitive surface is large, so that the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is less than the ratio threshold. Therefore, the area of the photosensitive surface is too small. jitter requirements.

According to an embodiment of the present disclosure, the photosensitive surface is in contact or non-contact with the surface of the measurement area.

According to embodiments of the present disclosure, the form of tissue composition measurement may include contact measurement and non-contact measurement. Among them, the contact measurement can prevent the interference light from being received by the photosensitive surface, thereby improving the possibility of obtaining the real measured tissue component signal. Non-contact measurement can avoid the influence of interfering factors such as temperature and pressure on the measurement results, which in turn can improve the possibility of obtaining the true signal of the measured tissue composition.

If the photosensitive surface is set in contact with the surface of the measurement area, the form of tissue composition measurement can be considered as contact measurement. If the photosensitive surface is set to be non-contact with the surface of the measurement area, the form of tissue composition measurement can be considered as non-contact measurement.

According to an embodiment of the present disclosure, the distance of the photosensitive surface from the surface of the measurement area is less than or equal to the first distance threshold and the efficiency of the photosensitive surface to receive Raman scattered light is greater than or equal to the efficiency threshold.

According to the embodiments of the present disclosure, since the photosensitive surface is made of photosensitive material, the area of the photosensitive surface is continuous, therefore, the reception of a wide range of light intensity values can be realized, and the efficiency of receiving Raman scattered light can be improved. Based on this, even in the case of being close to the surface of the measurement area, that is, in the case where the distance between the photosensitive surface and the surface of the measurement area is less than or equal to the first distance threshold, the efficiency of receiving Raman scattered light can be achieved to be greater than or equal to the efficiency threshold.

According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of different photosensitive surfaces are the same or different.

According to an embodiment of the present disclosure, each photosensitive surface may be made of a photosensitive material. The ring-shaped photosensitive surface can avoid the problem of azimuth positioning, and can also realize the design of a large area within a small source detection distance range. It should be noted that, in the measurement of living tissue composition, the source detection distance is usually a relatively important physical quantity, so it is very meaningful to realize a larger area design within a smaller source detection distance range.

According to embodiments of the present disclosure, in some cases, the use of a non-annular photosensitive surface has the following beneficial effects.

First, since the measurement results are affected by the measurement area, usually if the photosensitive surface is set in the measurement area that is conducive to measurement, the photosensitive surface is set in the measurement area that is conducive to measurement, compared to the photosensitive surface set in the measurement area that interferes with the measurement. Better measurement results are obtained, so that the photosensitive surface can be positioned in the right position according to the characteristics of the tissue structure. The non-annular photosensitive surface can easily avoid the measurement area that interferes with the measurement, such as the blood vessel or the wound area. Therefore, the use of the non-annular photosensitive surface will have a better effect.

Second, due to the non-uniformity of the tissue, the transmission paths of the same incident light in the tissue may be different, and thus the average optical paths corresponding to the Raman scattered light at different exit positions are different. Taking the measured tissue component as blood glucose as an example, the dermis is usually the main source of the blood glucose signal, so the Raman scattered light is required to be the Raman scattered light obtained after being mainly transmitted in the dermal layer. Correspondingly, the Raman scattered light is The average optical path corresponding to the light has certain requirements.

Assuming that the annular photosensitive surface of the corresponding size is designed according to the requirements for the average optical path, it can be considered that the average optical path corresponding to the Raman scattered light received at different photosensitive positions of the annular photosensitive surface is basically similar and is mainly caused by the pulling of the dermis layer. Mann scattered light, the average optical path is in the average optical path range C. In this case, if the skin tissue is homogeneous, the above conclusion is in line with the actual situation. However, because the skin tissue is usually not uniform, the average optical path difference corresponding to the Raman scattered light received by different photosensitive positions on the same annular photosensitive surface is relatively large. The average optical path lengths corresponding to the Raman scattered light are basically similar, all within the average optical path range C, and the average optical path corresponding to the Raman scattered light received by another part of the photosensitive surface of the ring-shaped photosensitive surface is quite different from the aforementioned one, which is not in the average optical path length. within range C. Since the average optical path of the Raman scattered light is within the average optical path range C, it can indicate that the Raman scattered light mainly passes through the dermis layer, and the Raman scattered light that is not in the average optical path range C may not mainly pass through The Raman scattered light of the dermis layer, and at the same time, the annular photosensitive surface outputs a Raman intensity. Therefore, in the case of uneven skin tissue, the signal quality of the Raman intensity obtained by using the annular photosensitive surface is not high, which affects the acquisition. Possibility of true measured tissue composition signal.

The non-ring photosensitive surface can be set according to the actual situation. Taking the above example as an example, assuming that the average optical length not within the average optical path range C is within the average optical path range D, two non-ring photosensitive surfaces can be used, where, One non-annular photosensitive surface is used to receive the light intensity value of Raman scattered light whose average optical path is within the average optical path range C, and the other non-annular photosensitive surface is used to receive the average optical path of Raman scattered light The light intensity value of the Raman scattered light in the average optical path range D, and the Raman intensity of the two non-annular photosensitive surfaces are consistent with the actual, which is beneficial to ensure the possibility of obtaining the real measured tissue composition signal.

Third, when using the pulse wave-based time difference measurement method to measure tissue components, it is necessary to make full use of the pulse signal, that is, to make the difference between the systolic light intensity and the diastolic light intensity as large as possible. In the above situation, since most of the annular photosensitive surface is not located above the blood vessel, the collection effect of the pulse signal is affected, and therefore, the degree of difference between the light intensity during systole and the light intensity during diastole is reduced. It can be seen that the difference between the systolic light intensity and the diastolic light intensity obtained by using the annular photosensitive surface is smaller than the difference between the systolic and diastolic light intensity obtained by using the non-ring photosensitive surface.

Fourth, due to the influence of tissue inhomogeneity and physiological background changes on Raman scattered light, the average optical path of Raman scattered light received by different photosensitive surfaces with the same source-detection distance from the center of the incident light may be different. Therefore, the Raman intensities collected by different photosensitive surfaces with the same source-detection distance from the center of the incident light can be used for differential operation to measure tissue composition. The above non-annular photosensitive surface can be realized, that is, for the same source detection distance, at least two non-annular photosensitive surfaces can be discretely arranged with the center of the incident light as the center, so as to output two Raman intensities.

Fifth, the manufacturing process is less difficult and the manufacturing cost is lower.

The fourth aspect will be described below with reference to FIG. 5 . FIG. 5 schematically shows a schematic diagram of a differential measurement according to an embodiment of the present disclosure. As shown in Figure 5, Figure 5 includes four fan ring photosensitive surfaces, namely fan ring photosensitive surface 1, fan ring photosensitive surface 2, fan ring photosensitive surface 3 and fan ring photosensitive surface 4, and the four fan ring photosensitive surfaces are individually In use, each fan ring photosensitive surface has a corresponding Raman intensity. The centers of the four fan-ring photosensitive surfaces have the same distance from the center of the incident light, that is, have the same source-detection distance. Due to the non-uniformity of the tissue, the average optical path corresponding to the Raman scattered light received by the fan ring photosensitive surface 1 and the fan ring photosensitive surface 2 is different. Therefore, according to the Raman intensity collected by the fan ring photosensitive surface 1 and the fan ring photosensitive The Raman intensity collected by surface 2 is subjected to differential operation to realize differential measurement.

According to an embodiment of the present disclosure, the non-ring-shaped photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

According to an embodiment of the present disclosure, the polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to the embodiments of the present disclosure, the central angle can be designed according to the actual situation, so as to obtain the corresponding photosensitive surface of the fan ring. For example, a fan ring photosensitive surface with a central angle of 90°, a fan ring photosensitive surface with a central angle of 180°, and a fan ring photosensitive surface with a central angle of 45°.

According to an embodiment of the present disclosure, the same type of photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, wherein the same type of photosensitive surface includes one or more photosensitive surfaces, and the same type of photosensitive surface is used to output a Raman intensity.

According to an embodiment of the present disclosure, the same type of photosensitive surface may be a ring-shaped photosensitive surface or a non-annular photosensitive surface, that is, the same type of photosensitive surface appears as a ring-shaped photosensitive surface or a non-annular photosensitive surface as a whole. According to the number of photosensitive surfaces included in the same type of photosensitive surface, it can be determined whether the overall shape is formed by a single photosensitive surface or formed by a combination of multiple photosensitive surfaces. The shape of each photosensitive surface in the same type of photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface.

According to an embodiment of the present disclosure, the same type of photosensitive surface is an annular photosensitive surface, which may include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, which may include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

According to the embodiment of the present disclosure, the plurality of photosensitive surfaces participating in the combination are closely arranged to ensure that there is no gap between adjacent photosensitive surfaces as much as possible. Since the circular photosensitive surface or the square photosensitive surface is more common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while the photosensitive surface of other shapes usually needs to be customized, the manufacturing process is more difficult and the manufacturing cost is higher. Therefore, if limited In terms of production cost, a combination method can be used to combine multiple circular photosensitive surfaces and/or multiple square photosensitive surfaces to form similar photosensitive surfaces of other shapes. Among them, square includes square or rectangle.

In addition, the production cost of the photosensitive surface is also related to the area of the photosensitive surface. Generally, the larger the area of the photosensitive surface, the higher the production cost. If a larger-area photosensitive surface is required, and there are currently multiple smaller-area photosensitive surfaces, in order to reduce the manufacturing cost, multiple smaller-area photosensitive surfaces can be combined to obtain a larger-area photosensitive surface.

According to an embodiment of the present disclosure, in the case where it is determined that the distance between the same type of photosensitive surface and the target site is greater than or equal to the second distance threshold, the same type of photosensitive surface includes a ring photosensitive surface, a fan ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface or Square photosensitive surface.

According to the embodiments of the present disclosure, when it is determined that the distance between the same photosensitive surface and the target site is greater than or equal to the second distance threshold, a photosensitive surface with an appropriate shape can be selected according to the jitter of the actual Raman scattered light, so as to maximize the Attenuates the adverse effects of jitter on measurements.

The target site may be the site where jitter occurs. Since one of the sources of jitter is pulse beating, and pulse beating is related to blood vessels, the target site can be blood vessels. Generally, the jitter distribution of the Raman scattered light close to the blood vessel has a certain directionality, while the jitter distribution of the Raman scattered light far from the blood vessel is relatively uniform and has no directionality.

If the same type of photosensitive surface is far away from the target part (such as the target blood vessel), it means that the jitter distribution of Raman scattered light is relatively uniform. or square photosensitive surface. That the photosensitive surfaces of the same type are far away from the target portion can be understood as the distance between each photosensitive surface of the same photosensitive surface from the target portion is greater than or equal to the second distance threshold. The distance between each photosensitive surface of the same type of photosensitive surface and the target site is greater than or equal to the second distance threshold value may include that the distance between the edge of the photosensitive surface of the same type of photosensitive surface closest to the target site and the target site is greater than or equal to the second distance threshold value, or, The photosensitive surfaces of the same type are not in contact with the target part, and the distance from the center of the photosensitive surface closest to the target part in the photosensitive surfaces of the same type to the target part is greater than or equal to the second distance threshold.

In the case where the same photosensitive surface is far away from the target part, if the average optical path of Raman scattered light received by different photosensitive positions of each photosensitive surface in the same photosensitive surface is less than or equal to the optical path threshold, it can be proved that the Raman scattered light The dithering condition is affected by the optical path size, wherein, the larger the average optical path length of the Raman scattered light, the more obvious the dithering condition of the Raman scattered light, and vice versa, the less obvious the dithering condition of the Raman scattered light. In this case, the arc length corresponding to the position farther from the center of the incident light can be designed to be longer, so that a ring-shaped photosensitive surface, a fan-shaped photosensitive surface or a fan-shaped photosensitive surface can be selected.

When the same photosensitive surface is far away from the target, if the average optical path of the Raman scattered light received by different photosensitive positions of each photosensitive surface in the same photosensitive surface is greater than the optical path threshold, it can explain the jitter of the Raman scattered light It has almost nothing to do with the optical path size. In this case, a circular photosensitive surface or a square photosensitive surface can be selected.

According to an embodiment of the present disclosure, in the case where the same type of photosensitive surface is a fan ring photosensitive surface, if the same type of photosensitive surface includes one photosensitive surface, the fan ring photosensitive surface is an independent fan ring photosensitive surface. If the same photosensitive surface includes multiple photosensitive surfaces, the fan ring photosensitive surface is a photosensitive surface formed by combining the multiple photosensitive surfaces. Similarly, for the case where the same type of photosensitive surface includes a ring-shaped photosensitive surface, a circular photosensitive surface, a square photosensitive surface or a fan-shaped photosensitive surface, it can be the same type of photosensitive surface formed independently or the same type of photosensitive surface formed in combination.

It should be noted that, because the current circular photosensitive surface or square photosensitive surface is more common, the production process is less difficult and the production cost is low, while the photosensitive surface of other shapes usually needs to be customized, the production process is more difficult, and the production cost is high. Therefore, if limited by the manufacturing cost, if the distance between the same type of photosensitive surface and the target site is determined to be greater than or equal to the first distance threshold, the same type of photosensitive surface includes a circular photosensitive surface or a square photosensitive surface.

According to an embodiment of the present disclosure, when it is determined that the distance between the same type of photosensitive surface and the target site is less than or equal to the third distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of Raman scattered light.

According to the embodiment of the present disclosure, if the same type of photosensitive surface is close to the target part (for example, the target blood vessel), it can be shown that the jitter distribution of the Raman scattered light has a certain directionality. In this case, the shape of the same photosensitive surface can be determined according to the jitter distribution of Raman scattered light, optionally, the shape of the same photosensitive surface and the jitter distribution of Raman scattered light are similar graphs. Exemplarily, if the jitter distribution of the Raman scattered light is elliptical, the shape of the same photosensitive surface can be designed to be an elliptical photosensitive surface. Alternatively, if the jitter distribution of the Raman scattered light is rectangular, the shape of the photosensitive surface of the same type can be designed to be a rectangular photosensitive surface. Alternatively, if the jitter distribution of the Raman scattered light is rhombic, the shape of the similar photosensitive surfaces can be designed to be rhombic photosensitive surfaces.

According to an embodiment of the present disclosure, the jitter distribution of Raman scattered light includes a jitter distribution along a first direction and a jitter distribution along a second direction, the first direction and the second direction are perpendicular to each other, and the same photosensitive surfaces are along the first direction. The ratio of the length in one direction to the length of the same photosensitive surface in the second direction is determined according to the ratio of the jitter amplitude of the Raman scattered light in the first direction to the jitter amplitude of the Raman scattered light in the second direction, The Raman scattered light has the largest jitter in the first direction.

According to an embodiment of the present disclosure, if the jitter distribution of the Raman scattered light includes the jitter distribution of the Raman scattered light along two mutually perpendicular directions, wherein the dither distributions of the two mutually perpendicular directions are the dither distributions of the Raman scattered light The jitter is decomposed into these two mutually perpendicular directions, and the two mutually perpendicular directions are called the first direction and the second direction respectively. The ratio of the jitter amplitude of the Mann scattered light along the first direction and the second direction, and setting the ratio of the length of the same photosensitive surface along the first direction to the length along the second direction, can make the same photosensitive surface along the first direction. The ratio of the upward length to the length along the second direction is greater than or equal to the ratio of the jitter amplitudes of the Raman scattered light along the first direction to the second direction.

同类感光面沿Y轴方向上的长度与沿X轴方向上的长度的比值可以表示为

则

Exemplarily, if the first direction and the second direction are the Y-axis direction and the X-axis direction in the rectangular coordinate system, respectively, then the ratio of the jitter amplitude along the Y-axis direction of the Raman scattered light to the jitter amplitude along the X-axis direction It can be expressed as

The ratio of the length of the same photosensitive surface along the Y-axis direction to the length along the X-axis direction can be expressed as

but

According to an embodiment of the present disclosure, the same type of photosensitive surface includes a rectangular photosensitive surface or an elliptical photosensitive surface, and the ratio of the length to the width of the rectangular photosensitive surface is determined according to the jitter amplitude of the Raman scattered light along the first direction and the Raman scattered light along the second direction. Determined by the ratio of the jitter amplitudes in the two directions, the ratio of the major axis to the minor axis of the elliptical photosensitive surface is based on the jitter amplitude of the Raman scattered light along the first direction and the jitter amplitude of the Raman scattered light along the second direction ratio is determined.

According to an embodiment of the present disclosure, if the distance between the same photosensitive surface and the target site is less than or equal to the third distance threshold, the jitter distribution of the Raman scattered light includes a jitter distribution decomposed into the first direction and the second direction, the first If the direction and the second direction are perpendicular to each other, the same photosensitive surface may include a rectangular photosensitive surface or an elliptical photosensitive surface. Wherein, the ratio of the length to the width of the rectangular photosensitive surface is greater than or equal to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude along the second direction. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is greater than or equal to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude along the second direction.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength may include the following operations.

The concentration of the measured tissue component is determined by processing at least one Raman intensity corresponding to the second preset wavelength based on the interference suppression method.

According to the embodiments of the present disclosure, since the variation of uncontrollable measurement conditions is unpredictable and uncontrollable, it is difficult to ensure the reproducibility of such measurement conditions by adopting an effective control method, thereby reducing the variation of uncontrollable measurement conditions influence on the measurement results. However, a reasonable mathematical algorithm can be used to reduce the influence of the change of uncontrollable measurement conditions on the measurement result, so that its influence on the measurement result can be reduced to a negligible level, that is, the influence of the change of the uncontrollable measurement condition on the measurement result is different from randomness. The level of influence of noise on the measurement results is comparable.

In order to reduce the influence of the variation of uncontrollable measurement conditions on the measurement result, an interference suppression method can be adopted, wherein the interference suppression method can include a differential measurement method. The differential measurement method may include a time differential measurement method and a position differential measurement method.

According to an embodiment of the present disclosure, processing at least one Raman intensity corresponding to the second preset wavelength based on the interference suppression method to determine the concentration of the measured tissue component may include the following operations.

The first Raman intensity and the second Raman intensity are determined from at least two Raman intensities corresponding to the second preset wavelength. Differential processing is performed on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal. According to the differential signal corresponding to the second preset wavelength, the concentration of the measured tissue component is determined.

According to the embodiments of the present disclosure, the reason why the differential measurement method can reduce the influence of uncontrollable measurement conditions on the measurement results is that if the interference information carried by the Raman intensities under different average optical The effective information carried by the Raman intensities under the optical path is different. Therefore, the Raman intensities (the first Raman intensity and the second Raman intensity) under the two average optical paths can be differentially processed to obtain a differential signal. The signal determines the concentration of the measured tissue component. Among them, the interference information can be understood as the response of the Raman intensity to the interference. Effective information can be understood as the Raman intensity response to the measured tissue composition.

According to an embodiment of the present disclosure, the differential processing in performing differential processing on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength may include a processing method in hardware and a processing method in software. Wherein, the processing manner in terms of hardware may include processing by using a differential circuit. The processing method in software may include using a difference algorithm to perform a difference operation. Differentiation algorithms may include direct differencing operations and logarithmic differencing operations. Among them, the direct difference operation refers to the difference processing of two parameters directly. The logarithmic difference operation refers to first performing the logarithmic operation on two parameters to obtain the logarithmic parameters, and then performing the difference processing of the two logarithmic parameters.

According to the embodiments of the present disclosure, the common-mode interference information can be effectively attenuated by the differential operation method, thereby improving the possibility of obtaining the real measured tissue component signal.

According to an embodiment of the present disclosure, performing differential processing on the first Raman intensity corresponding to the second preset wavelength and the second Raman intensity to obtain a differential signal may include the following operations.

A differential circuit is used to process the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal.

According to the embodiments of the present disclosure, a differential circuit can be used to implement differential processing of the first Raman intensity and the second Raman intensity, so as to directly obtain a differential signal.

According to an embodiment of the present disclosure, performing differential processing on the first Raman intensity corresponding to the second preset wavelength and the second Raman intensity to obtain a differential signal may include the following operations.

A differential algorithm is used to process the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, using a differential algorithm to process the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal may include the following operations.

A direct differential operation is performed on the first Raman intensity and the second Raman intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, using a differential algorithm to process the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal may include the following operations.

Logarithmic processing is performed on the first Raman scattered light intensity and the second Raman scattered light intensity corresponding to the second preset wavelength to obtain the first logarithmic light intensity and the second logarithmic light intensity. A differential operation is performed on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the second preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, the first logarithmic light intensity represents the logarithm of the first Raman intensity, and the second logarithmic light intensity represents the logarithm of the second Raman intensity.

The differential signal can be determined by the following formula (1).

表示第一拉曼强度，

表示第二拉曼强度。

表示与第一拉曼强度对应的平均光程，

表示与第二拉曼强度对应的平均光程。Among them, A _D represents the differential signal,

represents the first Raman intensity,

represents the second Raman intensity.

represents the mean optical path corresponding to the first Raman intensity,

represents the average optical path length corresponding to the second Raman intensity.

According to an embodiment of the present disclosure, the first Raman intensity and the second Raman intensity are acquired by the same or different photosensitive surfaces of the same type at different times, wherein the first Raman intensity is the systolic light intensity, and the second Raman intensity is The Raman intensity is the light intensity in the diastolic period, the same photosensitive surface includes one or more photosensitive surfaces, and the same photosensitive surface is used to output a Raman intensity.

According to the embodiments of the present disclosure, in the case where the first Raman intensity and the second Raman intensity are acquired by the same or different photosensitive surfaces of the same type at different times, a pulse wave-based time difference measurement method can be used to measure tissue composition Measurement.

Pulse is the arterial pulsation, which refers to the periodic contraction and relaxation with the beating of the heart. The pressure in the aorta causes pulsatile changes in the diameter of the blood vessels, and the blood flow in the blood vessels also changes regularly and periodically. Each pulse waveform includes an ascending branch and a descending branch, where the ascending branch characterizes the dilation of the ventricular systolic artery and the descending branch characterizes the ventricular diastolic arterial recoil. One contraction of the ventricle characterizes a pulsatile cycle.

According to the embodiments of the present disclosure, since the pulse wave-based time difference measurement method is adopted, the pulse information needs to be utilized as much as possible. Therefore, in order to improve the possibility of obtaining the real measured tissue component signal, the photosensitive surface can be set as far as possible in the At a location close to the target site (eg, target blood vessel). That is, the same photosensitive surface for outputting the first Raman intensity and the second Raman intensity can be set at a position where the distance from the target site is less than or equal to the fourth distance threshold. Wherein, the fourth distance threshold can be zero, that is, the same photosensitive surface can be set on the target part. The same photosensitive surface for outputting the first Raman intensity and the second Raman intensity is set at a position whose distance from the target site is less than or equal to the fourth distance threshold, that is, for outputting the first Raman intensity and the second Raman intensity The distance between each of the photosensitive surfaces of the same intensity from the target site is less than or equal to the fourth distance threshold. The distance between each photosensitive surface of the same photosensitive surface and the target site is less than or equal to the fourth distance threshold, which may be the distance between the edge of the photosensitive surface farthest from the target site and the target blood vessel in the same photosensitive surface is less than or equal to the fourth distance threshold.

It should be noted that using the pulse wave-based time difference measurement method, it is not contradictory to use the pulse information as much as possible and the above-mentioned use of a large-area photosensitive surface to reduce the adverse effects of pulse beating on the measurement. It is possible to utilize useful information from the pulse beat, which minimizes the adverse effects of the pulse beat. In addition, the first Raman intensity may be diastolic light intensity, and the second Raman intensity may also be systolic light intensity. The first Raman intensity and the second Raman intensity corresponding to the preset wavelength may be Raman intensities in the same pulsation period, or may be Raman intensities in different pulsation periods.

According to an embodiment of the present disclosure, the first Raman intensity corresponding to the second preset wavelength is collected from a first photosensitive surface of the same type corresponding to the second preset wavelength, and the second Raman intensity corresponding to the second preset wavelength The Mann intensity is collected from a second same type of photosensitive surface corresponding to the second preset wavelength, wherein the first same type of photosensitive surface includes one or more photosensitive surfaces, and the second same type of photosensitive surface includes one or more photosensitive surfaces.

According to an embodiment of the present disclosure, for the second preset wavelength, there are a first photosensitive surface of the same type and a second photosensitive surface of the same type corresponding to the second preset wavelength, wherein the first photosensitive surface of the same type is used for outputting the same photosensitive surface as the second photosensitive surface. The first Raman intensity corresponding to the preset wavelength, and the second photosensitive surface of the same type is used to output the second Raman intensity corresponding to the second preset wavelength. Both the first homogeneous photosensitive surface and the second homogeneous photosensitive surface may include one or more photosensitive surfaces.

According to an embodiment of the present disclosure, the first Raman intensity and the second Raman intensity may be processed using a position differential measurement method to determine the concentration of the measured tissue component.

According to the embodiments of the present disclosure, since the position difference measurement method needs to avoid the target part (for example, the target blood vessel) as much as possible, in order to improve the possibility of obtaining the real measured tissue component signal, the photosensitive surface can be set as far as possible from the target the location of the part. That is, the first similar photosensitive surface for outputting the first Raman intensity can be set at a position where the distance from the target site is greater than or equal to the fifth distance threshold, that is, each photosensitive surface of the first similar photosensitive surface is separated from the target site. The distance is greater than or equal to the fifth distance threshold. The distance between each photosensitive surface of the first similar photosensitive surface and the target site is greater than or equal to the fifth distance threshold, which may be the distance from the edge of the photosensitive surface closest to the target site in the first similar photosensitive surface to the target site is greater than or equal to the fifth distance threshold. Five distance thresholds. Alternatively, the photosensitive surfaces of the first similar type are not in contact with the target portion, and the distance from the center of the photosensitive surface closest to the target portion in the first similar photosensitive surfaces to the target portion is greater than or equal to the fifth distance threshold. The photosensitive surface for outputting the second Raman intensity is set at a position whose distance from the target site is greater than or equal to a sixth distance threshold. For the understanding that the second same type of photosensitive surface for outputting the second Raman intensity is set at a position whose distance from the target site is greater than or equal to the sixth distance threshold, please refer to the first similar photosensitive surface for outputting the first Raman intensity The above description will not be repeated here.

According to an embodiment of the present disclosure, the first and second similar photosensitive surfaces are the same same photosensitive surface, and the Raman scattered light received by the first similar photosensitive surface and the second similar photosensitive surface is incident light from different incident positions Incident is obtained by transmission.

According to an embodiment of the present disclosure, the first photosensitive surface of the same kind and the second photosensitive surface of the same kind are different photosensitive surfaces of the same kind.

According to the embodiment of the present disclosure, since the incident position of the incident light may include at least one, if the incident position of the incident light includes at least two, the first photosensitive surface of the same kind and the second photosensitive surface of the second kind may be the same photosensitive surface, so The difference is that if the same type of photosensitive surface is used to receive the Raman scattered light corresponding to the first Raman intensity, that is, it is used as the first similar photosensitive surface, the incident position of the Raman scattered light is the first one. an incident location. If the photosensitive surface of the same type is the same photosensitive surface used to receive the Raman scattered light corresponding to the second Raman intensity, that is, used as the second photosensitive surface of the same type, the incident position of the Raman scattered light is the second incident position , the first incident position and the second incident position are different incident positions.

According to an embodiment of the present disclosure, the first photosensitive surface of the same type and the second photosensitive surface of the same type may also be different photosensitive surfaces of the same type.

According to the embodiment of the present disclosure, the average optical path of Raman scattered light received by different light-sensing positions of each light-sensing surface in the first same-type light-sensing surface belongs to the first average optical path range, wherein the first average optical path range is based on The first optical path average value is determined, and the first optical path average value is an average value calculated according to the average optical path lengths of the Raman scattered light received by each photosensitive position of the first photosensitive surface of the same type. The average optical path lengths of the Raman scattered light received at different photosensitive positions on each photosensitive surface of the second same type of photosensitive surface belong to the second average optical path range, wherein the second average optical path range is determined according to the average value of the second optical path , wherein, the second optical path average value is an average value calculated according to the average optical path length of Raman scattered light received by each photosensitive position of the second photosensitive surface of the same type.

According to the embodiments of the present disclosure, in order to improve the possibility of obtaining a real measured tissue composition signal by using the position-based differential measurement method for tissue composition measurement, it is necessary to ensure that the Raman scattered light received by the first photosensitive surface of the same type has a short optical path. The Raman scattered light received by the second photosensitive surface of the same type also has the characteristics of a short optical path. The short optical path can be understood as the average optical path of Raman scattered light within the average optical path range.

For the first same type of photosensitive surface, the average optical path of Raman scattered light received by different photosensitive positions of each photosensitive surface in the first same type of photosensitive surface belongs to the first average optical path range. Wherein, the first average optical path range is determined in the following manner. A first optical path average value of the average optical path lengths of the Raman scattered light received by each light-sensing position of the first same-type light-sensing surface is determined, and the variation range of the first optical path is determined. The first average optical path range is determined according to the first optical path average value and the first optical path variation range. Exemplarily, if the average value of the first optical path is b and the variation range of the first optical path is ±40%, the first average optical path range may be greater than or equal to 0.6b and less than or equal to 1.4b.

For the second same type of photosensitive surface, the average optical path of Raman scattered light received by different photosensitive positions of each photosensitive surface in the second same type of photosensitive surface belongs to the second average optical path range. Wherein, the second average optical path range is determined in the following manner. A second optical path average value of the average optical path lengths of the Raman scattered light received by each photosensitive surface of the second same type of photosensitive surface is determined, and the variation range of the second optical path is determined. The second average optical path range is determined according to the second optical path average value and the second optical path variation range.

According to an embodiment of the present disclosure, the absolute value of the difference between the first optical path average value and the second optical path average value belongs to the first optical path difference range.

According to the embodiments of the present disclosure, in order to improve the possibility of obtaining a real measured tissue composition signal by performing tissue composition measurement based on the differential measurement method, it is necessary to set the first and second similar photosensitive surfaces within a suitable position range. The following description will be given by taking the measured tissue component as blood glucose as an example. If the measured tissue component is blood glucose, the target tissue layer is the dermis layer, and the Raman intensity is required to be the Raman intensity that mainly carries the tissue component information in the dermis layer.

First, if the distance between the position of the photosensitive surface and the center of the incident light is too small, the Raman intensity of the Raman scattered light will mainly carry the tissue composition information in the epidermis. If the distance between the position of the photosensitive surface and the center of the incident light is too large, the Raman intensity of the Raman scattered light will mainly carry the tissue composition information in the subcutaneous fat layer. The dermis layer is located between the epidermis layer and the subcutaneous fat layer. It can be seen that the setting positions of the first and second similar photosensitive surfaces need to be selected within an appropriate range of positions. The first and second similar photosensitive surfaces The distance between the faces should not be too large.

Second, although the differential measurement method can effectively weaken the common mode interference, the differential measurement method will also lose a part of effective information, that is, blood glucose information, while weakening the common mode interference. If the two locations are extremely close, the useful information may be completely lost. It can be seen that the setting positions of the first and second similar photosensitive surfaces need to be selected within a suitable position range, and the distance between the first and second similar photosensitive surfaces cannot be too small.

In order to realize the setting of the first photosensitive surface and the second photosensitive surface of the same type within a reasonable position range, it can be determined according to the principle of effective information measurement, the principle of differential measurement precision optimization and the principle of effective elimination of interference signals. Among them, the principle of effective information measurement may refer to the fact that the Raman scattered light at the two positions can carry as much tissue composition information in the target tissue layer as possible, therefore, the two positions should be within a reasonable position range. The principle of precision optimization of differential measurement can mean that there should be a certain distance between two positions to ensure that as much valid information as possible remains after the difference. The principle of effective interference signal elimination can mean that the distance between two positions should be as small as possible to improve the effect of the differential measurement method in eliminating common mode interference.

Set the first photosensitive surface of the same type and the second photosensitive surface of the same type within a reasonable range, which is reflected in the optical path, that is, the average value of the first optical path corresponding to the first photosensitive surface and the corresponding photosensitive surface of the second similar type. The absolute value of the difference between the second optical path average values belongs to the first optical path difference range. Wherein, the first optical path difference range is determined according to the optimal differential optical path. The optimal differential optical path may be determined according to at least one of the above three principles.

It can be understood that the position setting requirements for the first photosensitive surface and the second photosensitive surface also require that the area of the photosensitive surface should not be too large, otherwise the differential effect will be affected, thereby affecting the possibility of obtaining the real measured tissue component signal. .

According to an embodiment of the present disclosure, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to the embodiments of the present disclosure, in order to set the first photosensitive surface and the second photosensitive surface of the same type within a reasonable range as far as possible, it is also necessary to ensure that the first average optical path range is less than or equal to the first optical path as far as possible, as reflected in the optical path. difference range, and the second average optical path range is less than or equal to the first optical path difference range. Therefore, the absolute value of the difference between the average value of the first optical path corresponding to the first photosensitive surface of the same type and the average value of the second optical path corresponding to the second photosensitive surface of the same type belongs to the first optical path difference range, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to an embodiment of the present disclosure, the first optical path difference range is determined according to the optimal differential optical path corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, when the measurement area of the measured object is determined, there is an optimal differential sensitivity corresponding to the second preset wavelength, wherein the optimal differential sensitivity may represent a The sensitivity when the differential signal changes the most, the optimal differential optical path can be determined according to the optimal differential sensitivity, that is, the optimal differential optical path can be determined according to the principle of differential measurement precision optimization. The path is called the optimal differential optical path.

According to the embodiments of the present disclosure, after determining the optimal differential optical path corresponding to the second preset wavelength, the up and down adjustment range may be set, and according to the optimal differential optical path corresponding to the second preset wavelength and the vertical adjustment range, determine a first optical path difference range corresponding to the second preset wavelength.

According to the embodiment of the present disclosure, the source-detection distance of each photosensitive surface of the first same type of photosensitive surfaces corresponding to the second preset wavelength from the center of the incident light is within the range of the preset source-detection distance corresponding to the second preset wavelength , wherein the preset source detection distance range is determined according to the source detection distance between the floating reference position corresponding to the second preset wavelength and the center of the incident light.

According to the embodiments of the present disclosure, in order to further improve the possibility of obtaining the real measured tissue component signal, the position of the photosensitive surface can be set based on the floating reference method. Among them, the floating reference method will be described as follows.

For the measured object, when the incident light enters the tissue, absorption and scattering will occur. The absorption will directly lead to the attenuation of light energy, and the scattering will affect the distribution of Raman scattered light by changing the direction of photon transmission. The distribution of Mann scattered light is the result of the combined action of the two. Based on the floating reference method, for the measured tissue composition, there is a certain position from the center of the incident light, at this position, the Raman intensity of the Raman scattered light is affected to the same extent but in the opposite direction due to the absorption and scattering effects. , thus resulting in Raman scattered light being insensitive to changes in the concentration of the measured tissue components. A position with the above characteristics can be called a reference position (or a reference position). The Raman intensity of the Raman scattered light at the reference position reflects the response to disturbances other than the measured tissue composition during the measurement. At the same time, for the measured tissue component, there is also a certain position from the center of the incident light, at which the Raman intensity of the Raman scattered light has a sensitivity to the concentration change of the measured tissue component greater than or equal to the sensitivity threshold. A position having the above characteristics can be called a measurement position. The Raman intensity of the Raman scattered light at the measurement location reflects the response to the measured tissue component during the measurement process, as well as the response to other disturbances other than the measured tissue component. Also, the reference position and the measurement position vary depending on the wavelength, the object to be measured, and the measurement area, and thus the reference position can be called a floating reference position.

According to the embodiments of the present disclosure, since the Raman intensity of the Raman scattered light emitted at the floating reference position mainly carries the response to other disturbances other than the measured tissue components in the measurement process, it is possible to The Raman intensity of the outgoing Raman scattered light is introduced into the differential measurement to minimize common-mode interference and minimize the loss of useful information. Based on the above, when the measurement area of the measured object is determined, for the second preset wavelength, the source-detection distance of at least one of the M photosensitive surfaces from the center of the incident light is in the range corresponding to the second preset wavelength. The preset source-detection distance range is determined according to the source-detection distance from the floating reference position corresponding to the second preset wavelength to the center of the incident light. In the embodiment of the present disclosure, the source detection distance of each photosensitive surface of the first same type of photosensitive surface from the center of the incident light may be within a preset source detection distance range corresponding to the second preset wavelength.

Exemplarily, for example, for the measurement area B of the measured object A, the distance between the floating reference position corresponding to the second preset wavelength λ ₁ and the center of the incident light is 1.7 mm, then the distance corresponding to the second preset wavelength λ ₁ is 1.7 mm. The preset source detection distance range may be 1.5mm to 1.9mm.

Based on the above, the same type of photosensitive surface corresponding to the reference position and the same type of photosensitive surface corresponding to the measurement position can be determined, and the Raman intensity collected by the same type of photosensitive surface corresponding to the reference position is called the first Raman intensity. The Raman intensity collected by the same photosensitive surface corresponding to the measurement area is called the second Raman intensity. Alternatively, the Raman intensity collected by the same type of photosensitive surface corresponding to the measurement area is called the first Raman intensity, and the Raman intensity collected by the same type of photosensitive surface corresponding to the reference position is called the second Raman intensity.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength may include the following operations.

The third Raman intensity is determined from at least one Raman intensity corresponding to the second preset wavelength. According to the third Raman intensity corresponding to the second preset wavelength, the concentration of the measured tissue component is determined.

According to the embodiments of the present disclosure, a non-differential measurement method can be used to measure the tissue component, that is, the concentration of the measured tissue component can be determined according to the third Raman intensity corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, the third Raman intensity corresponding to the second preset wavelength is collected from the same photosensitive surface corresponding to the second preset wavelength, and different photosensitive positions of each photosensitive surface in the same photosensitive surface receive The difference between the average optical path length of the obtained Raman scattered light and the optimal optical path length corresponding to the second preset wavelength belongs to the second optical path difference range.

According to the embodiments of the present disclosure, in order to improve the possibility of acquiring a real measured tissue component signal, when the measurement area of the measured object is determined, for the second preset wavelength, the third Raman intensity can be used to collect the third Raman intensity. The average optical path length of the Raman scattered light received at different photosensitive positions in the same photosensitive surface is close to the optimal optical path corresponding to the second preset wavelength, that is, the same photosensitive surface used to collect the third Raman intensity is different in the same photosensitive surface. The absolute value of the difference between the average optical path length of the Raman scattered light received at the photosensitive position and the optimal optical path path corresponding to the second preset wavelength is less than or equal to the second optical path difference range. The optimal optical path length corresponding to the second preset wavelength can be understood as the optical path length corresponding to the maximum sensitivity of the measured tissue component under the second preset wavelength.

According to an embodiment of the present disclosure, each Raman intensity is obtained by processing according to the light intensity value of the Raman scattered light collected by one or more photosensitive surfaces, which may include the following operations.

Combine one or more photosensitive surfaces to output a Raman intensity. When each photosensitive surface of one or more photosensitive surfaces is used independently, a Raman intensity is obtained by calculating the light intensity value of the Raman scattered light collected by each photosensitive surface.

According to an embodiment of the present disclosure, a photosensitive surface for outputting one Raman intensity is referred to as a similar photosensitive surface, and a similar photosensitive surface may include one or more photosensitive surfaces. Wherein, the condition for the combined use of different photosensitive surfaces may be that the average optical path of the Raman scattered light received by each photosensitive surface is within the range of the average optical path. The average optical path range may be a range consisting of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to the optical path average value and the optical path variation amplitude. The average optical path length is the average value calculated from the average optical path length of the Raman scattered light received by each photosensitive surface of the same type of photosensitive surface.

The photosensitive surface is usually used in conjunction with the amplifier circuit corresponding to the photosensitive surface to output a light intensity value. In order to enable the same photosensitive surface to output more accurate Raman intensity, the product of the photoresponsivity of each photosensitive surface in the same photosensitive surface and the magnification of the amplification circuit used with the photosensitive surface needs to be the same preset value. Ensure that the photoresponsivity of each photosensitive surface and the magnification of the amplifying circuit used in conjunction with the photosensitive surface are the same preset value, so that the same photosensitive surface can output a Raman intensity. If the product of the photoresponsivity of the photosensitive surface and the magnification of the amplifying circuit used in conjunction with the photosensitive surface is not the same preset value, a corresponding method needs to be taken to make the product a preset value.

The same type of photosensitive surface can output a Raman intensity by means of hardware or software.

The first method is the hardware method. The cathodes of different photosensitive surfaces of the same photosensitive surface can be electrically connected to each other and the anodes of the same photosensitive surfaces can be electrically connected to each other, that is, the electrical connection of common cathode and common anode between different photosensitive surfaces can be realized. In this case, it is equivalent to connecting different photosensitive surfaces in parallel, so that one or more photosensitive surfaces are used in combination to output one Raman intensity. It should be noted that it is necessary to ensure that the photoresponsivity of different photosensitive surfaces is consistent as much as possible, so as to obtain a more accurate Raman intensity.

The second method is the software method. The cathodes between different photosensitive surfaces in the same photosensitive surface are not connected to each other and the anodes are not connected to each other, that is, each photosensitive surface is used alone to output a light intensity value. After the light intensity value corresponding to each photosensitive surface is obtained, a corresponding algorithm can be used to perform a weighted summation of the light intensity values of each photosensitive surface in the same photosensitive surface to obtain a Raman intensity.

Optionally, the Raman intensity corresponding to the same type of photosensitive surface can be determined by the following formulas (2) and (3).

Among them, I represents the Raman intensity corresponding to the same photosensitive surface, I _i represents the light intensity value corresponding to the photosensitive surface i, i∈{1,2,...,N-1,N},N Indicates the number of photosensitive surfaces included in the same photosensitive surface, 1≤N≤M, M denotes the total number of photosensitive surfaces, α _i denotes the weighting coefficient corresponding to the photosensitive surface i, H denotes the preset value, β _i denotes the photosensitive surface i The corresponding photoresponsivity, γ _i represents the magnification of the amplifier circuit used in conjunction with the photosensitive surface i.

According to an embodiment of the present disclosure, irradiating the measurement area with the incident light of the first preset wavelength may include the following operations.

Under the condition that the reproducibility of the controllable measurement conditions is satisfied, the measurement area is illuminated with the incident light of the first preset wavelength.

According to the embodiments of the present disclosure, during tissue composition measurement, changes in measurement conditions may overwhelm weak tissue composition signals, making it difficult to obtain the real measured tissue composition signals, and having a greater impact on measurement results.

For the controllable measurement conditions, because the changes of the controllable measurement conditions have different mechanisms for affecting the measurement results, it is difficult to suppress their influence on the measurement results by using mathematical algorithms. The method of controlling the reproducibility of the measurement conditions, so that the influence of the controllable measurement conditions on the measurement results can be reduced to a negligible level, that is, the influence of the changes of the controllable measurement conditions on the measurement results is equal to the influence of random noise on the measurement results. . Among them, the effective control method is not a mathematical algorithm, which can be implemented with hardware design. The reproducibility of the controllable measurement conditions may refer to maintaining the controllable measurement conditions within a preset variation range during each tissue composition measurement, so that the controllable measurement conditions remain unchanged or substantially unchanged.

Based on the above, in order to improve the possibility of obtaining the real measured tissue component signal, the inventor found that for the processing of controllable measurement conditions, a reasonable processing method is to use an effective control method to control it to achieve its reproducibility.

According to the embodiments of the present disclosure, the use of an effective control method to control the controllable measurement conditions can reduce the influence of changes in the controllable measurement conditions on the measurement results to a negligible level, thereby avoiding complex mathematical algorithms for processing , thereby improving the possibility of obtaining the real measured tissue component signal, and also reducing the difficulty of data processing and the amount of data processing.

According to an embodiment of the present disclosure, the method may further include the following operations.

Identify work features. From the positioning features, a measurement area is determined, wherein the measurement area is an area that satisfies the reproducibility of the controllable measurement conditions. Set the measuring probe to the position corresponding to the measuring area.

According to the embodiments of the present disclosure, in the embodiments of the present disclosure, the measurement posture reproducibility and the measurement area reproducibility are mainly aimed at. The measurement posture refers to the posture of the limb supporting the measurement site. And in the related art, no relevant content for measuring posture is found.

One is to measure the regional reproducibility. The positioning deviation of the measurement area is caused by the non-uniformity of tissue distribution and the difference in the flat state of the skin surface. When the relative position between the measurement probe and the measurement area is deviated, the transmission path of light in the tissue will be changed. It can be seen that in order to achieve the reproducibility of the controllable measurement conditions, it is necessary to ensure the reproducibility of the measurement area as much as possible.

Second, measure postural reproducibility. In the measurement of tissue components, it is difficult for the measured object to keep the same measurement posture, and the change of the measurement posture will lead to changes in the state of the skin in the measurement area, which in turn leads to changes in the transmission path of light in the tissue. Therefore, the measurement posture changes. Positioning errors will occur and affect the reliability of the measurement results. The skin state may include the shape of the skin surface and the internal structure of the skin. It can be seen that it is necessary to achieve the reproducibility of the measurement posture. The purpose of the measurement posture positioning is to make the measurement posture when the tissue component measurement is performed as the target measurement posture, that is, when the tissue component measurement is performed, if the current measurement posture is not the target measurement posture, then the current measurement posture needs to be adjusted to the target measurement posture, The target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement conditions.

But in fact, the importance of achieving the reproducibility of measured poses is often overlooked, which is reflected in the following two aspects.

First, the reproducibility of measurement posture was not found to be an important factor affecting the acquisition of real measured tissue composition signals. In the related art, it is generally believed that in terms of controllable measurement conditions, the reason that affects the reproducibility of the controllable measurement conditions is the reproducibility of the measurement area, that is, if the reproducibility of the measurement area is achieved, it is possible to improve the accuracy of the controllable measurement conditions. The possibility of the measured tissue composition signal without considering other reasons. In other words, in the related art, the improvement direction revolves around how to improve the positioning accuracy of the measurement area, and it is not found that in terms of controllable measurement conditions, the reproducibility of the measurement posture is also the possibility of obtaining the real measured tissue composition signal. an important reason.

In addition, according to the above analysis, even if the reproducibility of the measurement area is achieved, when the posture of the limb supporting the measurement site changes, the internal structure of the skin at the measurement area will also change, resulting in the transmission path of light in the tissue. Variations, therefore, also affect the reliability of the measurement results. In other words, only ensuring the reproducibility of the measurement area and ignoring the reproducibility of the measurement posture is not conducive to improving the possibility of acquiring the true measured tissue component signal.

Second, there is no effective way to achieve measurement posture reproducibility. Since the factors affecting the acquisition of the real measured tissue composition signal have not been studied in depth, the importance of achieving the reproducibility of the measurement posture has not been recognized. Therefore, in the tissue composition measurement, it is considered that the measurement of the subject itself by keeping the body stable. In this way, the control of the measurement posture can be realized, that is, if the measured object thinks that its body state has not changed, the measurement posture is well controlled. However, in most cases, the change of the measurement posture cannot be perceived by the measured object. Therefore, the error of this method of realizing the reproducibility of the measurement posture is large, which will cause great disturbance to the measurement result. That is, even if a method is adopted to control the measurement posture, since the importance of realizing the reproducibility of the measurement posture is not recognized, this method cannot substantially guarantee the reproducibility of the measurement posture.

It can be seen that in order to achieve the reproducibility of the measurement area, it is necessary to ensure the reproducibility of the measurement posture as much as possible, that is, to achieve accurate positioning of the measurement posture. Based on the above, the reproducibility of the measurement area needs to be premised on the reproducibility of the measurement posture, and therefore, the positioning of the measurement area needs to be premised on the positioning of the measurement posture.

During the positioning process, the positioning can be carried out according to the positioning features. The positioning feature may include a posture positioning feature and an area positioning feature, the posture positioning feature is used for positioning the measurement posture, and the area positioning feature is used for positioning the measurement area. The posture positioning feature can be set on the measured object or the non-measured object, the regional positioning feature can be set on the measured object or the non-measured object, and the non-measured object can include a measuring probe or other devices. The positioning features may include artificially set positioning features or inherent features on the measured object, wherein the inherent features on the measured object may include palm prints, fingerprints, birthmarks, moles or scabs, and the like.

According to the embodiment of the present disclosure, if the positioning feature is set manually, since the positioning feature set manually usually fades gradually over time, it needs to be set again, which may introduce new errors and affects the positioning accuracy. The inherent characteristics of the measured object have good stability, and it is not easy to generate setting errors.

In order to reduce the complexity of the positioning and improve the positioning accuracy, a setting method in which the inherent features on the measured object are used as the positioning features can be adopted. However, even if the inherent feature on the measured object is used as the setting method of the posture positioning feature, the internal structure of the skin will be affected by the change of the measurement posture, which will also cause the positioning deviation of the measurement area. The position on the object is not arbitrary, and needs to be determined according to the measurement site and the bone-muscle relationship between the measurement site and the surrounding site. Exemplarily, for example, the measurement site is the extensor side of the forearm, and its peripheral site includes the wrist. For the forearm extension side, since the change of the wrist state will greatly affect the skin condition of the forearm extension side, in order to improve the positioning accuracy, positioning features can be set on the forearm extension side and the back of the hand respectively. It should be noted that, if there is no inherent feature that can be used as the positioning feature, the positioning feature can be set manually. Exemplarily, for example, the positioning feature may be a dot-shaped mark point or a graphic mark point, and the graphic mark point may include a cross mark point.

According to an embodiment of the present disclosure, the positioning features include a first gesture positioning feature and an area positioning feature.

Determining the measurement area according to the positioning feature may include the following operations.

According to the first posture positioning feature, the current measurement posture of the measured object is adjusted to a target measurement posture, wherein the target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement condition. When the current measurement posture is the target measurement posture, the measurement area is determined according to the area positioning feature.

According to the embodiments of the present disclosure, when positioning the measurement posture and the measurement area, the premise of realizing the positioning of the measurement area is to realize the positioning of the measurement posture, and in the subsequent measurement process after the positioning of the measurement area is completed, usually the measurement area does not need to be positioned again. , there may also be situations where measurement pose positioning is required. The condition for completing the positioning of the measurement posture is that the current measurement posture is the target measurement posture, and the target measurement posture is the measurement posture that satisfies the reproducibility of the controllable measurement conditions.

According to the embodiment of the present disclosure, the reason why the above-mentioned situation that measurement posture positioning is required is that, in the embodiment of the present disclosure, in order to bring a better user experience to the measured object, a non-measurement method can be used. When measuring, the measurement position is allowed to move within a certain range, and the measurement posture is positioned during measurement. When measuring, it is necessary to ensure that the current measurement posture is the target measurement posture. Therefore, if the current measurement posture is not the target measurement posture, it is necessary to Adjust the measurement posture to ensure that the current measurement posture is the target measurement posture.

Based on the above, the positioning can be divided into the positioning of the first measurement posture, the positioning of the measurement area, and the positioning of the second measurement posture. Wherein, the positioning of the first measurement posture can be understood as the measurement posture positioning of the measurement area in cooperation. The re-measurement posture positioning can be understood as the measurement posture positioning performed when the measurement probe is set after the position corresponding to the measurement area and the measurement posture is not the target measurement posture.

According to an embodiment of the present disclosure, the area location feature is used to perform measurement area location. The posture localization feature adopted for the first measurement of posture localization is referred to as the first posture localization feature. The posture location feature used to measure the posture location again is referred to as the second posture location feature. The region location feature, the first gesture location feature, and the second gesture location feature may all be the same, partially the same, or all different. The number of area location features, first gesture location features, and second gesture location features may include one or more.

During the first measurement posture positioning and measurement area positioning, the current measurement posture of the measured object can be adjusted according to the first posture positioning feature so that the first posture positioning feature matches the preset feature, and the first posture positioning feature matches the preset feature. In the case of feature matching, it can be determined that the current measurement posture is the target measurement posture. When the current measurement posture is the target measurement posture, the measurement area is determined according to the area positioning feature. Thus, the positioning of the measurement posture and the measurement area is completed.

It should be noted that, determining the measurement area according to the regional positioning feature may be understood as determining the area corresponding to the regional positioning feature as the measurement area, which includes determining the area where the regional positioning feature is located as the measurement area. Or another area having an associated relationship with the area positioning feature is determined as the measurement area.

By locating the feature according to the first posture and the region locating feature, the positioning of the measurement area and the positioning of the measurement posture are realized synchronously.

According to an embodiment of the present disclosure, disposing the measurement probe at a position corresponding to the measurement area may include the following operations.

The measuring probe is arranged at a position corresponding to the measurement area by the fixing part, wherein the fixing part and the measuring probe are integrated, partially separated or completely separated.

According to an embodiment of the present disclosure, the fixing part is used to fix the measuring probe, and the fixing part and the measuring probe may be integrated, partially or completely independent, that is, the fixing part may be used as a component of the measuring probe, and may be mutually connected with the measuring probe. The two independent parts can also be part of the measuring probe, and the other part and the measuring probe are independent parts. The fixing part may include a fixing seat and a first fitting, or the fixing part may comprise a second fitting. The first matching piece is used for setting the fixing base at a position corresponding to the measurement area, and the fixing base is used for setting the measuring probe. The second fitting is used to set the measurement probe at a position corresponding to the measurement area.

If the fixing part includes a fixing base and a first fitting, the fixing base and the measuring probe are separate, and the first fitting and the fixing base are integrated or separate. If the fixing part includes the second fitting, the second fitting and the measuring probe are integral or separate.

According to an embodiment of the present disclosure, the fixing part includes a fixing seat and a first fitting part. Setting the measurement probe at a position corresponding to the measurement area by the fixing portion may include the following operations.

The fixing base is arranged at a position corresponding to the measurement area through the first matching piece. Set the measuring probe to the holder.

According to an embodiment of the present disclosure, the measurement probe is not directly disposed at the position corresponding to the measurement area, but is disposed at the position corresponding to the measurement area through the fixing seat.

In the process of tissue composition measurement, if the measurement probe is set at the position corresponding to the measurement area through the fixing seat, since the fixing seat can be set in the measurement area for a long time without departing from the measurement area, the measurement probe can be set during measurement. It is attached to the fixed seat, and it is separated from the fixed seat during non-measurement. In addition, since the fixing base is arranged at a position corresponding to the measurement area, when the measuring probe is separated from the fixing base and then installed on the fixing base, a good positioning accuracy can still be maintained, and the positioning difficulty of the measuring probe is reduced.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the first preset condition during the process of setting the fixing seat at the position corresponding to the measurement area by the first fitting.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the second preset condition during the process of disposing the measurement probe on the fixing seat.

According to the embodiments of the present disclosure, since the action of fixing the fixing seat will affect the skin condition of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the first fitting During the process of fixing the fixing base, it is ensured that the skin state of the skin at the measurement area satisfies the first preset condition. Wherein, the first preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the fixing seat by the first fitting member within the first preset range. Changes in skin condition can include skin deformation. Correspondingly, the first preset range may include the first preset deformation range.

According to the embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin condition of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, therefore, in order to ensure the positioning accuracy of the measurement area, the fixing seat can be fixed During the process of measuring the probe, it is ensured that the skin state of the skin in the measurement area satisfies the second preset condition. Wherein, the second preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the measurement probe on the fixing base within the second preset range. Changes in skin condition can include skin deformation. Correspondingly, the second preset range may include a second preset deformation range.

According to an embodiment of the present disclosure, the measurement probe does not move in the holder.

According to the embodiments of the present disclosure, when the measurement probe is fixed on the fixing base, the problem of affecting the reproducibility of the measurement conditions also occurs due to the weak fixing. In order to solve this problem, it can be ensured as far as possible that the measurement probe does not move in the fixed seat during the tissue composition measurement process.

According to an embodiment of the present disclosure, the fixing part includes a second fitting. Setting the measurement probe at a position corresponding to the measurement area by the fixing portion may include the following operations.

The measurement probe is set at a position corresponding to the measurement area through the second fitting.

According to the embodiments of the present disclosure, for the manner in which the measurement probe is arranged at the position corresponding to the measurement area, in addition to the above-mentioned method of arranging the measurement probe at the position corresponding to the measurement area through the fixing seat, a direct The method of disposing the measuring probe at the position corresponding to the measuring area does not require a fixing seat, but requires the cooperation of the second fitting.

It should be noted that the above-mentioned need of no fixing seat may include the following two understandings. First, the measuring probe is provided with a structure integral with it, which plays the same role as the independent fixing seat. Second, the measuring probe is not provided with a structure that plays the same role as the independent fixing seat.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the third preset condition during the process of setting the measurement probe at the position corresponding to the measurement area through the second fitting.

According to the embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin state of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the second fitting can be made During the process of fixing the measurement probe, it is ensured that the skin state of the skin at the measurement area satisfies the third preset condition. Wherein, the third preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the measurement probe by the second fitting member within the third preset range. Changes in skin condition can include skin deformation. Correspondingly, the third preset range may include a third preset deformation range.

According to an embodiment of the present disclosure, determining the measurement area according to the area positioning feature may include the following operations.

Get the first projected feature. In the case where it is determined that the regional positioning feature does not match the first projected feature, the position of the measuring probe and/or the fixing portion is adjusted until the regional positioning feature matches the first projected feature. When it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe and/or the fixing portion is determined as the measurement region.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the positioning of the measurement area, an optical method can be used, that is, the area positioning feature is matched with the first projection feature, and the measurement area is determined according to the matching result, wherein the first The projection feature is formed according to an optical method, that is, a light spot of a preset shape is projected by the light source, and the shape of the light spot can be determined according to the regional positioning feature. Exemplarily, the light spot with the preset shape is a cross light spot.

After the first projection feature is obtained, it is determined whether the regional positioning feature matches the first projection feature. If it is determined that the regional positioning feature does not match the first projection feature, the positions of the measuring probe and the fixing part can be adjusted so that the regional positioning feature does not match the first projection feature. Match with the first projected feature until the region location feature matches the first projected feature. When it is determined that the region positioning feature matches the first projection feature, it can be stated that the region where the measurement probe and the fixing part are currently located is the measurement region.

After the first projection feature is obtained by using the structure for projecting the first projection feature, it is determined whether the region positioning feature matches the first projection feature. /or the position of the fixing seat so that the area positioning feature matches the first projected feature until the area positioning feature matches the first projected feature. In the case where it is determined that the region positioning feature matches the first projection feature, it can be indicated that the region where the measurement probe and/or the fixing base are currently located is the measurement region.

According to an embodiment of the present disclosure, the structure for projecting the first projection feature may be provided on the object to be measured, the measurement probe, the holder, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. The adjustment process based on the optical method will be described below from two perspectives, the setting position of the structure for projecting the first projection feature and the setting position of the regional positioning feature.

Described from the perspective of the setting position of the structure for projecting the first projected feature.

First, if the structure for projecting the first projection feature is arranged on the object to be measured, the area positioning feature can be arranged on at least one of the object to be measured, the measuring probe, the fixed seat and other objects. It should be noted that, if the regional positioning feature is set on the object to be measured or other objects, the positioning of the measurement region can be achieved by the following methods, that is, according to the regional positioning feature and the first projection feature, the position of the measuring probe and/or the fixed seat is adjusted. , until the regional positioning feature matches the first projection feature. The matching of the regional positioning feature and the first projection feature here means that the regional positioning feature is blocked by the measuring probe and/or the fixed seat, so that the first projection feature cannot be projected to the region. The location of the work feature. If the region positioning feature does not match the first gesture positioning feature, there is at least one first projection feature that can be projected to the location where the region positioning feature is located.

Second, if the structure for projecting the first projection feature is provided on the measuring probe, the regional positioning feature cannot be set on the measuring probe, but can be set on the object to be measured, the holder or other objects. It should be noted that, if the area positioning feature is set on the fixed seat, and the positioning of the measuring probe is realized by setting the measuring probe at the position corresponding to the measuring area through the fixing part provided with the fixed seat, then in order to be able to realize the positioning of the measuring probe. The positioning of the measurement area can be achieved by adjusting the position of the fixed seat. Before the matching of the regional positioning feature and the first projection feature is achieved, the position of the measuring probe is fixed. According to the regional positioning feature and the first projection feature, the position of the fixing seat is adjusted until the regional positioning feature matches the first projection feature. , in the case of matching the two, the area corresponding to the fixed seat is determined as the measurement area, so that the measurement probe can be set on the fixed seat.

Thirdly, if the structure for projecting the first projection feature is set on the fixed seat, the regional positioning feature cannot be set on the fixed base, but can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the area positioning feature is provided on the measurement probe, and the measurement probe is positioned by setting the measurement probe at the position corresponding to the measurement area through the fixing part provided with the fixing seat, then in order to be able to realize the positioning of the measurement probe. The positioning of the measurement area can be achieved by adjusting the position of the fixed seat. Before the matching of the regional positioning feature and the first projection feature is achieved, the position of the measuring probe is fixed. According to the regional positioning feature and the first projection feature, the position of the fixing seat is adjusted until the regional positioning feature matches the first projection feature. , in the case of matching the two, the area corresponding to the fixed seat is determined as the measurement area, so that the measurement probe can be set on the fixed seat.

Fourth, if the structure for projecting the first projection feature is set on other objects, the area positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the regional positioning feature is set on the measured object or other objects, the structure used to project the first projection feature can be set on the measured object, and the regional positioning feature is set on the measured object or other objects. The positioning of the measurement area is implemented in a similar manner, which will not be repeated here.

From the perspective of the setting position of the regional positioning feature.

First, if the area positioning feature is set on the object to be measured, the structure for projecting the first projection feature can be set on the object to be measured, a measuring probe, a fixed seat or other objects. It should be noted that, if the structure for projecting the first projection feature is set on the object to be measured or other objects, the positioning of the measurement area can be achieved by the following methods, that is, according to the area positioning feature and the first projection feature, adjust the measurement probe and / or the position of the fixed seat, until the regional positioning feature matches the first projection feature, and the matching of the regional positioning feature with the first projected feature here means that the regional positioning feature is blocked by the measuring probe and/or the fixed seat, so that the first The projected feature cannot be projected to the location where the area work feature is located. If the region positioning feature does not match the first gesture positioning feature, there is at least one first projection feature that can be projected to the location where the region positioning feature is located.

Second, if the area positioning feature is set on the measuring probe, the structure for projecting the first projection feature is separate from the measuring probe, and can be set on the object to be measured, the holder or other objects. It should be noted that, if the structure for projecting the first projection feature is disposed on the fixed seat, the description in the corresponding part above can be referred to, and details are not repeated here.

Thirdly, if the area locating feature is set on the fixing base, the structure for projecting the first projection feature is separate from the fixing base, and can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the structure for projecting the first projection feature is disposed on the measurement probe, reference may be made to the description in the corresponding part above, which will not be repeated here.

Fourth, if the regional positioning feature is set on other objects, the structure for projecting the first projection feature can be set on the object to be measured, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the first projection feature is provided on the object to be measured or other objects, reference may be made to the description in the corresponding part above, and details are not repeated here.

Exemplarily, FIG. 6 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure. The area locating feature in Figure 6 is provided on the measurement probe. FIG. 7 schematically shows a schematic diagram of another implementation of positioning the measurement area based on an optical method according to an embodiment of the present disclosure. In Figure 7, the regional positioning feature is set on the measured object.

The positioning of the measurement area is realized by the optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the regional positioning feature. Therefore, the regional positioning feature can be set flexibly, thereby reducing the setting of the regional positioning feature. difficulty. On the other hand, by adjusting the shape of the Raman scattering spot, the matching with the regional positioning features can be better achieved, and the positioning accuracy can be improved.

According to an embodiment of the present disclosure, determining the measurement area according to the area positioning feature may include the following operations.

Acquire the first target image. A first template image is acquired, wherein the first template image includes regional positioning features. If it is determined that the first target image does not match the first template image, adjust the position of the measuring probe and/or the fixing part to acquire a new first target image until the new first target image matches the first template image . When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe and/or the fixing portion is determined as a measurement area.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the positioning of the measurement area, an image matching method can be used, that is, the first target image is matched with the first template image, and the measurement area is determined according to the matching result. Wherein, the first template image may include a region positioning feature, and the position of the region positioning feature in the first template image is a preset position. In the process of matching the first target image with the first template image, the first target image may be a target image that does not include regional positioning features, or may include regional positioning features but the position of the regional positioning features in the first target image is not The target image at the preset position may also be a target image including a region positioning feature and the position of the region positioning feature in the first target image is a preset position. Since the first template image includes the region positioning feature at the preset position, if the first target image matches the first template image, it can be said that the first target image includes the region positioning feature and the region positioning feature is in the first target image is the default position. In other words, the purpose of matching the first target image with the first template image is to make the acquired first target image include regional positioning features and the positions of the regional positioning features in the first target image are preset positions.

According to the embodiment of the present disclosure, when it is determined that the first target image matches the first template image, it can be stated that the area where the measurement probe and the fixing part are currently located is the measurement area. Wherein, determining whether the first target image matches the first template image may include determining the similarity between the first target image and the first template image. When the similarity is greater than or equal to the similarity threshold, it is determined that the first target image matches the first template image. In the case that the similarity is less than the similarity threshold, it is determined that the first target image does not match the first template image. Determining the similarity between the first target image and the first template image may include performing a correlation analysis on the first target image and the first template image to obtain a correlation coefficient, and determining the similarity between the first target image and the first template image according to the correlation coefficient.

According to an embodiment of the present disclosure, the structure for acquiring the first target image may be disposed on the object to be measured, the measurement probe, the fixed seat, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. For the description of the structure and the region positioning feature used for acquiring the first target image, reference may be made to the description of the structure and region positioning feature used for projecting the first projection feature, and details are not repeated here. The difference is that if the structure for acquiring the first target image is provided on the measuring probe, the area positioning feature may be provided on at least one of the object to be measured, the measuring probe, the holder and other objects. If the structure for capturing the first target image is provided on the mount, the area positioning feature may be provided on at least one of the object to be measured, the measurement probe, the mount, and other objects.

Exemplarily, FIG. 8 schematically shows a schematic diagram of positioning a measurement area based on an image matching method according to an embodiment of the present disclosure. The area locating feature in Figure 8 is provided on the measuring probe. FIG. 9 schematically shows a schematic diagram of realizing the positioning of the measurement area based on another image matching method according to an embodiment of the present disclosure. In Figure 9, the regional positioning feature is set on the measured object.

According to an embodiment of the present disclosure, determining the measurement area according to the area positioning feature may include the following operations.

A second target image is acquired, wherein the second target image includes regional localization features. In the case where it is determined that the position of the regional positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe and/or the fixing part to acquire a new second target image until the new second target image The position of the positioning feature in the middle area is the first preset position. When it is determined that the position of the area positioning feature in the new second target image is the first preset position, the area corresponding to the measurement probe and/or the fixing part is determined as the measurement area.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement area positioning, an imaging method can be used to achieve, that is, if the position of the area positioning feature in the second target image is the first preset position, it can be indicated that the completion of location of the measurement area.

According to the embodiment of the present disclosure, the process of using the imaging method to realize the measurement area positioning is the process of determining whether the position of the area positioning feature in the second target image is the first preset position. If the area positioning feature is in the second target image is not the first preset position, then the positions of the measuring probe and the fixing part can be adjusted to obtain a new second target image, until the position of the regional positioning feature in the new second target image is the first preset position . In the case where the position of the area positioning feature in the new second target image is the first preset position, it can be explained that the area where the measurement probe and the fixing part are currently located is the measurement area.

According to an embodiment of the present disclosure, the structure for acquiring the second target image may be provided on the object to be measured, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. For the description of the structure and the region positioning feature used for acquiring the second target image, reference may be made to the description of the structure and region positioning feature used for projecting the first projection feature, which will not be repeated here.

Exemplarily, FIG. 10 schematically shows a schematic diagram of positioning the measurement area implemented by an imaging method according to an embodiment of the present disclosure. The area locating feature in Figure 10 is provided on the measuring probe. FIG. 11 schematically shows a schematic diagram of implementing positioning of a measurement area based on another imaging method according to an embodiment of the present disclosure. In Figure 11, the area localization feature is set on the measured object. The movement of the measuring probe and the fixing base in FIG. 11 changes the relative positions of the two and the regional positioning feature, so that the position of the regional positioning feature presented in the image is located at the first preset position.

According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature may include the following operations.

Get the second projected feature. In the case where it is determined that the first posture locating feature does not match the second projection feature, the current measurement posture is adjusted until the first posture locating feature and the second projection feature match. When it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an optical method can be used to achieve, that is, the first posture positioning feature and the second projection feature are matched, and the target measurement posture is determined according to the matching result, wherein , the second projection feature is formed according to an optical method, that is, the second projection feature is formed by projecting a light spot of a preset shape by the light source, and the shape of the light spot can be determined according to the first posture positioning feature. That is, for the measured object, a second projection feature matching the first posture positioning feature is set according to the first posture positioning feature, so that the current measurement posture matching the first posture positioning feature and the second projection feature is the target measurement posture.

According to an embodiment of the present disclosure, the structure for projecting the second projection feature may be provided on the object to be measured, the measurement probe, the mount, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture positioning feature may be provided on at least one of the measurement probe, the fixed seat, the object to be measured, and other objects. The adjustment process based on the optical method will be described below from two angles of the setting position of the structure for projecting the second projection feature and the setting position of the first posture positioning feature.

Described from the perspective of the setting position of the structure for projecting the second projection feature.

First, if the structure for projecting the second projection feature is arranged on the measured object, the first posture positioning feature can be arranged on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the first posture positioning feature is provided on the measurement probe, in order to realize the positioning of the measurement posture, the position of the measurement probe needs to be fixed during the first measurement posture positioning stage. Similarly, if the first posture positioning feature is provided on the fixed seat, in order to realize the positioning of the measurement posture, it is necessary to make the position of the fixed seat be fixed during the first measurement posture positioning stage.

Second, if the structure for projecting the second projection feature is arranged on the measuring probe, the first posture positioning feature cannot be arranged on the measuring probe, but can be arranged on the object to be measured, the holder or other objects. It should be noted that the position of the measurement probe needs to be fixed in the first measurement posture positioning stage. In addition, if the first posture positioning feature is set on the fixed seat, the positioning of the first measurement posture can be realized by the following method, that is, according to the first posture positioning feature and the second projection feature, the current measurement posture of the measured object is adjusted until the first posture positioning feature and the second projection feature are adjusted. The posture positioning feature matches the second projection feature. The matching of the first posture positioning feature and the second projection feature here means that the first posture positioning feature is blocked by the measured object, so that the second projection feature cannot be projected to the first posture. The location of the work feature. If the first gesture location feature does not match the second gesture location feature, then there is at least one second projection feature that can be projected to the location where the first gesture location feature is located. If the first posture positioning feature is set on other objects, the positioning of the measurement posture can be implemented in a manner similar to that when the first posture positioning feature is set on the fixed seat, which will not be repeated here.

Third, if the structure for projecting the second projection feature is installed on the fixed seat, the first posture positioning feature cannot be installed on the fixed seat, but can be installed on the object to be measured, the measuring probe or other objects. It should be noted that, it is necessary to make the position of the fixed seat be fixed in the first measurement posture positioning stage. In addition, if the first posture positioning feature is provided on the measuring probe or other object, it can be used in a similar manner as the structure for projecting the second projection feature is provided on the measuring probe, and the first posture positioning feature is provided on the holder or other object The positioning of the measurement posture is realized, which is not repeated here.

Fourth, if the structure for projecting the second projection feature is set on other objects, the first posture positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the first posture positioning feature is set on the measuring probe, the fixed seat or other objects, the same structure as the structure used to project the second projection feature can be set on the measuring probe, and the first posture positioning feature is set on the fixed position. The positioning of the measurement posture can be achieved in a similar manner to a seat or other objects, which will not be repeated here.

From the perspective of the setting position of the first posture positioning feature.

First, if the first posture positioning feature is provided on the measured object, the structure for projecting the second projection feature can be provided on the measured object, a measuring probe, a fixed seat or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the measurement probe, it is required that the position of the measurement probe is fixed in the first measurement posture positioning stage. Similarly, if the structure for projecting the second projection feature is arranged on the fixed seat, it is necessary to make the position of the fixed seat be fixed during the first measurement of the posture positioning stage.

Second, if the first posture positioning feature is set on the measuring probe, the structure for projecting the second projection feature is separate from the measuring probe, and can be set on the object to be measured, the holder or other objects. It should be noted that, if the structure for projecting the second projection feature is disposed on the object to be measured, the holder or other objects, the description in the corresponding part above can be referred to, and details are not repeated here.

Thirdly, if the first posture locating feature is set on the fixed base, the structure for projecting the second projection feature is separate from the fixed base, and can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the object to be measured, the measuring probe or other objects, reference may be made to the description of the corresponding part above, and details are not repeated here.

Fourth, if the first posture positioning feature is set on other objects, the structure for projecting the second projection feature can be set on the measured object, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the object to be measured, the measuring probe, the fixed seat or other objects, the description of the corresponding part above can be referred to, and details are not repeated here.

Exemplarily, FIG. 12 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure. In FIG. 12 , the first posture positioning feature is set on the measured object.

The positioning of the measurement posture is realized by an optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the first posture positioning feature. Therefore, the first posture positioning feature can be flexibly set, thereby reducing the The difficulty of a pose localization feature setting. On the other hand, by adjusting the shape of the Raman scattering light spot, the matching with the first posture positioning feature can be better achieved, and the positioning accuracy can be improved.

According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature may include the following operations.

A third target image is acquired. A second template image is acquired, wherein the second template image includes the first gesture location feature. When it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image until the new third target image matches the second template image. When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an image matching method can be used, that is, the third target image is matched with the second template image, and the target measurement posture is determined according to the matching result. Wherein, the second template image may include a first posture positioning feature, and the position of the first posture positioning feature in the second template image is a preset position. In the process of matching the third target image with the second template image, the third target image may be a target image that does not include the first posture positioning feature, or may include the first posture positioning feature but the first posture positioning feature is in the third The position of the target image is not the target image at the preset position, and may also be a target image including the first posture positioning feature and the position of the first posture positioning feature in the third target image is the preset position. Since the second template image includes the first posture localization feature at the preset position, if the third target image matches the second template image, it can be explained that the third target image includes the first posture localization feature and the first posture localization feature The position in the third target image is a preset position. In other words, the purpose of matching the third target image with the second template image is to make the acquired third target image include the first posture positioning feature and the position of the first posture positioning feature in the third target image is predetermined set location.

According to the embodiment of the present disclosure, in the case where it is determined that the third target image matches the second template image, it can be stated that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the third target image may be provided on the object to be measured, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture positioning feature may be provided on at least one of the measurement probe, the fixed seat, the object to be measured, and other objects. For the description of the structure for acquiring the third target image and the first posture positioning feature, reference may be made to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here. The difference is that if the structure for acquiring the third target image is provided on the measuring probe, the first posture positioning feature may be provided on at least one of the measured object, the measuring probe, the fixing seat and other objects. If the structure for capturing the third target image is provided on the fixture, the first posture positioning feature may be provided on at least one of the object to be measured, the measurement probe, the fixture, and other objects.

Exemplarily, FIG. 13 schematically shows a schematic diagram of the positioning of the measurement posture implemented by an image matching method according to an embodiment of the present disclosure. In FIG. 13 , the first posture positioning feature is set on the object to be measured.

According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature may include the following operations.

A fourth target image is acquired, wherein the fourth target image includes the first gesture positioning feature. In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image until the first posture is positioned in the new fourth target image The location of the feature is at the second preset location. When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined as the target measurement posture.

According to the embodiments of the present disclosure, in order to ensure the flexibility of use and the accuracy of measuring posture positioning, an imaging method can be used, that is, if the position of the first posture positioning feature in the fourth target image is the second preset position, it can be It indicates that the positioning of the measurement pose is completed.

According to the embodiment of the present disclosure, the process of using the imaging method to measure the posture positioning is the process of determining whether the position of the first posture positioning feature in the fourth target image is the second preset position. The position in the four target images is not the second preset position, then the current measurement posture can be adjusted to obtain a new fourth target image, until the position of the first posture positioning feature in the new fourth target image is the second preset position set location. When the position of the first posture positioning feature in the new fourth target image is the second preset position, it can be explained that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the fourth target image may be disposed on the measured object, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture positioning feature may be provided on at least one of the measurement probe, the fixed seat, the object to be measured, and other objects. For the description of the structure for acquiring the fourth target image and the first posture positioning feature, reference may be made to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here.

Exemplarily, FIG. 14 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an imaging method according to an embodiment of the present disclosure. In FIG. 14 , the first posture positioning feature is set on the measured object.

According to an embodiment of the present disclosure, the method may further include the following operations.

If the measurement probe is set at a position corresponding to the measurement area, in a case where it is determined that the current measurement posture is not the target measurement posture, the second posture positioning feature is determined. According to the second posture positioning feature, the current measurement posture is adjusted to the target measurement posture.

According to an embodiment of the present disclosure, in a case where it is determined that the current measurement posture is not the target measurement posture, the re-measurement posture positioning described above needs to be performed. The current measurement posture may be adjusted according to the second posture positioning feature until the current measurement posture is the target measurement posture. The second gesture location feature may be the same as or different from the first gesture location feature.

According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature may include the following operations.

Get the third projected feature. If it is determined that the second posture locating feature does not match the third projection feature, the current measurement posture is adjusted until the second posture locating feature matches the third projection feature. When it is determined that the second posture positioning feature matches the third projection feature, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an optical method can be adopted, that is, the second posture positioning feature is matched with the third projection feature, and the target measurement posture is determined according to the matching result, wherein , the third projection feature is formed according to an optical method, that is, a light spot with a preset shape is projected by the light source to form the third projection feature, and the shape of the light spot can be determined according to the second posture positioning feature. That is, for the measured object, a third projection feature matching the second posture positioning feature is set according to the second posture positioning feature, so that the current measurement posture matching the second posture positioning feature and the third projection feature is the target measurement posture.

According to an embodiment of the present disclosure, the structure for projecting the third projection feature may be provided on the object to be measured, the measurement probe, the mount, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. The adjustment process based on the optical method will be described below from two angles of the setting position of the structure for projecting the third projection feature and the setting position of the second posture positioning feature.

Described from the perspective of the setting position of the structure for projecting the third projection feature.

First, if the structure for projecting the third projection feature is arranged on the measured object, the second posture positioning feature can be arranged on at least one of the measured object, the measuring probe, the fixed seat and other objects.

Second, if the structure for projecting the third projection feature is set on the measuring probe, the second posture positioning feature cannot be set on the measuring probe and the holder, but can be set on the measured object or other objects, because the After being set at the position corresponding to the measurement area, the probe head is set on the fixed seat.

Thirdly, if the structure for projecting the third projection feature is set on the fixed seat, the second posture positioning feature cannot be set on the measuring probe and the fixed base, but can be set on the measured object or other objects. It is also caused by the fact that after the measuring probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Fourth, if the structure for projecting the third projection feature is set on other objects, the second posture positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the second posture positioning feature is set on other objects, the positioning of the measurement posture can be realized by the following method, that is, when it is determined that the second posture positioning feature does not match the third projection feature, the current measurement posture is adjusted. , until the second posture positioning feature matches the third projection feature, and when it is determined that the second posture positioning feature matches the third projection feature, the current measurement posture is determined as the target measurement posture. The matching between the second posture positioning feature and the third projection feature mentioned here means that the second posture positioning feature is blocked by the measured object, so that the third projection feature cannot be projected to the position where the second posture positioning feature is located. If the matching of the positioning feature and the third projection feature does not match, there is at least one third projection feature that can be projected to the position where the second posture positioning feature is located.

From the perspective of the setting position of the second posture positioning feature.

First, if the second posture positioning feature is arranged on the object to be measured, the structure for projecting the third projection feature can be arranged on the object to be measured, a measuring probe, a fixed seat or other objects.

Second, if the second posture positioning feature is set on the measuring probe, the structure for projecting the third projection feature is separate from the measuring probe and the fixed seat, and can be set on the object to be measured or other objects. After the probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Thirdly, if the second posture positioning feature is set on the fixed seat, the structure for projecting the third projection feature is separate from the measuring probe and the fixed seat, and can be set on the measured object or other objects. It is also caused by the fact that after the measuring probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Fourth, if the second posture positioning feature is set on other objects, the structure for projecting the third projection feature can be set on the measured object, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the third projection feature is set on another object, please refer to the description of the corresponding part above, which will not be repeated here.

The positioning of the measurement posture is realized by an optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the second posture positioning feature. Therefore, the second posture positioning feature can be flexibly set, thereby reducing the The difficulty of setting the feature of the second pose location. On the other hand, by adjusting the shape of the Raman scattering light spot, the matching with the positioning feature of the second posture can be better achieved, and the positioning accuracy can be improved.

According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature may include the following operations.

A fifth target image is acquired. A third template image is acquired, wherein the third template image includes the second gesture location feature. When it is determined that the fifth target image does not match the third template image, the current measurement posture is adjusted to acquire a new fifth target image until the new fifth target image matches the third template image. When it is determined that the new fifth target image matches the third template image, the current measurement posture is determined to be the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an image matching method can be used, that is, the fifth target image is matched with the third template image, and the target measurement posture is determined according to the matching result. Wherein, the third template image may include the second posture positioning feature and the position of the second posture positioning feature in the third template image is a preset position. In the process of matching the fifth target image with the third template image, the fifth target image may be a target image that does not include the second posture positioning feature, or may include the second posture positioning feature but the second posture positioning feature is in the fifth target image. The position of the target image is not the target image at the preset position, and may also be a target image including the second posture positioning feature and the position of the second posture positioning feature is the preset position at the position of the fifth target image. Since the third template image includes the second gesture positioning feature located at the preset position, if the fifth target image matches the third template image, it can be explained that the fifth target image includes the second gesture positioning feature and the second gesture positioning feature The position in the fifth target image is a preset position. In other words, the purpose of matching the fifth target image with the third template image is to make the acquired fifth target image include the second posture positioning feature and the position of the second posture positioning feature in the fifth target image is a predetermined set location.

According to the embodiment of the present disclosure, in the case where it is determined that the fifth target image matches the third template image, it can be stated that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the fifth target image may be provided on the object to be measured, the measurement probe, the fixed seat or other objects. Other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. For the description of the structure for acquiring the fifth target image and the second posture positioning feature, reference may be made to the description of the structure for projecting the third projection feature and the second posture positioning feature, which will not be repeated here. The difference is that if the structure for acquiring the fifth target image is provided on the measurement probe, the second posture positioning feature may be provided on at least one of the measured object, the measurement probe, the fixed seat and other objects. If the structure for capturing the fifth target image is provided on the fixed seat, the second posture positioning feature may be provided on at least one of the measured object, the measurement probe, the fixed seat and other objects.

According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature may include the following operations.

A sixth target image is acquired, wherein the sixth target image includes the second gesture positioning feature. If it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position, adjust the current measurement posture to obtain a new sixth target image until the second posture is positioned in the new sixth target image The location of the feature is at the third preset location. When it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position, the current measurement posture is determined as the target measurement posture.

According to the embodiments of the present disclosure, in order to ensure the flexibility of use and the accuracy of measuring posture positioning, an imaging method can be used, that is, if the position of the second posture positioning feature in the sixth target image is the third preset position, it can be It indicates that the positioning of the measurement pose is completed.

According to the embodiment of the present disclosure, the process of using the imaging method to measure the posture positioning is the process of determining whether the position of the second posture positioning feature in the sixth target image is the third preset position. The position in the six target images is not the third preset position, then the current measurement posture can be adjusted to obtain a new sixth target image, until the position of the second posture positioning feature in the new sixth target image is the third preset position. set location. In the case where the position of the second posture positioning feature in the new sixth target image is the third preset position, it can be explained that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the sixth target image may be disposed on the object to be measured, the measurement probe, the fixed seat, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. For the description of the structure for acquiring the sixth target image and the second posture positioning feature, reference may be made to the description of the structure for projecting the third projection feature and the second posture positioning feature, which will not be repeated here.

According to an embodiment of the present disclosure, the method may further include the following operations.

Prompt information is generated, wherein the prompt information is used to prompt that the measurement posture positioning and/or the measurement area positioning is completed, and the form of the prompt information includes at least one of image, voice or vibration.

According to the embodiments of the present disclosure, in order for the user to know in time whether the positioning of the measurement posture and/or the positioning of the measurement area is completed, prompt information may be generated after the positioning of the measurement posture and/or the positioning of the measurement area is completed. Wherein, the specific expression form of the prompt information may include at least one of image, voice and vibration.

According to an embodiment of the present disclosure, the method may further include the following operations.

When it is determined that the fixing seat is installed at the position corresponding to the measurement area and the measurement probe is not installed in the fixing portion, the measurement probe is installed on the fixing seat. When it is determined that the fixing seat is not arranged at the position corresponding to the measurement area, the fixing seat is arranged at the position corresponding to the measurement area through the first fitting, and the measuring probe is arranged on the fixing seat.

According to the embodiment of the present disclosure, if the measurement probe is set at a position corresponding to the measurement area through the fixing seat, during the tissue composition measurement process, the fixing seat can be separated from the measurement area, and the measurement probe can be separated from the fixing seat. If the fixing base is not set at the position corresponding to the measurement area, the fixing base can be set at the position corresponding to the measurement area through the first fitting, and the measuring probe can be set at the fixing base. If the fixing base is set at the position corresponding to the measurement area and the measuring probe is not set on the fixing base, the measuring probe can be set at the fixing base.

Exemplarily, for short-term measurement at any time, the fixing base can be arranged at a position corresponding to the measurement area, the measuring probe can be separated from the fixing base, and the measuring probe can be arranged on the fixing base when measurement is required. For long-term measurement, the fixing seat can be separated from the measurement area, and the measuring probe can be separated from the fixing seat. When measurement is required, the fixing seat is set at the position corresponding to the measurement area through the first fitting, and the measuring probe is set on the fixing seat.

According to an embodiment of the present disclosure, the method may further include the following operations.

When it is determined that the measurement probe is not arranged at the position corresponding to the measurement area, the measurement probe is arranged at the position corresponding to the measurement area through the second fitting.

According to the embodiment of the present disclosure, if the measurement probe is directly set at the position corresponding to the measurement area, the measurement probe can be separated from the measurement area during the tissue composition measurement process, and the measurement probe can be set through the second fitting when measurement is required. at the position corresponding to the measurement area.

According to an embodiment of the present disclosure, the photosensitive surface is obtained by disposing a mask on the initial photosensitive surface, and the light transmittance of the mask is less than or equal to a light transmittance threshold.

According to an embodiment of the present disclosure, the shape of the mask is determined according to the jitter distribution of Raman scattered light.

According to the embodiments of the present disclosure, since a circular photosensitive surface or a square photosensitive surface is relatively common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while other shapes of the photosensitive surface usually need to be customized, the manufacturing process is more difficult, and the manufacturing cost is relatively low. Therefore, if it is limited by the production cost, the method of setting a mask plate on the initial photosensitive surface can be adopted, wherein the part of the initial photosensitive surface blocked by the mask plate is less than or equal to the light transmittance of the mask plate. The light transmittance threshold is difficult to receive the light intensity value.

Based on the above, the shape and position of the mask plate can be set according to the actual required shape and area, so as to obtain a photosensitive surface with a preset shape and area. Wherein, the actual required shape and area can be determined according to the jitter distribution of Raman scattered light.

Exemplarily, FIG. 15 schematically shows a schematic diagram of setting a mask plate on an initial photosensitive surface to obtain a photosensitive surface according to an embodiment of the present disclosure. In Figure 15, the initial photosensitive surface is a square photosensitive surface, and the photosensitive surface is a circular photosensitive surface.

According to the embodiment of the present disclosure, the intensity distribution of the light spot irradiated by the incident light to the measurement area is uniform.

According to the embodiments of the present disclosure, in order to enable the measured object to perform tissue composition measurement under more relaxed requirements, so as to better improve the possibility of obtaining a real measured tissue composition signal, it is possible to ensure that the incident light is irradiated to the measurement The intensity distribution of the light spot in the area is achieved in a uniform manner. At the same time, the more uniform the intensity distribution of the light spot irradiated by the incident light to the measurement area, the lower the requirement for the reproducibility of the controllable measurement conditions, and the better the effect of using the differential measurement method to suppress the influence of the uncontrollable measurement conditions on the measurement results. Therefore, the reliability of the measurement results can also be better guaranteed. In addition, since the measures to make the intensity distribution of the incident light spot on the measurement area uniform will attenuate the light energy of the incident light to a certain extent, and the tissue composition measurement requires that the light energy of the incident light cannot be too small, it is necessary to try to Under the condition that the intensity distribution of the incident light spot on the measurement area is uniform, the light energy attenuation of the incident light is as small as possible. In addition, if the incident light is realized by means of optical fiber transmission, the distribution of the incident light spot on the measurement area is uniform, and the adverse effect of fiber jitter on the measurement result is also reduced.

According to an embodiment of the present disclosure, the area of the light spot irradiated by the incident light to the measurement region is greater than or equal to the light spot area threshold.

According to the embodiments of the present disclosure, in order to enable the measured object to perform tissue composition measurement under more relaxed requirements, so as to better ensure the reliability of the measurement results, the area of the light spot irradiated by the incident light to the measurement area may be larger than or equal to the spot area threshold. At the same time, within a certain range, the larger the area of the light spot irradiated by the incident light to the measurement area, the lower the requirement for the reproducibility of the controllable measurement conditions, and the effect of using the differential measurement method to suppress the influence of the uncontrollable measurement conditions on the measurement results. The better, and therefore, the better the reliability of the measurement results can be guaranteed. The light spot area threshold can be set according to the actual situation, which is not specifically limited here. In addition, if the incident light is realized by optical fiber transmission, the area of the light spot irradiated by the incident light to the measurement area is greater than or equal to the light spot area threshold, which also reduces the adverse effect of fiber jitter on the measurement results.

It should be noted that, in order to improve the possibility of obtaining the real measured tissue component signal, the following three aspects need to be ensured as much as possible. First, it has the ability to perceive changes in the concentration of expected tissue components. Second, try to minimize the adverse effects of changes in uncontrollable measurement conditions on the measurement results. Second, try to ensure the reproducibility of the controllable measurement conditions. The technical solutions provided by the embodiments of the present disclosure ensure the above three aspects.

The measurement device for realizing tissue composition has the ability to sense the concentration change of the expected tissue composition, and achieves high stability and efficiency of receiving outgoing light by adopting a large-area photosensitive surface. In order to reduce the influence of uncontrollable measurement conditions on the measurement results, the differential measurement method is used. Aiming at controlling the controllable measurement conditions, it is realized by adopting an effective control method.

FIG. 16 schematically shows a block diagram of a Raman scattering-based tissue composition measurement device according to an embodiment of the present disclosure.

As shown in FIG. 16 , the tissue composition measurement device 1600 includes a light source module 1610 , an acquisition module 1620 and a processing module 1630 .

The light source module 1610 is used to illuminate the measurement area with incident light of the first preset wavelength, and the incident light of the first preset wavelength passes through the measurement area and then exits from the exit position to form at least one beam of Raman scattered light of the second preset wavelength, The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift.

The acquisition module 1620 is configured to acquire the Raman intensity corresponding to each beam of Raman scattered light acquired by the measurement probe 1640, wherein the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in tissue component concentration .

The processing module 1630 is configured to determine the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

According to the technical solutions of the embodiments of the present disclosure, by irradiating the measurement area with the incident light of the first preset wavelength, the incident light of the first preset wavelength passes through the measurement area and then exits from the exit position to form at least one beam of the second preset wavelength. For the Raman scattered light, the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift, and the Raman intensity corresponding to each Raman scattered light collected by the measuring probe is obtained, and set The tissue component measuring device with the measuring probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in the concentration of the tissue component, and determines the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength. Since the adopted tissue composition measuring device provided with a measuring probe has a signal-to-noise ratio level that can distinguish the expected tissue composition concentration change, the ability to perceive the expected tissue composition concentration change is realized, thereby improving the acquisition of the real measured tissue composition. signal possibilities.

According to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a time gating module, and the time gating module is used for shielding fluorescence interference.

According to an embodiment of the present disclosure, the same incident light is irradiated to different incident positions by a spectroscopic method.

According to an embodiment of the present disclosure, the measurement probe 1640 includes M photosensitive surfaces.

The acquisition module 1620 includes an acquisition unit. The acquisition unit is configured to acquire the light intensity values corresponding to each Raman scattered light collected by the M photosensitive surfaces, and obtain T Raman intensities, wherein each Raman intensity is collected according to one or more photosensitive surfaces. The total area of the same photosensitive surface is greater than or equal to the area threshold and the area of each photosensitive surface in the same photosensitive surface is continuous, the same photosensitive surface includes one or more photosensitive surfaces, the same photosensitive surface The plane is used to output a Raman intensity, 1≤T≤M, so that the tissue component measurement device has a level of signal-to-noise that satisfies the resolution of expected changes in tissue component concentration.

According to the embodiment of the present disclosure, each photosensitive surface can collect the light intensity value of the Raman scattered light emitted from the emission position within the preset anti-shake range corresponding to the photosensitive surface.

According to an embodiment of the present disclosure, the ratio of the average optical path of the Raman scattered light received by each photosensitive surface in the target tissue layer to the total optical path is greater than or equal to the proportional threshold, wherein the total optical path is the Raman scattered light in the The total distance traveled within the measurement area.

According to an embodiment of the present disclosure, the total area of the photosensitive surfaces of the same type is determined according to the tissue structure characteristics in the measurement area.

According to an embodiment of the present disclosure, the ratio of the area of each photosensitive surface to the photosensitive perimeter of the photosensitive surface is greater than or equal to the ratio threshold.

According to an embodiment of the present disclosure, the ratio threshold is greater than or equal to 0.04 mm.

According to an embodiment of the present disclosure, the photosensitive surface is in contact or non-contact with the surface of the measurement area.

According to an embodiment of the present disclosure, the distance of the photosensitive surface from the surface of the measurement area is less than or equal to the first distance threshold and the efficiency of the photosensitive surface to receive Raman scattered light is greater than or equal to the efficiency threshold.

According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of different photosensitive surfaces are the same or different.

According to an embodiment of the present disclosure, the non-ring-shaped photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

According to an embodiment of the present disclosure, the polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to an embodiment of the present disclosure, the same type of photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface.

According to an embodiment of the present disclosure, the same type of photosensitive surface is an annular photosensitive surface, including: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, including: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

According to an embodiment of the present disclosure, in the case where it is determined that the distance between the same type of photosensitive surface and the target site is greater than or equal to the second distance threshold, the same type of photosensitive surface includes a ring photosensitive surface, a fan ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface or Square photosensitive surface.

According to an embodiment of the present disclosure, when it is determined that the distance between the same type of photosensitive surface and the target site is less than or equal to the third distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of Raman scattered light.

According to an embodiment of the present disclosure, the jitter distribution of Raman scattered light includes a jitter distribution along a first direction and a jitter distribution along a second direction, the first direction and the second direction are perpendicular to each other, and the same photosensitive surfaces are along the first direction. The ratio of the length in one direction to the length of the same photosensitive surface in the second direction is determined according to the ratio of the jitter amplitude of the Raman scattered light in the first direction to the jitter amplitude of the Raman scattered light in the second direction, The Raman scattered light has the largest jitter in the first direction.

According to an embodiment of the present disclosure, the same type of photosensitive surface includes a rectangular photosensitive surface or an elliptical photosensitive surface, and the ratio of the length to the width of the rectangular photosensitive surface is determined according to the jitter amplitude of the Raman scattered light along the first direction and the Raman scattered light along the second direction. Determined by the ratio of the jitter amplitudes in the two directions, the ratio of the major axis to the minor axis of the elliptical photosensitive surface is based on the jitter amplitude of the Raman scattered light along the first direction and the jitter amplitude of the Raman scattered light along the second direction ratio is determined.

According to an embodiment of the present disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°.

According to the embodiment of the present disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°, so as to realize the diffusion measurement. According to the embodiments of the present disclosure, a suitable location of the photosensitive surface can be determined according to the wavelength characteristic and/or the measurement area characteristic, wherein the wavelength characteristic may include the penetration depth of the wavelength, and the measurement area characteristic may include the thickness of the measurement area. Optionally, it is generally possible to set the included angle between each part of the photosensitive surface and the direction of the corresponding incident light to be a preset angle.

Exemplarily, if the penetration depth of the wavelength is relatively deep and/or the thickness of the measurement area is relatively thin, the position of the photosensitive surface and the incident position of the corresponding incident light may be located on opposite sides of the measurement area. If the penetration depth of the wavelength is shallow and/or the thickness of the measurement area is thick, the position of the photosensitive surface can be set to be on the same side of the measurement area as the incident position of the corresponding incident light.

Exemplarily, FIG. 17 schematically shows a schematic diagram of a diffusion measurement according to an embodiment of the present disclosure. In Figure 17, the angle between the photosensitive surface C and the incident light is 90°, the position of the photosensitive surface D and the position of the incident light are located on the same side of the measurement area, and the position of the photosensitive surface E and the position of the incident light are located on the different side of the measurement area. side.

According to an embodiment of the present disclosure, the processing module 1630 includes a processing unit. The processing unit is configured to process at least one Raman intensity corresponding to the second preset wavelength based on the interference suppression method to determine the concentration of the measured tissue component.

According to an embodiment of the present disclosure, one or more photosensitive surfaces of the same type corresponding to the second preset wavelength exist in the M photosensitive surfaces, wherein the photosensitive surfaces of the same type are used to collect the first photosensitive surfaces corresponding to the second preset wavelength at different times. Raman intensity and/or second Raman intensity, the first Raman intensity is the systolic light intensity, the second Raman intensity is the diastolic light intensity, and the same photosensitive surface includes one or more photosensitive surfaces.

The processing unit is configured to determine the concentration of the measured tissue component according to the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, among the M photosensitive surfaces, there are a first photosensitive surface of the same type and a second photosensitive surface of the same type corresponding to the second preset wavelength, wherein the first photosensitive surface of the same type is used for collecting images corresponding to the second preset wavelength. the first Raman intensity of Multiple photosensitive surfaces.

The processing unit is configured to determine the concentration of the measured tissue component according to the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, the first and second similar photosensitive surfaces are the same same photosensitive surface, and the Raman scattered light received by the first similar photosensitive surface and the second similar photosensitive surface is incident light from different incident positions Incident is obtained by transmission.

According to an embodiment of the present disclosure, the first photosensitive surface of the same kind and the second photosensitive surface of the same kind are different photosensitive surfaces of the same kind.

According to the embodiment of the present disclosure, the average optical path of Raman scattered light received by different light-sensing positions of each light-sensing surface in the first same-type light-sensing surface belongs to the first average optical path range, wherein the first average optical path range is based on The first optical path average value is determined, and the first optical path average value is an average value calculated according to the average optical path lengths of the Raman scattered light received by each photosensitive position of the first photosensitive surface of the same type.

The average optical path lengths of the Raman scattered light received at different photosensitive positions on each photosensitive surface of the second same type of photosensitive surface belong to the second average optical path range, wherein the second average optical path range is determined according to the average value of the second optical path , wherein, the second optical path average value is an average value calculated according to the average optical path length of Raman scattered light received by each photosensitive position of the second photosensitive surface of the same type.

According to an embodiment of the present disclosure, the absolute value of the difference between the first optical path average value and the second optical path average value belongs to the first optical path difference range.

According to an embodiment of the present disclosure, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to an embodiment of the present disclosure, the first optical path difference range is determined according to the optimal differential optical path corresponding to the second preset wavelength.

According to the embodiment of the present disclosure, the source-detection distance of each photosensitive surface of the first same type of photosensitive surfaces corresponding to the second preset wavelength from the center of the incident light is within the range of the preset source-detection distance corresponding to the second preset wavelength , wherein the preset source detection distance range is determined according to the source detection distance between the floating reference position corresponding to the second preset wavelength and the center of the incident light.

According to an embodiment of the present disclosure, the M photosensitive surfaces have the same photosensitive surface corresponding to the second preset wavelength, wherein the same photosensitive surface is used to collect the third Raman intensity corresponding to the second preset wavelength, and the same photosensitive surface includes One or more photosensitive surfaces.

The processing unit is configured to determine the concentration of the measured tissue component according to the third Raman intensity corresponding to the second preset wavelength.

According to an embodiment of the present disclosure, the difference between the average optical path length of the Raman scattered light received by different light sensitive positions of each light sensitive surface in the same light sensitive surface and the optimal optical path corresponding to the second preset wavelength belongs to the second light range of travel.

According to the embodiments of the present disclosure, different parts of the same photosensitive surface are on the same plane or different planes.

According to an embodiment of the present disclosure, the photosensitive surface may be a flat photosensitive surface or a three-dimensional photosensitive surface, wherein if different parts of the photosensitive surface are on the same plane, the photosensitive surface is a flat photosensitive surface. If there are different parts of the photosensitive surface on different planes, the photosensitive surface is a three-dimensional photosensitive surface. The specific use of a plane photosensitive surface or a three-dimensional photosensitive surface can be set according to the actual situation, which is not specifically limited here.

Optionally, for contact measurement, in order to improve the measurement accuracy, it is necessary to make the target surface of the photosensitive surface and the skin surface of the measurement area in a good fit state as much as possible. Among them, the target surface of the photosensitive surface refers to the surface close to the measurement area. Since the flatness of the skin surface in the measurement area may not be high, if a flat photosensitive surface is used, it may be difficult to achieve a good fit between the target surface of the photosensitive surface and the skin surface of the measurement area, while the stereo photosensitive surface is There are photosensitive surfaces with different parts in different planes. Therefore, a three-dimensional photosensitive surface can be used, and a specific stereoscopic photosensitive surface can be set according to the organizational structure characteristics of the measurement area.

FIG. 18 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a glove according to an embodiment of the present disclosure. FIG. 19 schematically shows a schematic diagram of another stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure.

FIG. 20 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a wristband according to an embodiment of the present disclosure. FIG. 21 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of another wristband according to an embodiment of the present disclosure.

FIG. 22 schematically shows a schematic diagram of a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure. In FIG. 22 , the distances of different parts of the photosensitive surface from the preset plane can be set according to the structural characteristics of the arm. In Figure 22, h ₁ and h ₂ represent the distances of different parts of the photosensitive surface from the preset plane.

According to an embodiment of the present disclosure, the photosensitive surface sets are on the same plane or different planes, wherein the photosensitive surface set includes a plurality of photosensitive surfaces.

According to an embodiment of the present disclosure, each photosensitive surface included in the set of photosensitive surfaces may be a planar photosensitive surface or a three-dimensional photosensitive surface. If the photosensitive surface set includes multiple plane photosensitive surfaces, the photosensitive surface form presented by the photosensitive surface set can be realized by setting some or all of the plane photosensitive surfaces on different planes. It is a three-dimensional photosensitive surface.

It should be noted that, according to the three-dimensional photosensitive surface formed by a plurality of planar photosensitive surfaces, the above-mentioned effects for the contact measurement can also be achieved, which will not be repeated here.

According to an embodiment of the present disclosure, the anodes of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected to each other, the anodes of some of the photosensitive surfaces are electrically connected, or the anodes of all the photosensitive surfaces are electrically connected.

According to an embodiment of the present disclosure, each of the M photosensitive surfaces may be used independently, and in this case, anodes of different photosensitive surfaces of the M photosensitive surfaces are not electrically connected.

Some of the M photosensitive surfaces may be used in combination, and in this case, the anodes of the different photosensitive surfaces used in combination are electrically connected.

All of the M photosensitive surfaces may be used in combination, in which case the anodes of the different photosensitive surfaces used in combination are electrically connected.

According to an embodiment of the present disclosure, FIG. 23 schematically shows a schematic diagram of an anode electrical connection of different photosensitive surfaces according to an embodiment of the present disclosure. As shown in FIG. 23 , the anodes of all the photosensitive surfaces were electrically connected.

According to an embodiment of the present disclosure, the light source module includes a light source unit. The light source unit is used for irradiating the measurement area with the incident light of the first preset wavelength under the condition that the reproducibility of the controllable measurement condition is satisfied.

According to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a first determination module, a second determination module and a setting module. The first determining module is used to determine the positioning feature. The second determination module is configured to determine a measurement area according to the positioning feature, wherein the measurement area is an area that satisfies the reproducibility of the controllable measurement condition. The setting module is used to set the measuring probe at the position corresponding to the measuring area.

According to an embodiment of the present disclosure, the positioning features include a first gesture positioning feature and an area positioning feature.

The second determination module may include a first adjustment unit and a first determination unit. The first adjustment unit is configured to adjust the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature. The first determining unit is configured to determine the measurement area according to the area positioning feature when the current measurement posture is the target measurement posture.

As shown in FIG. 24 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a fixing part 1650 , and the fixing part 1650 is used to set the measurement probe 1640 at a position corresponding to the measurement area, wherein the fixing part 1650 is connected to The measurement probe 1640 is integral, partially discrete, or fully discrete.

According to an embodiment of the present disclosure, the fixing part 1650 and the measuring probe 1640 in FIG. 24 may be integrated or separate.

As shown in FIG. 25 , according to an embodiment of the present disclosure, the fixing part 1650 includes a fixing seat 1651 and a first fitting part 1652 . The first fitting 1652 is used to set the fixing base 1651 at a position corresponding to the measurement area. The fixing base 1651 is used to fix the measuring probe 1640 .

According to an embodiment of the present disclosure, the hardness of the first fitting member 1652 includes a first hardness and a second hardness, wherein the first hardness is smaller than the second hardness, and the first hardness is the first hardness in the process of fixing the fixing seat 1651 by the first fitting member 1652 . Corresponding to the hardness, the second hardness is the hardness corresponding to the first fitting member 1652 after fixing the fixing seat 1651 .

According to the embodiment of the present disclosure, in order for the first fitting member 1652 to play a fixing role on the fixing seat 1651, the first fitting member 1652 needs to be relatively rigid. At the same time, in order to minimize the influence generated when the first matching member 1652 fixes the fixing seat 1651, the first matching member 1652 needs to have a certain flexibility. It can be seen that the above-mentioned requirements are imposed on the hardness of the first fitting member 1652 .

In order to solve the above problem, a method of changing the hardness of the first fitting member 1652 may be adopted, that is, the hardness of the first fitting member 1652 includes the first hardness and the second hardness. The first hardness represents the hardness corresponding to the process of fixing the fixing seat 1651 by the first fitting 1652, and the second hardness represents the hardness corresponding to the fixing of the fixing seat 1651 by the first fitting 1652. The first hardness is smaller than the second hardness, The above can try to ensure that the first fitting part 1652 can not only play a fixing role, but also can reduce the influence produced when the first fitting part 1652 fixes the fixing seat 1651 as much as possible.

According to an embodiment of the present disclosure, the first fitting 1652 includes a first Velcro or a first elastic band.

Exemplarily, FIG. 26 schematically shows a schematic diagram of a first fitting according to an embodiment of the present disclosure. The first fitting 1652 in FIG. 26 is a Velcro. Since the material of the matte surface of the Velcro is very soft, the influence generated when the first fitting 1652 is fixed to the fixing seat 1651 can be reduced. At this time, the hardness of the first fitting 1652 is the first hardness. At the same time, in order to enable it to play a fixing role, after the first fitting 1652 fixes the fixing seat 1651, the hook surface can be pasted on the rough surface to increase the hardness of the first fitting 1652. At this time, the first fitting The hardness of the piece 1652 is the second hardness.

According to the embodiment of the present disclosure, since the hardness corresponding to the first matching piece 1652 in the process of fixing the fixing seat 1651 is the first hardness, it can reduce the influence generated when the first matching piece 1652 fixes the fixing seat 1651, and therefore, it can be Try to ensure that the skin state of the skin in the measurement area satisfies the first preset condition during the process of setting the fixing seat 1651 at the position corresponding to the measurement area through the first fitting 1652 .

According to an embodiment of the present disclosure, the hardness of the first fitting 1652 is greater than or equal to the first hardness threshold and less than or equal to the second hardness threshold.

According to an embodiment of the present disclosure, in order to meet the hardness requirement of the first fitting member 1652, in addition to the above-mentioned methods, a material whose hardness is greater than or equal to the first hardness threshold and less than or equal to the second hardness threshold can also be used According to the method of making the first fitting member 1652 , it is also possible to realize that the first fitting member 1652 can fix the fixing seat 1651 and reduce the influence of the first fitting member 1652 when fixing the fixing seat 1651 as much as possible. It should be noted that, the first hardness threshold and the second hardness threshold may be set according to actual conditions, which are not specifically limited herein.

As shown in FIG. 27 , according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a first magnetic part 1660 , the whole or part of the first fitting part 1652 is a metal hinge, and the first magnetic part 1660 is matched with the first magnetic part 1660 . The fitting 1652 is used to fix the fixing base 1651 .

According to the embodiment of the present disclosure, in order to meet the hardness requirement of the first fitting 1652, in addition to the above-mentioned manner, the first fitting 1652 may be entirely or partially a metal hinge. It is realized that the first fitting member 1652 can fix the fixing seat 1651, and the influence generated when the first fitting member 1652 fixes the fixing seat 1651 is reduced as much as possible.

For the fixed effect, the implementation is as follows. After the first fitting 1652 completes the fixing of the fixing base 1651, the first magnetic part 1660 can be adsorbed to the first fitting 1652, so that the first magnetic part 1660 cooperates with the first fitting 1652 to fix the fixing base 1651. play a fixed role. See Figure 27. FIG. 27 schematically shows a schematic diagram of another first fitting according to an embodiment of the present disclosure. All of the first fittings 1652 in FIG. 27 are metal hinges. After the first matching member 1652 completes the fixing of the fixing base 1651 , the first magnetic portion 1660 can be adsorbed to the first matching member 1652 . The first magnetic part 1660 may be a micro electromagnet.

In addition, since the metal hinge is a ferromagnetic metal, and the metal is easy to absorb heat, the direct contact between the metal hinge and the skin will have a greater impact on the skin temperature. Therefore, in order to avoid the impact of the metal heat absorption on the skin temperature, the metal hinge can be The way the insulation is placed below. Alternatively, the insulation may be fleece.

The above can be achieved because, since the metal hinge has better flexibility, the influence produced when the first fitting 1652 is fixed to the fixing seat 1651 can be reduced. At the same time, after the first fitting 1652 completes the fixing of the fixing seat 1651, since the first magnetic part 1660 is adsorbed on the first fitting 1652, the cooperation of the two makes the first fitting 1652 more rigid. Therefore, the first fitting 1652 can be achieve a fixed effect.

It should be noted that, since all or part of the first fitting 1652 is a metal hinge, and the flexibility of the metal hinge is better, it can reduce the influence produced when the first fitting 1652 fixes the fixing seat 1651. Therefore, it can be ensured as much as possible. The skin state of the skin of the skin at the measurement area satisfies the first preset condition during the process of setting the fixing seat 1651 at the position corresponding to the measurement area through the first fitting 1652 .

According to an embodiment of the present disclosure, the surface of the first fitting 1652 is provided with holes.

According to an embodiment of the present disclosure, the measuring probe 1640 is fixed to the fixing base 1651 in at least one of the following manners: the measuring probe 1640 is fixed to the fixing base 1651 by an adhesive tape. The measuring probe 1640 is fixed to the fixing base 1651 by fasteners. The measuring probe 1640 is fixed to the fixing base 1651 by magnetic force. The friction coefficient between the measuring probe 1640 and the fixing base 1651 is greater than or equal to the friction coefficient threshold.

According to an embodiment of the present disclosure, in order to realize that the measurement probe 1640 is fixed to the fixing seat 1651 and ensure that the measurement probe 1640 does not move in the fixing seat 1651, at least one of the following methods may be adopted.

In a first way, the measuring probe 1640 can be fixed to the fixing base 1651 by tape. In the second way, the measuring probe 1640 can be fixed to the fixing base 1651 by a fastener. In a third way, the measuring probe 1640 can be fixed to the fixing base 1651 by magnetic force. In a fourth manner, the friction coefficient between the measuring probe 1640 and the fixing seat 1651 is greater than or equal to the friction coefficient threshold. Optionally, the material of the fixing base 1651 is rubber, aluminum or plastic.

According to an embodiment of the present disclosure, the fixing part 1650 includes a second fitting. The second fitting is used to set the measurement probe 1640 at a position corresponding to the measurement area.

According to an embodiment of the present disclosure, the hardness of the second fitting includes a third hardness and a fourth hardness, wherein the third hardness is smaller than the fourth hardness, and the third hardness corresponds to the process of fixing the measurement probe 1640 by the second fitting Hardness, the fourth hardness is the hardness corresponding to the second fitting member after fixing the measuring probe 1640 .

According to an embodiment of the present disclosure, the second fitting includes a second Velcro or a second elastic band.

According to an embodiment of the present disclosure, the hardness of the second fitting is greater than or equal to the third hardness threshold and less than or equal to the fourth hardness threshold.

According to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a second magnetic part, the whole or part of the second fitting is a metal hinge, and the second magnetic part cooperates with the second fitting to fix the measurement probe 1640 .

According to an embodiment of the present disclosure, the surface of the second fitting is provided with holes.

According to the embodiment of the present disclosure, for the relevant description of the second fitting member, reference may be made to the description of the first fitting member 1652 above, and details are not repeated here. The difference is that the second fitting is used to fix the measuring probe 1640 .

According to an embodiment of the present disclosure, the first determining unit is configured to: acquire the first projection feature. In the case where it is determined that the regional positioning feature does not match the first projected feature, the positions of the measuring probe 1640 and/or the fixing portion 1650 are adjusted until the regional positioning feature matches the first projected feature. When it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe 1640 and/or the fixing portion 1650 is determined as the measurement region.

As shown in FIGS. 28 to 29 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a region positioning portion 1670 , and the region positioning portion 1670 is disposed on the object to be measured, the measurement probe 1640 , the fixing portion 1650 or other objects , the region positioning unit 1670 is used to project the first projection feature.

According to an embodiment of the present disclosure, FIG. 28 schematically shows a schematic diagram of a region positioning part according to an embodiment of the present disclosure. The measuring probe 1640 and the fixing part 1650 are not shown in FIG. 28 , and the area positioning part 1670 is used to project the first projection feature, and the first projection feature is a cross light spot. The regional positioning feature is the cross mark point.

FIG. 29 schematically shows a schematic diagram of another area positioning part according to an embodiment of the present disclosure. In FIG. 29, the area positioning part 1670 is integrated with the measuring probe 1640 and the fixing part 1650, and the area positioning feature is set on the back of the hand of the measured object. The area positioning unit 1670 is used to project the first projection feature, and the first projection feature is a cross light spot.

According to an embodiment of the present disclosure, in the case where it is determined that the region positioning part 1670 is provided on the measurement probe 1640 , the region positioning feature is not provided on the measurement probe 1640 . If it is determined that the region positioning feature is provided on the fixing portion 1650 , the region positioning feature is not provided on the fixing portion 1650 .

According to an embodiment of the present disclosure, the area positioning part 1670 includes a first laser.

According to an embodiment of the present disclosure, the first laser may project a spot of a preset shape to form the first projection feature.

According to an embodiment of the present disclosure, the first determination unit is configured to: acquire the first target image. A first template image is acquired, wherein the first template image includes regional positioning features. If it is determined that the first target image does not match the first template image, adjust the position of the measuring probe 1640 and/or the fixing part 1650 to acquire a new first target image until the new first target image matches the first template Image matching. When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe 1640 and/or the fixing part 1650 is determined as a measurement area.

As shown in FIG. 30 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a first image acquisition part 1680 , and the first image acquisition part 1680 is disposed on the measured object, the measurement probe 1640 , the fixing part 1650 or other The object, the first image acquisition part 1680 is used to acquire the first target image.

According to an embodiment of the present disclosure, FIG. 30 schematically shows a schematic diagram of a first image acquisition part according to an embodiment of the present disclosure. In FIG. 30 , the first image acquisition part 1680 is integrated with the measurement probe 1640 and the fixing part 1650 , and the regional positioning feature is set on the back of the hand of the measured object. The first image acquisition part 1680 is used to acquire the first target image. The first image acquisition part 1680 may be an image sensor.

According to an embodiment of the present disclosure, the first determination unit is configured to: acquire a second target image, wherein the second target image includes a region localization feature. If it is determined that the position of the region positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe 1640 and/or the fixing part 1650 to acquire a new second target image until the new second target image is The position of the regional positioning feature in the target image is the first preset position. In the case that the position of the region positioning feature in the new second target image is determined to be the first preset position, the region corresponding to the measurement probe 1640 and/or the fixing portion 1650 is determined as the measurement region.

According to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a second image acquisition part, the second image acquisition part is arranged on the measured object, the measurement probe 1640 , the fixing part 1650 or other objects, and the second image acquisition part uses for collecting the second target image.

According to an embodiment of the present disclosure, in a case where it is determined that the second image acquisition part is provided on the measurement probe 1640 , the area positioning feature is not provided on the measurement probe 1640 . In the case where it is determined that the second image capturing part is arranged on the fixing part 1650 , the area positioning feature is not arranged on the fixing part 1650 .

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire the second projection feature. In the case where it is determined that the first posture locating feature does not match the second projection feature, the current measurement posture is adjusted until the first posture locating feature and the second projection feature match. When it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.

As shown in FIG. 31 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a first posture positioning part 1690 , and the first posture positioning part 1690 is arranged on the object to be measured, the measurement probe 1640 , the fixing part 1650 or other Object, the first pose locator 1690 is used to project the second projected feature.

According to an embodiment of the present disclosure, in a case where it is determined that the first posture positioning part 1690 is provided on the measurement probe 1640 , the first posture positioning feature is not provided on the measurement probe 1640 . When it is determined that the first posture positioning portion 1690 is provided on the fixing portion 1650 , the first posture positioning feature is not provided on the fixing portion 1650 .

According to an embodiment of the present disclosure, the first posture positioning part 1690 includes a second laser.

According to an embodiment of the present disclosure, the second laser may project a predetermined shaped light spot to form the second projection feature.

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire a third target image. A second template image is acquired, wherein the second template image includes the first gesture location feature. When it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image until the new third target image matches the second template image. When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.

As shown in FIG. 32 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a third image acquisition part 1700 , and the third image acquisition part 1700 is arranged on the measured object, the measurement probe 1640 , the fixing part 1650 or other The object, the third image acquisition part 1700 is used to acquire the third target image.

According to an embodiment of the present disclosure, FIG. 32 schematically shows a schematic diagram of a third image acquisition part according to an embodiment of the present disclosure. In FIG. 32 , the third image acquisition part 1700 is integrated with the measurement probe 1640 and the fixing part 1650 , and the first posture positioning feature is set on the back of the hand of the measured object. The third image acquisition part 1700 is used to acquire a third target image. The third image acquisition part 1700 may be an image sensor.

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire a fourth target image, wherein the fourth target image includes the first posture positioning feature. In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image until the first posture is positioned in the new fourth target image The location of the feature is at the second preset location. When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined as the target measurement posture.

According to the embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a fourth image acquisition part, the fourth image acquisition part is arranged on the measured object, the measurement probe 1640 , the fixing part 1650 or other objects, and the fourth image acquisition part uses to collect the fourth target image.

According to an embodiment of the present disclosure, in a case where it is determined that the fourth image acquisition part is provided on the measurement probe 1640 , the first posture positioning feature is not provided on the measurement probe 1640 . In the case where it is determined that the fourth image capturing part is provided on the fixing part 1650 , the first posture positioning feature is not provided on the fixing part 1650 .

According to an embodiment of the present disclosure, the tissue composition measurement device 1650 may further include a third determination module and an adjustment module. The third determining module is configured to determine the second posture positioning feature under the condition that the current measurement posture is not the target measurement posture if the measurement probe 1640 is set at a position corresponding to the measurement area. The adjustment module is configured to adjust the current measurement posture to the target measurement posture according to the second posture positioning feature.

According to an embodiment of the present disclosure, the adjustment module may include a first acquisition unit, a second adjustment unit, and a second determination unit.

The first obtaining unit is used to obtain the third projection feature. The second adjustment unit is configured to adjust the current measurement posture when it is determined that the second posture positioning feature does not match the third projection feature until the second posture positioning feature matches the third projection feature. The second determining unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the second posture positioning feature matches the third projection feature.

According to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a second posture positioning part, the second posture positioning part is arranged on the measured object, the measuring probe 1640 , the fixing part 1650 or other objects, and the second posture positioning part is used for for projecting the third projected feature.

According to an embodiment of the present disclosure, in a case where it is determined that the second posture positioning part is provided on the measuring probe 1640 , the second posture positioning feature is not provided on the measuring probe 1640 and the fixing part 1650 . In the case where it is determined that the second posture positioning part is provided on the fixing part 1650 , the second posture positioning feature is not provided on the measuring probe 1640 and the fixing part 1650 .

According to an embodiment of the present disclosure, the second posture positioning portion includes a third laser.

According to an embodiment of the present disclosure, the third laser may project a predetermined shaped light spot to form the third projection feature.

According to an embodiment of the present disclosure, the adjustment module may include a second acquisition unit, a third acquisition unit, a third adjustment unit, and a third determination unit. The second acquiring unit is configured to acquire the fifth target image. A third acquiring unit, configured to acquire a third template image, wherein the third template image includes the second posture positioning feature. A third adjustment unit, configured to adjust the current measurement posture to obtain a new fifth target image when it is determined that the fifth target image does not match the third template image, until the new fifth target image and the third template image match. The third determination unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the new fifth target image matches the third template image.

According to an embodiment of the present disclosure, the tissue composition measurement device may further include a fifth image acquisition part, the fifth image acquisition part is disposed on the measured object, the measurement probe 1640 , the fixing part 1650 or other objects, and the fifth image acquisition part is used for A fifth target image is acquired.

According to an embodiment of the present disclosure, the adjustment module may include a fourth acquisition unit, a fourth adjustment unit, and a fourth determination unit. The fourth acquisition unit is configured to acquire a sixth target image, wherein the sixth target image includes the second posture positioning feature. The fourth adjustment unit is configured to adjust the current measurement posture to obtain a new sixth target image when it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position, until the new sixth The position of the second gesture positioning feature in the target image is at a third preset position. The fourth determining unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position.

According to the embodiment of the present disclosure, the tissue composition measurement device 1600 may further include a sixth image acquisition part, the sixth image acquisition part is arranged on the measured object, the measurement probe 1640, the fixing part 1650 or other objects, and the sixth image acquisition part uses to collect the sixth target image.

According to an embodiment of the present disclosure, in a case where it is determined that the sixth image acquisition part is provided on the measurement probe 1640 , the second posture positioning feature is not provided on the measurement probe 1640 and the fixing part 1650 . In the case where it is determined that the sixth image capturing part is provided on the measuring probe 1640 , the second posture positioning feature is not provided on the measuring probe 1640 and the fixing part 1650 .

According to an embodiment of the present disclosure, the sixth image acquisition part, the fifth image acquisition part, the fourth image acquisition part, the third image acquisition part 1700, the first image acquisition part 1680, and the second image acquisition part may be different, partially the same, or All the same.

According to an embodiment of the present disclosure, when an optical method is used to locate the measurement area and the measurement posture, the area locating part 1670 , the first posture locating part 1690 and the second posture locating part may be all the same, partially the same, or all different The said part is the same means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the first projected feature, the second projected feature and the third projected feature. The above manner can simplify the complexity of the positioning structure.

When the image matching method is used to locate the measurement area and the measurement posture, the first image acquisition part 1680, the third image acquisition part 1700 and the fifth image acquisition part may be all the same, partially the same or all different, The said part is the same means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the first target image, the third target image and the fifth target image. The above manner can simplify the complexity of the positioning structure.

When the imaging method is used to locate the measurement area and the measurement posture, the second image acquisition part, the fourth image acquisition part and the sixth image acquisition part may be all the same, partially the same or all different, and the parts are the same It means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the second target image, the fourth target image and the sixth target image. The above manner can simplify the complexity of the positioning structure.

The region positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit have the same structure. The second pose location feature is identical to the region location feature and is partially identical to the first pose location feature. The measurement area is the extended side of the forearm.

FIG. 33 schematically shows a schematic diagram of a measurement posture and measurement area positioning according to an embodiment of the present disclosure. The area positioning part 1670 , the first attitude positioning part 1690 and the second attitude positioning part all include laser 1 and laser 2 . The laser 1 and the laser 2 are provided in the measurement probe 1640 .

During the first measurement posture positioning, the measurement probe 1640 is set on the base, and the position of the measurement probe 1640 is fixed before the first measurement posture positioning is completed. According to the first posture positioning feature and the second projection feature, adjust the current measurement posture until the first posture positioning feature and the second projection feature match, and in the case of matching, the first measurement posture positioning is completed.

When positioning the measurement area, the measurement probe 1640 is set on the object to be measured, and the position of the measurement probe 1640 is adjusted according to the area location feature and the first projection feature until the area location feature matches the first projection feature. Next, it explains that the positioning of the measurement area is completed.

After the measurement probe 1640 is set on the object to be measured, if the current measurement posture is not the target posture, before the measurement, it is necessary to perform the positioning of the measurement posture again. According to the second posture positioning feature and the third projection feature, adjust the current measurement posture until the second posture positioning feature and the third projection feature match.

The region positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit have the same configuration. The region location feature is exactly the same as the second gesture location feature, and is partially the same as the first gesture location feature. The measurement area is the extended side of the forearm.

FIG. 34 schematically shows another schematic diagram of measurement posture and measurement area positioning according to an embodiment of the present disclosure. In FIG. 34 , the area positioning part 1670 and the second posture positioning part both include the laser 3 and the laser 4 . The first posture positioning unit 1690 includes the laser 5 and the laser 6 . The laser 3 and the laser 4 are provided in the measurement probe 1640 . The laser 5 and the laser 6 are provided on the base.

According to an embodiment of the present disclosure, the tissue composition measurement device 1600 may include a prompting module. The prompting module is used to generate prompting information, wherein the prompting information is used to prompt that the measurement posture positioning and/or the measurement area positioning is completed, and the form of the prompting information includes at least one of image, voice or vibration.

According to an embodiment of the present disclosure, the photosensitive surface is obtained by disposing a mask on the initial photosensitive surface, and the light transmittance of the mask is less than or equal to a light transmittance threshold.

According to an embodiment of the present disclosure, the shape of the mask is determined according to the jitter distribution of Raman scattered light.

As shown in FIG. 35 , according to an embodiment of the present disclosure, the measurement probe 1640 is provided with a first sleeve 1710 . The first end surface of the first sleeve 1710 extends beyond the target surface of the measurement probe 1640, wherein the first end surface represents the end surface close to the measurement area, and the target surface of the measurement probe 1640 represents the surface close to the measurement area.

According to an embodiment of the present disclosure, in order to shield the interference light, the first sleeve 1710 may be provided on the measurement probe 1640 so that the end face of the first sleeve 1710 close to the measurement area exceeds the target surface of the measurement probe 1640 . Interfering light may include surface reflected light and/or diffracted light.

According to an embodiment of the present disclosure, the second end face and/or the inner area of the first sleeve 1710 are provided with scattering objects, wherein the first end face and the second end face are two opposite end faces, and the inner area includes a partial inner area or the entire area inside.

According to the embodiment of the present disclosure, in order to make the intensity distribution of the light spot irradiated by the incident light to the measurement area uniform, a manner of disposing scatterers on the corresponding part of the first sleeve 1710 may be adopted. The scatterer can include sulfated paper, silica gel, or a target mixture, wherein the target mixture can include a mixture of polydimethylsiloxane and titanium dioxide particles.

As shown in FIG. 36 , according to an embodiment of the present disclosure, the tissue composition measurement device 1600 further includes a second sleeve 1720 , and the second sleeve 1720 is disposed outside the target area of the first sleeve 1710 , wherein the target area represents The first sleeve 1710 extends beyond part or all of the target surface of the measurement probe 1640 .

According to the embodiment of the present disclosure, in order to make the light spot irradiated by the incident light to the measurement area as large as possible, a manner of disposing the second sleeve 1720 outside the target area of the first sleeve 1710 may be adopted.

According to an embodiment of the present disclosure, the second sleeve 1710 is provided with a diffuser.

According to the embodiment of the present disclosure, if the second sleeve 1710 is provided, in order to make the intensity distribution of the light spot irradiated by the incident light to the measurement area uniform, a way of disposing scatterers in the corresponding part of the second sleeve 1710 may be adopted.

According to an embodiment of the present disclosure, the inner diameter of the first sleeve is greater than or equal to the inner diameter threshold.

According to an embodiment of the present disclosure, the opening of the first end surface of the first sleeve is greater than or equal to the opening of the second end surface of the first sleeve.

According to an embodiment of the present disclosure, in order to make the incident light irradiated to the measurement area as large as possible, the inner diameter of the first sleeve 1710 may be greater than or equal to the inner diameter threshold, and/or the first end face of the first sleeve 1710 may be used. The opening of the first sleeve 1710 is greater than or equal to the opening of the second end surface of the first sleeve 1710, that is, the opening of the end surface of the first sleeve 1710 close to the measurement area is greater than or equal to the opening of the first sleeve 1710 away from the measurement area. End openings.

As shown in FIGS. 38 to 39 , according to an embodiment of the present disclosure, a refractive index matcher is filled between the photosensitive surface and the measurement area.

According to the embodiments of the present disclosure, the skin surface in the measurement area is unstable due to the jitter, which in turn causes the exit angle of the outgoing light to change, which affects the possibility of acquiring the real measured tissue component signal. Therefore, in order to minimize the jitter band In order to avoid adverse effects, a refractive index matching material can be filled between the photosensitive surface and the measurement area to improve the stability and efficiency of the photosensitive surface receiving outgoing light.

Illustratively, the jitter caused by pulse beating is taken as an example for description. Pulse beat can be reflected by the state of blood vessels. FIG. 37 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light without filling with an index matcher according to an embodiment of the present disclosure. In FIG. 37 , the blood vessel state 1 represents the vasoconstriction state, the blood vessel state 2 represents the vasodilation state, the skin state 1 represents the skin state corresponding to the blood vessel state 1 , and the skin state 2 represents the skin state corresponding to the blood vessel state 2 . It can be seen from Figure 37 that jitter will cause instability of the skin surface in the measurement area, which in turn will change the exit angle of the exiting light.

FIG. 38 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light under the condition of filling with a refractive index matcher according to an embodiment of the present disclosure.

FIG. 39 schematically shows another schematic diagram of the photosensitive surface receiving the outgoing light under the condition of filling with an index matching material according to an embodiment of the present disclosure.

It can be seen from Figure 38 and Figure 39 that filling the refractive index matching material between the photosensitive surface and the measurement area can improve the stability and efficiency of the photosensitive surface receiving outgoing light.

According to an embodiment of the present disclosure, the surfaces of the S photosensitive surfaces in the M photosensitive surfaces are respectively provided with filters for filtering out the incident light of the first preset wavelength and extracting the second preset wavelength, 1≤S≤M . Filters include long-pass filters and band-pass filters. Alternatively, the filters include band-stop filters and band-pass filters.

According to an embodiment of the present disclosure, in order to obtain the second preset wavelength, a method of arranging a filter on the surface of the photosensitive surface can be adopted. Wherein, the filter may include a long-pass filter and a band-pass filter, the long-pass filter is used to filter out the first preset wavelength (ie incident light) as much as possible, and the band-pass filter is used to make the second wavelength The preset wavelength (ie Raman scattered light) passes through, and the two cooperate to filter out the first preset wavelength and measure the second preset wavelength. In addition, the filter may further include a band-stop filter and a band-pass filter. The band-stop filter is used to filter out the first preset wavelength as much as possible, and the band-pass filter is used to pass the second preset wavelength. , and the two cooperate to filter out the first preset wavelength and measure the second preset wavelength.

Any of the modules, units, or at least part of the functions of any of the modules according to the embodiments of the present disclosure may be implemented in one module. Any one or more of the modules and units according to the embodiments of the present disclosure may be divided into multiple modules for implementation. Any one or more of the modules and units according to the embodiments of the present disclosure may be at least partially implemented as hardware circuits, such as Field Programmable Gate Arrays (FPGA), Programmable Logic Arrays (Programmable Logic Arrays, PLA), system-on-chip, system-on-substrate, system-on-package, Application Specific Integrated Circuit (ASIC), or any other reasonable means of hardware or firmware that can integrate or package circuits, Or it can be implemented in any one of the three implementation manners of software, hardware and firmware, or in an appropriate combination of any of them. Alternatively, one or more of the modules and units according to the embodiments of the present disclosure may be implemented at least in part as computer program modules, which, when executed, may perform corresponding functions.

For example, any number of acquisition modules and processing modules may be combined into one module/unit for implementation, or any one of the modules/units may be split into multiple modules/units. Alternatively, at least part of the functionality of one or more of these modules/units may be combined with at least part of the functionality of other modules/units and implemented in one module/unit. According to embodiments of the present disclosure, at least one of the acquisition module and the processing module may be implemented at least in part as a hardware circuit, such as a field programmable gate array (FPGA), a programmable logic array (PLA), a system on a chip, a A system, a system on a package, an application specific integrated circuit (ASIC), or any other reasonable means of integrating or packaging a circuit can be implemented in hardware or firmware, or in any one of software, hardware, and firmware implementations or any appropriate combination of any of them. Alternatively, at least one of the acquisition module and the processing module may be implemented, at least in part, as a computer program module that, when executed, may perform corresponding functions.

It should be noted that the tissue composition measurement device in the embodiment of the present disclosure corresponds to the tissue composition measurement method part in the embodiment of the present disclosure, and the description of the tissue composition measurement device part refers to the tissue composition measurement method part, which is not described here. Repeat.

FIG. 40 schematically shows a schematic diagram of a wearable device according to an embodiment of the present disclosure. The wearable device 4000 shown in FIG. 40 is only an example, and should not impose any limitations on the functions and scope of use of the embodiments of the present disclosure.

As shown in FIG. 40 , the wearable device 4000 includes a Raman scattering-based tissue composition measurement device 1600 .

According to the technical solutions of the embodiments of the present disclosure, by irradiating the measurement area with the incident light of the first preset wavelength, the incident light of the first preset wavelength passes through the measurement area and then exits from the exit position to form at least one beam of the second preset wavelength. For the Raman scattered light, the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift, and the Raman intensity corresponding to each Raman scattered light collected by the measuring probe is obtained, and set The tissue component measuring device with the measuring probe has a signal-to-noise ratio level that satisfies the resolution of expected changes in the concentration of the tissue component, and determines the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength. Since the adopted tissue composition measuring device provided with a measuring probe has a signal-to-noise ratio level that can distinguish the expected tissue composition concentration change, the ability to perceive the expected tissue composition concentration change is realized, thereby improving the acquisition of the real measured tissue composition. signal possibilities.

As shown in FIG. 41 , according to an embodiment of the present disclosure, the wearable device 4000 further includes a buckle portion 4010 and a body 4020 . The buckle portion 4010 and the main body 4020 are used to cooperate and fix the Raman scattering-based tissue composition measurement device 1600 .

According to an embodiment of the present disclosure, FIG. 41 schematically shows a schematic diagram of an assembling process of a wearable device according to an embodiment of the present disclosure.

According to an embodiment of the present disclosure, the quality of the wearable device 4000 is less than or equal to a quality threshold, so that the movement law of the wearable device 4000 is consistent with the skin shaking law at the measurement area.

According to the embodiments of the present disclosure, in order to improve the possibility of acquiring the real measured tissue component signal, the weight of the wearable device 4000 can be made lighter, so that when the wearable device 4000 is set at a position corresponding to the measurement area, The wearable device 4000 can follow the skin shaking at the measurement area, that is, the movement law of the wearable device 4000 can be consistent with the skin shaking law at the measurement area, so that the average optical path of the outgoing light received by the measurement probe 1640 is within the skin. Keep within the preset optical path range during dithering. The reason why the average optical length of the outgoing light received by the measurement probe 1640 can be kept within the preset optical length range during the skin shaking process at the measurement area is that if the wearable device 4000 can follow the skin shaking at the measurement area, Then, the relative position of the measurement probe 1640 on the measurement area can be kept unchanged or basically unchanged, so that the measurement probe 1640 can receive the outgoing light emitted from the fixed outgoing position. The relative position of the measurement area remains the same or remains substantially unchanged at the exit position. At the same time, during the skin shaking process at the measurement area, the relative position of the incident position of the incident light on the measurement area can remain unchanged or substantially unchanged. Under the circumstance, it can be ensured that the average optical path of the outgoing light remains unchanged as much as possible.

Exemplarily, FIG. 42 schematically shows a method according to an embodiment of the present disclosure, under the condition that the wearable device is consistent with the skin shaking law, so that the average optical path of the outgoing light received by the measuring probe is kept at the same value during the skin shaking process. Schematic representation of preset optical path ranges. During the skin shaking process, the measurement probe 1640 (not shown in FIG. 42 ) can stably receive the outgoing light emitted from the outgoing position B in the measurement area after the incident light is incident from the incident position A in the measurement area. The movement range of the skin is represented by ζ ₁ , and the movement range of the measuring probe 1640 is represented by ζ ₂ , where ζ ₁ =ζ ₂ .

According to an embodiment of the present disclosure, the wearable device 4000 makes the movement amplitude of the skin at the measurement area less than or equal to the movement amplitude threshold.

According to the embodiments of the present disclosure, in order to improve the possibility of acquiring the real measured tissue component signal, the quality of the wearable device 4000 can be made larger, and when the wearable device 4000 is set at a position corresponding to the measurement area, The skin shaking at the measurement area, that is, the movement amplitude of the skin at the measurement area is less than or equal to the movement amplitude threshold, so that the average optical length of the outgoing light received by the measurement probe 1640 is maintained at the preset optical length during the skin shaking process. within the range. The above-mentioned reason that the average optical length of the outgoing light received by the measurement probe 1640 can be maintained within the preset optical path range during the skin shaking process at the measurement area is that if the wearable device 4000 can suppress the skin shaking at the measurement area , the relative position of the measurement probe 1640 on the measurement area can be kept unchanged or substantially unchanged as much as possible, so that the measurement probe 1640 can receive the outgoing light emitted from the fixed outgoing position. At the same time, during the skin shaking process at the measurement area, the relative position of the incident position of the incident light on the measurement area can remain unchanged or substantially unchanged. Under the circumstance, it can be ensured that the average optical path of the outgoing light remains unchanged as much as possible.

Exemplarily, FIG. 43 schematically shows the average light of the outgoing light received by the measurement probe when the wearable device makes the movement amplitude of the skin at the measurement area less than or equal to the movement amplitude threshold according to an embodiment of the present disclosure. Schematic illustration of how the optical path stays within the preset optical path range during skin shaking. The movement amplitude of the skin at the measurement area in Figure 43 is close to zero.

According to the embodiments of the present disclosure, for the specific description of the tissue component measurement device, reference may be made to the corresponding part above, and details are not repeated here. In addition, the tissue composition measurement device includes a processor that can execute various programs according to a program stored in a read-only memory (Read-Only Memory, ROM) or a program loaded from a storage portion into a random access memory (Random Access Memory, RAM). appropriate action and handling. A processor may include, for example, a general-purpose microprocessor (eg, a CPU), an instruction set processor and/or a related chipset, and/or a special-purpose microprocessor (eg, an application specific integrated circuit (ASIC)), among others. Processing may also include on-board memory for caching purposes. The processor may comprise a single processing unit or multiple processing units for performing different actions of the method flow according to the embodiments of the present disclosure.

In the RAM, various programs and data necessary for the operation of the tissue composition measurement device are stored. The processor, ROM, and RAM are connected to each other through a bus. The processor performs various operations of the method flow according to the embodiments of the present disclosure by executing programs in the ROM and/or RAM. Note that the program may also be stored in one or more memories other than ROM and RAM. Processes may also perform various operations of method flows according to embodiments of the present disclosure by executing programs stored in the one or more memories.

According to an embodiment of the present disclosure, the wearable device may further include an input/output (I/O) interface, which is also connected to the bus. The wearable device may also include one or more of the following components connected to the I/O interface: an input portion including a keyboard, a mouse, etc.; an input portion such as a cathode ray tube (CRT), a liquid crystal display (LCD), etc. and an output section for speakers, etc.; a storage section including a hard disk, etc.; and a communication section including a network interface card such as a LAN card, a modem, and the like. The communication section performs communication processing via a network such as the Internet. Drives are also connected to the I/O interface as required. Removable media, such as magnetic disks, optical disks, magneto-optical disks, semiconductor memories, etc., are mounted on the drive as needed, so that the computer program read therefrom is installed into the storage section as needed.

The present disclosure also provides a computer-readable storage medium. The computer-readable storage medium may be included in the device/apparatus/system described in the above embodiments; it may also exist alone without being assembled into the device/system. device/system. The above-mentioned computer-readable storage medium carries one or more programs, and when the above-mentioned one or more programs are executed, implement the method according to the embodiment of the present disclosure.

According to an embodiment of the present disclosure, the computer-readable storage medium may be a non-volatile computer-readable storage medium. Examples may include, but are not limited to, portable computer disks, hard disks, random access memory (RAM), read only memory (ROM), erasable programmable read only memory (EPROM) or flash memory), portable compact Disk Read-Only Memory (Computer Disc Read-Only Memory, CD-ROM), optical storage device, magnetic storage device, or any suitable combination of the above. In this disclosure, a computer-readable storage medium may be any tangible medium that contains or stores a program that can be used by or in conjunction with an instruction execution system, apparatus, or device.

For example, according to embodiments of the present disclosure, a computer-readable storage medium may include one or more memories other than ROM and/or RAM and/or ROM and RAM described above.

Embodiments of the present disclosure also include a computer program product, which includes a computer program, and the computer program includes program codes for executing the methods provided by the embodiments of the present disclosure.

When the computer program is executed by the processor, the above-described functions defined in the system/apparatus of the embodiments of the present disclosure are performed. According to embodiments of the present disclosure, the systems, apparatuses, modules, units, etc. described above may be implemented by computer program modules.

In one embodiment, the computer program may rely on a tangible storage medium such as an optical storage device, a magnetic storage device, or the like. In another embodiment, the computer program may also be transmitted, distributed in the form of a signal over a network medium, and downloaded and installed through the communication portion, and/or installed from a removable medium. The program code embodied by the computer program may be transmitted using any suitable network medium, including but not limited to: wireless, wired, etc., or any suitable combination of the foregoing.

According to the embodiments of the present disclosure, the program code for executing the computer program provided by the embodiments of the present disclosure may be written in any combination of one or more programming languages, and specifically, high-level procedures and/or object-oriented programming may be used. programming language, and/or assembly/machine language to implement these computational programs. Programming languages include, but are not limited to, languages such as Java, C++, python, "C" or similar programming languages. The program code may execute entirely on the user computing device, partly on the user device, partly on a remote computing device, or entirely on the remote computing device or server. In cases involving remote computing devices, the remote computing devices may be connected to the user computing device through any kind of network, including Local Area Networks (LANs) or Wide Area Networks (WANs), or may be connected to external A computing device (eg, connected via the Internet using an Internet service provider).

The flowchart and block diagrams in the Figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present disclosure. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of code that contains one or more logical functions for implementing the specified functions executable instructions. It should also be noted that, in some alternative implementations, the functions noted in the blocks may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It is also noted that each block of the block diagrams or flowchart illustrations, and combinations of blocks in the block diagrams or flowchart illustrations, can be implemented in special purpose hardware-based systems that perform the specified functions or operations, or can be implemented using A combination of dedicated hardware and computer instructions is implemented. Those skilled in the art will appreciate that various combinations and/or combinations of features recited in various embodiments and/or claims of the present disclosure are possible, even if such combinations or combinations are not expressly recited in the present disclosure. In particular, various combinations and/or combinations of the features recited in the various embodiments of the present disclosure and/or in the claims may be made without departing from the spirit and teachings of the present disclosure. All such combinations and/or combinations fall within the scope of this disclosure.

Embodiments of the present disclosure have been described above. However, these examples are for illustrative purposes only, and are not intended to limit the scope of the present disclosure. Although the various embodiments are described above separately, this does not mean that the measures in the various embodiments cannot be used in combination to advantage. The scope of the present disclosure is defined by the appended claims and their equivalents. Without departing from the scope of the present disclosure, those skilled in the art can make various substitutions and modifications, and these substitutions and modifications should all fall within the scope of the present disclosure.

Claims (10)

1. A method of tissue element measurement based on raman spectroscopy comprising:

irradiating a measurement area with incident light with a first preset wavelength, wherein the incident light with the first preset wavelength is emitted from an emitting position after passing through the measurement area to form at least one bundle of Raman scattering light with a second preset wavelength, and the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to preset Raman shift;

acquiring Raman intensity corresponding to each beam of Raman scattered light acquired by a measuring probe, wherein a tissue component measuring device provided with the measuring probe has a signal-to-noise ratio level which meets the requirement of distinguishing the concentration change of expected tissue components; and

And determining the concentration of the detected tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

2. The method of claim 1, wherein the acquiring Raman intensities corresponding to each beam of the Raman scattered light acquired by a measurement probe comprises:

acquiring Raman intensity corresponding to each beam of the Raman scattered light collected by the measuring probe under the condition of shielding fluorescence interference.

3. The method of claim 2, further comprising:

fluorescence interference is shielded based on a time-gated approach.

4. The method of claim 1, wherein the same incident beam is spectroscopically illuminated to different incident positions.

5. The method of claim 1, wherein the measurement probe comprises M photosurfaces;

the acquiring of the raman intensity corresponding to each bundle of the raman scattered light acquired by the measuring probe, wherein the tissue composition measuring device provided with the measuring probe has a signal-to-noise level satisfying a resolution of a change in concentration of an expected tissue composition, includes:

and acquiring light intensity values which are acquired by the M photosensitive surfaces and correspond to each beam of Raman scattering light to acquire T Raman intensities, wherein each Raman intensity is acquired by processing according to the light intensity value of the Raman scattering light acquired by one or more photosensitive surfaces, the total area of the same type of photosensitive surfaces is larger than or equal to an area threshold value, the area of each photosensitive surface in the same type of photosensitive surfaces is continuous, the same type of photosensitive surfaces comprises one or more photosensitive surfaces, the same type of photosensitive surfaces is used for outputting one Raman intensity, and T is more than or equal to 1 and less than or equal to M, so that the tissue component measuring device has the signal-to-noise ratio level which meets the requirement of distinguishing the concentration change of the expected tissue component.

6. The method of claim 5, wherein each photosensitive surface is capable of collecting the intensity value of the Raman scattered light emitted from the emission position within the preset anti-shake range corresponding to the photosensitive surface.

7. A tissue constituent measurement device based on raman scattering, comprising:

the device comprises a light source module, a Raman scattering module and a Raman scattering module, wherein the light source module is used for irradiating a measurement area with incident light with a first preset wavelength, the incident light with the first preset wavelength is emitted from an emitting position after passing through the measurement area to form at least one bundle of Raman scattering light with a second preset wavelength, and the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to preset Raman displacement;

an acquisition module for acquiring the raman intensity corresponding to each bundle of the raman scattered light acquired by the measurement probe, wherein the tissue composition measurement device provided with the measurement probe has a signal-to-noise level that satisfies the resolution of the expected tissue composition concentration variation; and

and the processing module is used for determining the concentration of the detected tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

8. A wearable device comprising the tissue composition measurement device of claim 7.

9. The wearable device of claim 8, wherein the mass of the wearable device is less than or equal to a mass threshold to achieve that the movement law of the wearable device is consistent with the skin jitter law at the measurement area.

10. The wearable device of claim 8, wherein the wearable device causes an amplitude of movement of skin at the measurement area to be less than or equal to an amplitude of movement threshold.

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