CN111920377B - High-speed functional fundus three-dimensional detection system based on near-infrared light - Google Patents
High-speed functional fundus three-dimensional detection system based on near-infrared light Download PDFInfo
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Abstract
The invention discloses a high-speed functional fundus three-dimensional detection system based on near-infrared light, which comprises a supercontinuum laser module, a laser scanning module, a dispersion focusing module, a non-de-scanning spectrum detection module and a de-scanning spectrum detection module. The invention utilizes the near infrared band of the supercontinuum laser to irradiate the eyeground, not only can reduce the influence of visible light on human eyes, but also can improve the focusing effect and the imaging resolution by means of the high spatial coherence of the supercontinuum laser.
Description
Technical Field
The invention belongs to the field of optical detection, and particularly relates to a high-speed functional fundus three-dimensional detection system based on near infrared light.
Background
The fundus inspection system is an important medical instrument for screening ophthalmic diseases. Through fundus detection, people can obtain the morphological characteristics of retina and choroid, and further analyze optic nerve papilla and fundus blood vessels through the morphological characteristics to carry out disease diagnosis. In addition, recent researches show that the pathological changes of fundus nerves and fundus blood vessels are closely related to cranial nerves and cerebrovascular diseases, so that fundus detection plays an important role in monitoring human health.
However, since the biological structure of the fundus is complicated, in order to more accurately acquire the morphological characteristics of the nerves and blood vessels of the fundus, a three-dimensional optical fundus inspection system has been developed, which can acquire a three-dimensional morphological image of the fundus at the micron level. Similar to the diagnosis of other medical images, the three-dimensional image of the fundus also requires interpretation by a professional doctor, which causes a shortage of medical resources. In order to overcome the above problems, an automated image feature analysis technique has been developed, but the automated image feature analysis technique cannot completely replace a doctor because of the accuracy problem. On the other hand, a fundus hyperspectral image detection technique has attracted attention in recent years. By acquiring spectral data of the fundus, people can accurately separate the blood vessel information of the fundus image and can also calculate the blood oxygen saturation by combining with the hemoglobin absorption spectrum.
Currently, the fundus three-dimensional optical detection technology and the fundus hyperspectral detection technology have important positions in ophthalmic medical instruments, and the two technologies have corresponding functions on ophthalmic disease diagnosis. However, there is no technology to integrate the two technologies in a single detection system. In the invention, the three-dimensional optical detection and hyperspectral detection of the eyeground are realized simultaneously by integrating various optical and electromechanical devices.
Disclosure of Invention
The invention provides a high-speed functional fundus three-dimensional detection system based on near-infrared light, which integrates a supercontinuum laser module, a dispersion focusing module, a de-scanning spectrum detection module and a non-de-scanning detection module to realize the hardware part of the system.
The technical scheme adopted by the invention for solving the technical problems is as follows:
the invention discloses a high-speed functional fundus three-dimensional detection system based on near-infrared light, which comprises a supercontinuum laser module, a laser scanning module, a dispersion focusing module, a non-de-scanning spectrum detection module and a de-scanning spectrum detection module;
the laser scanning module comprises a light splitting lens and a two-dimensional scanning galvanometer, the supercontinuum laser enters the two-dimensional scanning galvanometer after being reflected by the light splitting lens, and two of the two-dimensional scanning galvanometersThe rotation angle of the two lenses is controlled by a signal generator, and the signal generator generates two-dimensional voltage signal arrays respectively having a voltage signal value of
And
m and N are integers greater than 0, representing the number of points scanned in the X-axis and Y-axis respectively, and the values of the elements of the two arrays are calculated by the following two equations:
,
wherein i is an integer from 1 to M, j is an integer from 1 to N, Vd is a natural number greater than 0, and the two-dimensional voltage signal array is driven by first generating
The initial value of j is set to 1, and then M X-axis scanning voltage signals are generated in sequence, which are defined as:
，
,...
and then adding 1 to the value of j, regenerating M X-axis scanning voltage signals, circulating the steps until the value of j is greater than N, and changing the rotation direction of the two-dimensional scanning galvanometer through the two-dimensional voltage signal array to realize the scanning of the laser at different positions of the fundus oculi.
Preferably, the chromatic dispersion focusing module comprises a reflector, a beam splitter, an electric variable focal length lens and a chromatic dispersion lens, and the laser passing through the two-dimensional scanning vibration mirror is reflected by the reflector and is reflected according to the two-dimensional scanning vibration mirrorThe sub-transmission beam splitting lens, the electric variable focal length lens and the dispersion lens change the phases of different wavelength components in the near infrared spectrum in the super-continuous spectrum laser and focus the components to the scanning position point of the eyeground, and the relation between the scanning position point coordinate of the eyeground and the two-dimensional voltage signal array is
And
wherein
The focal length of an eyeball is shown, laser is focused to an eyeground area by the crystalline lens of the eyeball, the focusing points of different wavelengths are positioned at different depths of the eyeground area, the laser with corresponding wavelength is reflected by the external layer interface of the eyeground in a mirror mode, the laser with other wavelengths is backscattered by the internal layer tissue of the eyeground, the laser reflected in the mirror mode and the backscattered laser are reversely transmitted in a reflected mode, after the laser sequentially passes through the crystalline lens, the dispersive lens and the electric variable focal length lens, part of the laser is reflected by the light splitting lens and enters the non-demodulation scanning spectrum detection module, and part of the light penetrates through the light splitting lens and is reflected back.
Preferably, in the dispersive focusing module, during the two-dimensional galvanometer scanning process, the signal generator sequentially transmits 3 voltages to the electric variable focusing lens, the values of the 3 voltages are natural numbers and are defined as V1, V2 and V3, the electric variable focusing lens generates 3 focal lengths under the three voltages, the peak wavelengths of the three spectra detected by the de-scanning spectrum detection module are lamda1, lamda2 and lamda3 respectively, the value of the peak wavelength is a rational number larger than 0, and the product data of the electric variable focusing lens is inquired to obtain the focal lengths under the three voltages and the three peak wavelengths
，
，
Substituting the three focal lengths into the following three equations:
，
，
where Lz denotes the depth of the focused fundus position,
the method comprises the steps of expressing the focal length of an eyeball, expressing the distance from the eyeground to an equivalent principal point of the eyeball, expressing the distance from the eyeground to the equivalent principal point of the eyeball, expressing the distance from the d to the equivalent principal point of the eyeball and the principal point of the electric variable-focus lens, solving the three equations to obtain the numerical value of Lz, and implementing an execution method of a dispersion focusing module for the scanning position point of each eyeground through galvanometer scanning to obtain the depth data of the scanning position point of each eyeground.
Preferably, the method also comprises a reflection spectrum type oxyhemoglobin saturation detection method, and comprises a data calibration method and an oxyhemoglobin saturation derivation method, wherein in the data calibration method, a standard reflection white plate is placed in front of the dispersive lens, the supercontinuum laser is turned on, and the reference spectrum detection module is used for detecting the reference spectrum
Where lamda represents the wavelength, which is a natural number greater than 0, the supercontinuum laser is turned off, and the dark background spectrum is detected again using the non-unscanned spectrum detection module
During the scanning process of the fundus oculi galvanometer, when the supercontinuum laser is focused on one scanning position point of the fundus oculi, the reflection spectrum of the supercontinuum laser is detected by the non-solution scanning spectrum detection module, and the detection spectrum is
The spectrum after data calibration is
In the method for deriving the blood oxygen saturation, the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin are obtained by querying the data and are respectively defined as
And
the concentrations of the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin at the scanning position point of the fundus oculi are defined as
And
fitting the equation by using the least square method
Three parameters of
，
And
the three parameters are all natural numbers larger than 0, and the natural numbers are fitted by a least square method
And
then, the blood oxygen saturation at the current scanning position point is
A reflection spectrum type blood oxygen saturation detection method is carried out on all scanning position points, and blood oxygen saturation function information of each scanning position point of the whole eyeground is obtained.
Preferably, the supercontinuum laser module comprises a supercontinuum laser, an optical fiber collimator, a polarizer, a laser isolator and a near infrared filter lens, the laser of the supercontinuum laser is used as illumination light and enters the laser scanning module after sequentially passing through the optical fiber collimator, the polarizer, the laser isolator and the near infrared filter lens, the laser scanning module comprises a beam splitting lens and a two-dimensional scanning galvanometer, the supercontinuum laser is reflected by the beam splitting lens, is sequentially reflected by two lenses in the two-dimensional scanning galvanometer and then enters the dispersion focusing module, the dispersion focusing module comprises a reflector, a beam splitting lens, an electric variable focal length lens and a dispersion lens, the supercontinuum laser is reflected by the reflector, passes through the beam splitting lens, the electric variable focal length lens and the dispersion lens, enters the eye and is focused in the fundus region, focus points with different wavelengths are positioned at different depths of the fundus, the supercontinuum laser is reflected by the fundus, is reversely transmitted in a reflected light mode, reversely passes through a dispersion lens and an electric variable focal length lens, part of the laser is reflected by a beam splitting lens in a dispersion focusing module and is detected by a non-de-scanning spectrum detection module, part of the laser penetrates through the beam splitting lens in the dispersion focusing module, is reflected by a reflector and then enters a laser scanning module again, the reflected supercontinuum laser reversely passes through a two-dimensional scanning galvanometer to realize de-scanning, and enters a de-scanning spectrum detection module after passing through the beam splitting lens of the laser scanning module, the de-scanning spectrum detection module obtains the depth information of the current focusing point on the fundus after combining with the dispersion focusing module to obtain the spectrum signal, and the spectrum signal obtained by the non-de-scanning spectrum detection module calculates the blood oxygen saturation information at the current focusing point by a reflection spectrum type blood oxygen saturation detection, in the fundus scanning process, the signal generator generates voltage signals to control the two-dimensional scanning galvanometer and the electric variable focal length lens, the focusing point is subjected to covering type scanning in a fundus two-dimensional area through the scanning of the scanning galvanometer, the depth information and the saturation information of each position of the whole fundus are acquired, and the three-dimensional image detection of the fundus and the functional detection of the blood oxygen saturation degree are realized.
Preferably, the laser generated by the supercontinuum laser module is collimated by the optical fiber collimator, and then passes through the polarizer to purify the linear polarization component of the supercontinuum laser, wherein the polarization direction of the polarizer is parallel to the maximum polarization direction of the supercontinuum laser.
The supercontinuum laser is emitted through the laser isolator, the reflected supercontinuum laser is prevented from entering the supercontinuum laser, the stability of the laser is improved, visible light spectrum components in the supercontinuum laser are filtered out after the reflected supercontinuum laser penetrates through the near-infrared filter lens, the near-infrared spectrum components penetrate through the near-infrared filter lens, and the sensitivity of human eyes to the laser is reduced.
Preferably, the non-de-scanning spectrum detection module comprises a focusing objective lens, a large numerical aperture optical fiber, an analyzer, a focusing lens, a slit, a collimating lens, a grating, an imaging lens and an area array camera, wherein laser reflected by the splitting lens is focused to the input end face of the large numerical aperture optical fiber by the focusing objective lens, the focal plane of the focusing objective lens is superposed with the input end face of the large numerical aperture optical fiber, the laser is transmitted in the optical fiber, and after being emitted through the output end face of the optical fiber, the laser reflected by the front surface of an eyeball is filtered by the analyzer and then is focused to the slit by the focusing lens, the slit and the output end face of the optical fiber are respectively positioned at two sides of the focusing lens, the positions of the slit and the output end face of the optical fiber are optically conjugated, the laser is collimated by the collimating lens after penetrating through the slit, the front focal plane of the collimating lens is superposed with the position of the slit, the collimated and output, the focal plane of the imaging lens coincides with the photosensitive surface of the area-array camera.
Preferably, the de-scanning spectrum detection module comprises an analyzer, a focusing lens, a confocal pinhole, a collimating lens, a grating, an imaging lens and a photosensitive camera, wherein the scanning angle of the reflected laser is relieved after passing through the two-dimensional scanning galvanometer, the reflected laser passes through a beam splitting lens of the laser scanning module, the analyzer filters the reflected laser on the front surface of an eyeball and is focused to the confocal pinhole by the focusing lens, the position of the pinhole is optically conjugate with the outer layer interface point of the fundus region, the laser passes through the confocal pinhole and is collimated by the collimating lens, the front focal plane of the collimating lens coincides with the position of the confocal pinhole, the collimated laser sequentially passes through grating diffraction beam splitting, the diffracted light is focused at the photosensitive camera by the imaging lens, and the focal plane of the imaging lens coincides with the photosensitive surface of the photosensitive camera.
According to the method, the fundus is irradiated by utilizing the near infrared band of the supercontinuum laser, the influence of visible light on human eyes can be reduced, the focusing effect and the imaging resolution can be improved by means of the high spatial coherence of the supercontinuum laser, the depth data of the fundus is calculated by using the de-scanning spectrum detection module and the dispersion focusing point module in the detection and data processing processes of the fundus depth information, the blood oxygen saturation of the fundus is detected and processed by using the large-numerical-aperture two-dimensional optical fiber bundle terminal in the non-de-scanning spectrum detection module, the spectrum detection efficiency is improved, the blood oxygen saturation of each part of the fundus is calculated by using the reflection spectrum type blood oxygen saturation detection method, and the three-dimensional data of the fundus and the functional information of the blood oxygen saturation can be synchronously obtained by the method.
Drawings
Fig. 1 is a schematic diagram of a high-speed functional fundus three-dimensional detection system based on near infrared light.
FIG. 2 is an exploded view of a non-unscanned spectral detection module.
FIG. 3 is an exploded view of the descan spectroscopy detection module.
Detailed Description
In order to make the public more clearly understand the technical spirit and the beneficial effects of the patent of the invention, the applicant shall make the following detailed description by way of example, but the description of the example is not a limitation to the patent solution of the invention, and any equivalent changes made according to the patent idea of the invention, which are only formal and not substantive, shall be regarded as the technical scope of the patent of the invention.
Example 1:
the invention is further described with reference to fig. 1, fig. 2, fig. 3 and example 1.
As shown in the attached figure 1, the system disclosed by the invention is divided into a hardware part and a method part, wherein the hardware part comprises a supercontinuum laser module 1, a laser scanning module 2, a dispersion focusing module 3, a non-unscanning spectrum detection module 4 and an unscanning spectrum detection module 5, the supercontinuum laser module 1 comprises a supercontinuum laser 1-1, an optical fiber collimator 1-2, a polarizer 1-3, a laser isolator 1-4 and a near infrared filter lens 1-5, laser of the supercontinuum laser 1-1 is used as illumination light, and enters the laser scanning module 2 after sequentially passing through the optical fiber collimator 1-2, the polarizer 1-3, the laser isolator 1-4 and the near infrared filter lens 1-5; the laser scanning module 2 comprises a beam splitting lens 2-1 and a two-dimensional scanning galvanometer 2-2, the supercontinuum laser is reflected by the beam splitting lens 2-1 and then is sequentially reflected by two lenses in the two-dimensional scanning galvanometer 2-2 and then enters a dispersion focusing module 3, the dispersion focusing module comprises a reflecting lens 3-1, a beam splitting lens 3-2, an electric variable focal length lens 3-3 and a dispersion lens 3-4, the supercontinuum laser is reflected by the reflecting lens 3-1, passes through the beam splitting lens 3-2, the electric variable focal length lens 3-3 and the dispersion lens 3-4 and then enters the eye and is focused in the fundus region, the focus points with different wavelengths are positioned at different depths of the fundus, the supercontinuum laser is reflected by the fundus, is reversely transmitted in a reflected light form, reversely passes through the dispersion lens 3-4 and the electric variable focal length lens 3-3, part of laser is reflected by a beam splitting lens 3-2 in a dispersion focusing module 3 and is detected by a non-de-scanning spectrum detection module 4, part of laser penetrates through the beam splitting lens 3-2 in the dispersion focusing module 3, is reflected by a reflector 3-1 and then enters a laser scanning module 2 again, the reflected supercontinuum laser reversely passes through a two-dimensional scanning vibrating mirror 2-2 to realize de-scanning, penetrates through the beam splitting lens 2-1 of the laser scanning module 2 and enters a de-scanning spectrum detection module 5, the de-scanning spectrum detection module acquires a spectrum signal by combining with the dispersion focusing module, so that the depth information of a current focusing point on the fundus can be obtained, the spectrum signal acquired by the non-de-scanning spectrum detection module 4 calculates the blood oxygen saturation information at the current focusing point by a reflection spectrum type blood oxygen saturation detection method, in the fundus scanning process, the signal generator 6 generates voltage signals to control the two-dimensional scanning galvanometer 2-2 and the electric variable-focus lens 3-3, and the two-dimensional scanning galvanometer 2-2 scans the focus point in a two-dimensional area of the eyeground in a covering mode to acquire depth information and saturation information of each position of the whole eyeground so as to realize three-dimensional image detection of the eyeground and functional detection of blood oxygen saturation.
As shown in fig. 1, the supercontinuum laser module 1 comprises a supercontinuum laser 1-1, an optical fiber collimator 1-2, a polarizer 1-3, a laser isolator 1-4 and a near infrared filter lens 1-5, wherein laser generated by the supercontinuum laser 1-1 is collimated by the optical fiber collimator 1-2, then penetrates through the polarizer 1-3 to purify a linear polarization component of the supercontinuum laser 1-1, and the polarization direction of the polarizer 1-3 is parallel to the maximum polarization direction of the supercontinuum laser 1-1; the supercontinuum laser is emitted through the laser isolator 1-4, the reflected supercontinuum laser is prevented from entering the supercontinuum laser 1-1, the stability of the laser is improved, visible light spectrum components in the supercontinuum laser are filtered out after the reflected supercontinuum laser penetrates through the near infrared filter lens 1-5, the near infrared spectrum components penetrate through the near infrared filter lens, and the sensitivity of human eyes to the laser is reduced.
As shown in figure 1, the laser scanning module 2 comprises a light splitting lens 2-1 and a two-dimensional scanning galvanometer 2-2, the supercontinuum laser enters the two-dimensional scanning galvanometer 2-2 after being reflected by the light splitting lens 2-1, two lenses in the two-dimensional scanning galvanometer turn the laser transmission direction, the rotation angles of the two lenses are controlled by a signal generator, and the signal generator 6 generates two-dimensional voltage signal arrays which are respectively a two-dimensional voltage signal array
And
m and N are integers greater than 0, representing the number of points scanned in the X-axis and Y-axis respectively, and the values of the elements of the two arrays are calculated by the following two equations:
,
wherein i is an integer from 1 to M, j is an integer from 1 to N, Vd is a natural number greater than 0, and the two-dimensional voltage signal array is driven by first generating
The initial value of j is set to 1, and then M X-axis scanning voltage signals are generated in sequence, which are defined as:
，
,...
and then adding 1 to the value of j, regenerating M X-axis scanning voltage signals, circulating the steps until the value of j is greater than N, and changing the rotation direction of the two-dimensional scanning galvanometer through the two-dimensional voltage signal array to realize the scanning of the laser at different positions of the fundus oculi.
As shown in figure 1, the dispersive focusing module 3 comprises a reflector 3-1, a beam splitter 3-2, an electric variable focal length lens 3-3 and a dispersive lens 3-4, laser passing through a two-dimensional scanning vibrating mirror is reflected by the reflector 3-1, the beam splitter 3-2, the electric variable focal length lens 3-3 and the dispersive lens 3-4 are arranged in sequence, phases of different wavelength components in a near infrared spectrum in the supercontinuum laser are changed, the laser is focused to a scanning position point of an eyeground, and the relation between the scanning position point coordinate of the eyeground and a two-dimensional voltage signal array is
And wherein
Indicating the focal length of the eye, the laser light being focused by the lens of the eye into the fundus region, the different wavelengths of which are focusedThe point is located at different depths of the eyeground area, the mirror image of the outer layer interface of the eyeground reflects the laser with corresponding wavelength, the back scattering of the laser with other wavelength is carried out on the inner layer tissue of the eyeground, the mirror image reflection and the back scattering of the laser are transmitted in reverse direction in a reflection mode, after the mirror image reflection and the back scattering of the laser sequentially pass through the crystalline lens, the dispersive lens 3-4 and the electric variable focal length lens 3-3, part of the laser is reflected by the light splitting lens 3-2 and enters the non-solution scanning spectrum detection module 4, and part of the light penetrates through the light splitting lens 3-2.
As shown in figure 2, the non-unscrambling spectrum detection module comprises a focusing objective lens 4-1, a large numerical aperture optical fiber 4-2, an optical element mounting long tube 4-3, an analyzer 4-4, a focusing lens 4-5, a slit 4-6, an angle matching sleeve 4-7, a collimating lens 4-8, a grating 4-9, an optical element mounting short tube 4-10, an imaging lens 4-11 and an area array camera 4-13, wherein the analyzer 4-4, the focusing lens 4-5 and the slit 4-6 are mounted in the optical element mounting long tube 4-3, the collimating lens 4-8 is mounted in the angle matching sleeve 4-7, the optical element mounting short tube 4-10 is used for mounting the grating 4-9, and the optical element is fixed in the mounting tube and the sleeve by a threaded ring, the inclination angle of the main shaft of the angle matching sleeve 4-7 is equal to the blazed angle of the grating 4-9, the laser reflected by the beam splitting lens is focused to the input end surface of the large numerical aperture optical fiber 2 by the focusing objective 4-1, the focal plane of the focusing objective 4-1 is superposed with the input end surface of the large numerical aperture optical fiber 4-2, the laser is transmitted in the large numerical aperture optical fiber 4-2, after being emitted through the output end surface of the optical fiber, the reflected laser on the front surface of the eyeball is filtered through the analyzer 4-4, then the laser is focused to the slit 4-6 by the focusing lens 4-5, the slit 4-6 and the output end surface of the large numerical aperture optical fiber 4-2 are respectively positioned at the two sides of the focusing lens 4-5, the positions of the slit 4-6 are optically conjugated, the laser after penetrating through the slit 4-6 is collimated by, the front focal plane of the collimating lens 4-8 is coincided with the position of the slit 4-6, the laser output by collimation enters the grating 4-9 for diffraction and light splitting, then is further focused on the area-array camera 4-13 by the imaging lens 4-11, and the focal plane of the imaging lens 4-11 is coincided with the photosensitive surface of the area-array camera 4-13.
As shown in figure 3, the de-scanning spectrum detection module comprises an analyzer 5-1, a focusing lens 5-2, a lens mounting cylinder 5-3, a confocal pinhole 5-4, an optical element mounting cylinder 5-5, a collimating lens 5-6, a grating 5-7, an angle matching cylinder 5-8, an imaging lens 5-9 and a photosensitive camera 5-10, wherein the scanning angle of reflected laser is relieved after passing through a two-dimensional scanning galvanometer, the reflected laser passes through a light splitting lens of the laser scanning module and is filtered by the analyzer 5-1 to remove the reflected laser on the front surface of an eyeball, the focusing lens 5-2 is fixed with the lens mounting cylinder 5-3 through rear threads, the confocal pinhole 5-4 is mounted at the front end of the optical element mounting cylinder 5-5, the collimating lens 5-6 is mounted at the rear end of the optical element mounting cylinder 5-5 after being glued with the grating 5-7, the thread of the focusing lens 5-2 is rotated to realize focusing, laser is focused to a confocal small hole 5-4 by the focusing lens 5-2, the position of the small hole is optically conjugate with an outer layer interface point of an eyeground area, the laser passes through the confocal small hole 5-4 and is collimated by the collimating lens 5-6, a front focal plane of the collimating lens 5-6 is superposed with the position of the confocal small hole 5-4, the collimated laser sequentially diffracts light through the grating 5-7, the diffraction angle of the grating 5-7 is counteracted by the angle matching barrel 5-8, the inclination angle of the central axis of the angle matching barrel 5-8 is equal to the diffraction angle, the diffracted light is focused at the photosensitive camera 5-10 by the imaging lens 5-9, and the focal plane of the imaging lens 5-9 is superposed with the photosensitive surface of the photosensitive camera 5-10.
In the two-dimensional galvanometer scanning process, the dispersive focusing module sequentially transmits 3 voltages to the electric variable focusing lens by the signal generator, the numerical values of the 3 voltages are natural numbers and are defined as V1, V2 and V3, the electric variable focusing lens generates 3 focal lengths under the three voltages, the peak wavelengths of three spectrums detected by the de-scanning spectrum detection module are lambda 1, lambda 2 and lambda 3 respectively, the numerical values of the peak wavelengths are rational numbers larger than 0, and product data of the electric variable focusing lens are inquired to obtain the focal lengths under the three voltages and the three peak wavelengths
，
，
The above-mentionedThree focal lengths are substituted into the following three equations:
，
，
where Lz denotes the depth of the focused fundus position,
the method comprises the steps of expressing the focal length of an eyeball, expressing the distance from the eyeground to an equivalent principal point of the eyeball, expressing the distance from the eyeground to the equivalent principal point of the eyeball, expressing the distance from the d to the equivalent principal point of the eyeball and the principal point of the electric variable-focus lens, solving the three equations to obtain the numerical value of Lz, and implementing an execution method of a dispersion focusing module for the scanning position point of each eyeground through galvanometer scanning to obtain the depth data of the scanning position point of each eyeground.
The reflection spectrum type oxyhemoglobin saturation detection method comprises a data calibration method and an oxyhemoglobin saturation derivation method, wherein in the data calibration method, a standard reflection white plate is placed in front of a dispersion lens, a supercontinuum laser is turned on, and a reference spectrum is detected by a non-solution scanning spectrum detection module
Where lamda represents the wavelength, which is a natural number greater than 0, the supercontinuum laser is turned off, and the dark background spectrum is detected again using the non-unscanned spectrum detection module
During the scanning process of the fundus oculi galvanometer, when the supercontinuum laser is focused on one scanning position point of the fundus oculi, the reflection spectrum of the supercontinuum laser is detected by the non-solution scanning spectrum detection module, and the detection spectrum is
The spectrum after data calibration is
In the method for deriving the blood oxygen saturation, the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin are obtained by querying the data and are respectively defined as
And
the concentrations of the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin at the scanning position point of the fundus oculi are defined as
And
fitting the equation by using the least square method
Three parameters of
，
And
the three parameters are all natural numbers larger than 0, and the natural numbers are fitted by a least square method
And
then, the blood oxygen saturation at the current scanning position point is
For all scanning position pointsThe reflection spectrum type oxyhemoglobin saturation detection method obtains oxyhemoglobin saturation function information of each scanning position point of the whole eyeground.
Claims (6)
1. A high-speed functional fundus three-dimensional detection system based on near-infrared light is characterized in that: the system comprises a supercontinuum laser module, a laser scanning module, a dispersion focusing module, a non-de-scanning spectrum detection module and a de-scanning spectrum detection module;
the laser scanning module comprises a light splitting lens and a two-dimensional scanning galvanometer, supercontinuum laser enters the two-dimensional scanning galvanometer after being reflected by the light splitting lens, two lenses in the two-dimensional scanning galvanometer turn the laser transmission direction, the rotation angles of the two lenses are controlled by a signal generator, and the signal generator generates two-dimensional voltage signal arrays which are respectively a two-dimensional voltage signal array
And
m and N are integers greater than 0, representing the number of points scanned in the X-axis and Y-axis respectively, and the values of the elements of the two arrays are calculated by the following two equations:
,
wherein i is an integer from 1 to M, j is an integer from 1 to N, Vd is a natural number greater than 0, and the two-dimensional voltage signal array is driven by first generating
The initial value of j is set to 1, and then M X-axis scanning voltage signals are generated in sequence, which are defined as:
，
,...
then adding 1 to the value of j, regenerating M X-axis scanning voltage signals, circulating the process until the value of j is greater than N, and changing the rotation direction of the two-dimensional scanning galvanometer through the two-dimensional voltage signal array to realize the scanning of the laser at different positions of the fundus oculi;
the dispersion focusing module comprises a reflector, a beam splitting lens, an electric variable focal length lens and a dispersion lens, laser passing through the two-dimensional scanning vibrating lens is reflected by the reflector and sequentially passes through the beam splitting lens, the electric variable focal length lens and the dispersion lens, the phases of different wavelength components in a near infrared spectrum in the super-continuous spectrum laser are changed, the laser is focused to a scanning position point of the eyeground, and the relation between the scanning position point coordinate of the eyeground and the two-dimensional voltage signal array is
And
wherein
The focal length of an eyeball is represented, laser is focused to an eyeground area by a crystalline lens of the eyeball, focus points of the laser with different wavelengths are positioned at different depths of the eyeground area, the laser with corresponding wavelengths is reflected by an outer layer interface of the eyeground, the laser with other wavelengths is backscattered by an inner layer tissue of the eyeground, the laser reflected by the mirror and backscattered is reversely transmitted in a reflective mode, after the laser sequentially passes through the crystalline lens, a dispersive lens and an electric variable focal length lens, part of the laser is reflected by a beam splitter lens and enters a non-unscanned spectrum detection module, and part of the light penetrates through the beam splitter lens and is reflected back to a laser scanning;
the chromatic dispersion focusing module is as followsIn the scanning process of the two-dimensional galvanometer, 3 voltages are sequentially transmitted to the electric variable focusing lens by the signal generator, the numerical values of the 3 voltages are natural numbers and are defined as V1, V2 and V3, the electric variable focusing lens generates 3 focal lengths under the three voltages, the peak wavelengths of three spectrums detected by the de-scanning spectrum detection module are lambda 1, lambda 2 and lambda 3 respectively, the numerical values of the peak wavelengths are rational numbers larger than 0, and the product data of the electric variable focusing lens is inquired to obtain the focal lengths under the three voltages and the three peak wavelengths
，
，
Substituting the three focal lengths into the following three equations:
，
，
where Lz denotes the depth of the focused fundus position,
expressing the focal length of an eyeball, Lh expressing the distance from the eyeground to an equivalent principal point of the eyeball, d expressing the distance from the equivalent principal point of the eyeball to a principal point of the electric variable-focus lens, solving the three equations to obtain the numerical value of Lz, and implementing an execution method of a dispersion focusing module for the scanning position point of each eyeground through galvanometer scanning to obtain the depth data of the scanning position point of each eyeground;
the supercontinuum laser module comprises a supercontinuum laser, an optical fiber collimator, a polarizer, a laser isolator and a near infrared filter lens, laser of the supercontinuum laser is used as illumination light and enters the laser scanning module after sequentially passing through the optical fiber collimator, the polarizer, the laser isolator and the near infrared filter lens, the laser scanning module comprises a beam splitting lens and a two-dimensional scanning galvanometer, the supercontinuum laser is reflected by the beam splitting lens and then sequentially reflected by two lenses in the two-dimensional scanning galvanometer and then enters a dispersion focusing module, the dispersion focusing module comprises a reflector, a beam splitting lens, an electric variable focal length lens and a dispersion lens, the supercontinuum laser is reflected by the reflector, passes through the beam splitting lens, the electric variable focal length lens and the dispersion lens, enters eyes and is focused in an eyeground area, focus points with different wavelengths are positioned at different depths of the eyeground, the supercontinuum laser is reflected by the fundus, is reversely transmitted in a reflected light mode, reversely passes through a dispersion lens and an electric variable focal length lens, part of the laser is reflected by a beam splitting lens in a dispersion focusing module and is detected by a non-de-scanning spectrum detection module, part of the laser penetrates through the beam splitting lens in the dispersion focusing module, is reflected by a reflector and then enters a laser scanning module again, the reflected supercontinuum laser reversely passes through a two-dimensional scanning galvanometer to realize de-scanning, and enters a de-scanning spectrum detection module after passing through the beam splitting lens of the laser scanning module, the de-scanning spectrum detection module obtains the depth information of the current focusing point on the fundus after combining with the dispersion focusing module to obtain the spectrum signal, and the spectrum signal obtained by the non-de-scanning spectrum detection module calculates the blood oxygen saturation information at the current focusing point by a reflection spectrum type blood oxygen saturation detection, in the fundus scanning process, the signal generator generates voltage signals to control the two-dimensional scanning galvanometer and the electric variable focal length lens, the focusing point is subjected to covering type scanning in a fundus two-dimensional area through the scanning of the scanning galvanometer, the depth information and the saturation information of each position of the whole fundus are acquired, and the three-dimensional image detection of the fundus and the functional detection of the blood oxygen saturation degree are realized.
2. The near-infrared light-based high-speed functional fundus three-dimensional inspection of claim 1A system, characterized by: the method also comprises a data calibration method and a blood oxygen saturation derivation method, wherein in the data calibration method, a standard reflection white plate is placed in front of the dispersive lens, the supercontinuum laser is turned on, and the reference spectrum is detected by the non-solution scanning spectrum detection module
Where lamda represents the wavelength, which is a natural number greater than 0, the supercontinuum laser is turned off, and the dark background spectrum is detected again using the non-unscanned spectrum detection module
During the scanning process of the fundus oculi galvanometer, when the supercontinuum laser is focused on one scanning position point of the fundus oculi, the reflection spectrum of the supercontinuum laser is detected by the non-solution scanning spectrum detection module, and the detection spectrum is
The spectrum after data calibration is
In the method for deriving the blood oxygen saturation, the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin are obtained by querying the data and are respectively defined as
And
the concentrations of the absorption spectra of oxygenated hemoglobin and non-oxygenated hemoglobin at the scanning position point of the fundus oculi are defined as
And
fitting the equation by using the least square method
Three parameters of
，
And
the three parameters are all natural numbers larger than 0, and the natural numbers are fitted by a least square method
And
then, the blood oxygen saturation at the current scanning position point is
A reflection spectrum type blood oxygen saturation detection method is carried out on all scanning position points, and blood oxygen saturation function information of each scanning position point of the whole eyeground is obtained.
3. The near-infrared-light-based high-speed functional fundus three-dimensional detection system according to claim 1, characterized in that the laser generated by the supercontinuum laser module is collimated by the optical fiber collimator, and then passes through the polarizer to purify the linear polarization component of the supercontinuum laser, and the polarization direction of the polarizer is parallel to the maximum polarization direction of the supercontinuum laser.
4. The near-infrared light-based high-speed functional fundus three-dimensional detection system according to claim 3, characterized in that: the super-continuum spectrum laser is emitted through the laser isolator, visible light spectrum components in the super-continuum spectrum laser are filtered after the super-continuum spectrum laser penetrates through the near-infrared filter lens, and the near-infrared spectrum components penetrate through the super-continuum spectrum laser.
5. The near-infrared light-based high-speed functional fundus three-dimensional detection system according to claim 1, characterized in that: the non-unscrambling spectrum detection module is composed of a focusing objective lens, a large numerical aperture optical fiber, an analyzer, a focusing lens, a slit, a collimating lens, a grating, an imaging lens and an area array camera, wherein laser reflected by the beam splitting lens is focused to the input end face of the large numerical aperture optical fiber by the focusing objective lens, the focal plane of the focusing objective lens is superposed with the input end face of the large numerical aperture optical fiber, the laser is transmitted in the optical fiber, after being emitted through the output end face of the optical fiber, the laser reflected by the front surface of an eyeball is filtered through the analyzer and then is focused to the slit by the focusing lens, the slit and the output end face of the optical fiber are respectively positioned at two sides of the focusing lens, the positions of the slit and the output end face of the optical fiber are optically conjugated, the laser is collimated by the collimating lens after penetrating through the slit, the front focal plane of the collimating lens is superposed with the position of the slit, the, the focal plane of the imaging lens coincides with the photosensitive surface of the area-array camera.
6. The near-infrared light-based high-speed functional fundus three-dimensional detection system according to claim 1, it is characterized in that the de-scanning spectrum detection module consists of an analyzer, a focusing lens, a confocal pinhole, a collimating lens, a grating, an imaging lens and a photosensitive camera, after reflected laser passes through a two-dimensional scanning galvanometer, the scanning angle is released, then the reflected laser on the front surface of the eyeball is filtered by the analyzer through the beam splitting lens of the laser scanning module, and the laser is focused to the confocal pinhole by the focusing lens, the position of the small hole is optically conjugated with the outer layer interface point of the eyeground area, after laser passes through the confocal small hole, the collimating lens is used for collimating, the front focal plane of the collimating lens is coincided with the position of the confocal pinhole, the collimated laser sequentially passes through grating diffraction light splitting, the diffracted light is focused at the photosensitive camera by the imaging lens, and the focal plane of the imaging lens is coincided with the photosensitive plane of the photosensitive camera.
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| CN102885612A (en) * | 2012-02-14 | 2013-01-23 | 苏州微清医疗器械有限公司 | Fundus imaging equipment for clinical diagnosis |
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| CN108056754B (en) * | 2017-12-01 | 2020-06-09 | 华中科技大学 | Fast axial scanning photoacoustic microimaging device based on acoustic gradient refractive index mirror |
| CN111272101A (en) * | 2019-12-18 | 2020-06-12 | 浙江大学 | Four-dimensional hyperspectral depth imaging system |
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| CN102885612A (en) * | 2012-02-14 | 2013-01-23 | 苏州微清医疗器械有限公司 | Fundus imaging equipment for clinical diagnosis |
| JP2014045950A (en) * | 2012-08-31 | 2014-03-17 | Canon Inc | Fundus device and ophthalmological lighting method |
| CN206151435U (en) * | 2016-07-11 | 2017-05-10 | 孙明斋 | Multispectral eye ground imaging system |
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