CN213883159U

CN213883159U - Ophthalmic measurement system based on shutter switching

Info

Publication number: CN213883159U
Application number: CN202020735955.2U
Authority: CN
Inventors: 吴蕾; 蔡守东
Original assignee: Shenzhen Certainn Technology Co Ltd
Current assignee: Ganzhou Moting Medical Technology Co ltd; Shenzhen Moting Medical Technology Co ltd
Priority date: 2020-05-07
Filing date: 2020-05-07
Publication date: 2021-08-06
Anticipated expiration: 2030-05-07

Abstract

The embodiment of the application discloses an ophthalmological measurement system based on shutter switching, which comprises a main body module, an optical path switching and scanning device, a first OCT optical path component and a shutter device; the main body module is used for providing measuring light for the optical path switching scanning device; the optical path switching scanning device is used for transmitting the measuring light to the first OCT optical path component; the optical path of the first OCT optical path component is at least a part of the measuring optical path; at least one part of the shutter device can be inserted into the measuring optical path and can be drawn out of the measuring optical path so that the measuring light can irradiate different parts of the eye to be measured, and therefore different parts of the eye to be measured can be measured. The embodiment of the application can improve the definition and the signal-to-noise ratio of the imaging of different parts of the eye to be measured under the condition of limited cost.

Description

Ophthalmic measurement system based on shutter switching

Technical Field

The application relates to the technical field of ophthalmologic measurement, in particular to an ophthalmologic measurement system based on shutter switching.

Background

Nowadays, the number of the elderly suffering from cataract is increasing, and the transplantation of the intraocular lens is an effective scheme for treating cataract which is widely used at present. However, the calculation of the intraocular lens requires many parameters, such as the anterior and posterior surface curvatures of the cornea, the thickness of the cornea, the anterior chamber depth, the thickness of the lens, the anterior and posterior surface curvatures of the lens, the axial length of the eye, the white-to-white distance, the diameter of the pupil, and the like. The measured parameters are more, but the complete data can be obtained after the detection of various medical devices is often needed. Therefore, if a medical apparatus capable of acquiring the data by one apparatus is realized, the convenience of measurement and the accuracy of measurement can be improved for the detection of a patient.

Optical Coherence Tomography (OCT) is a new optical imaging technique, and has the advantages of high resolution, fast imaging speed, no radiation damage, moderate price, compact structure and the like compared with the traditional clinical imaging means, and is an important potential tool for basic medical research and clinical diagnosis application. Currently, among a variety of ophthalmic apparatuses using an optical instrument, an OCT device for ophthalmic examination and treatment has become an indispensable ophthalmic apparatus for ophthalmic disease diagnosis.

Chinese patent application No. 201290000031.1 discloses an ophthalmic optical coherence tomography system. The system adopts a device for rapidly and accurately switching and positioning a plurality of angles, has higher instrument cost, and influences the OCT imaging quality of each tissue in the anterior segment because different focuses are not realized on tissues with different depths in the anterior chamber.

Chinese patent application No. 201810130278.9 discloses an ophthalmologic measurement system and method. The method can not simultaneously realize optical path compensation and focusing position adjustment for tissues with different depths in the anterior chamber, and influences the OCT imaging quality of each tissue in the anterior segment.

Chinese patent application No. 201920204215.3 discloses an ophthalmologic measurement system. The system can not simultaneously realize optical path compensation and focusing position adjustment for tissues with different depths in the anterior chamber, and influences the OCT imaging quality of tissues in the anterior section.

The time domain OCT technology has low cost, the detection depth can be made deeper, but the imaging speed is slow, and the time domain OCT technology is easily influenced by eye movement; the scanning OCT technology has high imaging speed and deep detection depth, but the cost is high. The frequency domain OCT technology has limited imaging depth, but the imaging speed is comparable to that of the frequency sweep OCT technology, and the frequency domain OCT technology has great cost advantage.

The above background disclosure is only for the purpose of assisting in understanding the inventive concepts and technical solutions of the present application and does not necessarily pertain to the prior art of the present application, and should not be used to assess the novelty and inventive step of the present application in the absence of explicit evidence to suggest that such matter has been disclosed at the filing date of the present application.

SUMMERY OF THE UTILITY MODEL

The application provides an ophthalmology measuring system based on shutter switching, which can improve the imaging definition and signal-to-noise ratio of different parts of the eye to be measured under the condition of limited cost.

An ophthalmic measurement system based on shutter switching comprises a main body module, an optical path switching scanning device, a first OCT optical path component and a shutter device;

the main body module is used for providing measuring light for the optical path switching scanning device;

the optical path switching scanning device is used for transmitting the measuring light to the first OCT optical path component;

the optical path of the first OCT optical path component is at least a part of the measuring optical path;

at least one part of the shutter device can be inserted into the measuring optical path and can be drawn out of the measuring optical path so that the measuring light can irradiate different parts of the eye to be measured, and therefore different parts of the eye to be measured can be measured.

In some preferred embodiments, the first OCT optical-path component is an anterior-segment OCT optical-path component for measuring an anterior segment of an eye to be measured; at least a portion of the shutter device is insertable into and withdrawable from the measurement optical path to focus measurement light at different depths of the anterior segment.

In some preferred embodiments, the at least a portion of the shutter device is an insert mirror.

In some preferred embodiments, the shutter device comprises a plurality of insert mirrors.

In some preferred embodiments, the insertion mirrors are used for focusing and/or for adjusting the optical path, each of which can be inserted into the measurement beam path and can be removed from the measurement beam path.

In some preferred embodiments, the shutter device further comprises a shutter switching mechanism; the shutter switching mechanism is used for inserting and extracting the insertion mirror into and from the measurement optical path; and each insertion mirror is inserted into the measuring optical path or drawn out from the measuring optical path through the shutter switching mechanism, so that the measuring light is focused on the positions of the eye to be measured at different depths.

In some preferred embodiments, the specific form of the shutter switching mechanism includes: the quick telescopic mechanism is connected with the insertion mirror; a magnetic mechanism that attracts or repels the insertion mirror by magnetic force; wherein the insertion mirror is inserted into or withdrawn from the measurement optical path in a defined direction by a change of magnetic polarity of the magnetic mechanism.

In some preferred embodiments, the plurality of insertion scopes include a phakic anterior surface insertion scope and a corneal insertion scope.

In some preferred embodiments, at least a portion of the shutter device is insertable into and withdrawable from the optical path of the first OCT optical path component.

In some preferred embodiments, the optical system further comprises a vision fixation optical component and a posterior segment OCT optical path component; the optical path of the fixation optical component is a part of the measuring optical path; the vision fixation optical component and the posterior segment OCT optical path component share a refraction adjusting unit.

In some preferred embodiments, the device further comprises an anterior ocular segment camera assembly; the optical path of the anterior ocular segment camera component is a part of the measuring optical path; the anterior segment imaging assembly shares at least a portion of the optical components with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly, and the fixation optical assembly.

Compared with the prior art, the beneficial effects of the embodiment of the application are as follows:

the measurement light provided by the main body module is transmitted to the first OCT light path component through the light path switching scanning device, and at least one part of the shutter device is inserted into the measurement light path or pulled out of the measurement light path so as to enable the measurement light to irradiate different parts of the eye to be measured. The light path switching scanning device is matched with the shutter device, so that the rapid switching of the light path can be realized, the scanning of different parts of the eye to be detected can also be realized, and the imaging definition and the signal-to-noise ratio of the different parts of the eye to be detected are improved under the condition of limited cost.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments or the background art of the present application, the drawings required to be used in the embodiments or the background art of the present application will be described below.

FIG. 1 illustrates the overall structure of a shutter-switching based ophthalmic measurement system according to one embodiment of the present application;

FIG. 2 illustrates the structure of an anterior segment OCT optical path component and shutter device of an embodiment of the application;

FIG. 3 illustrates a state in which a shutter switching based ophthalmic measurement system according to one embodiment of the present application measures a front surface of a crystal;

FIG. 4 illustrates a state of a shutter-switching based ophthalmic measurement system measuring a cornea according to an embodiment of the present application;

FIG. 5 shows a structure of a posterior segment OCT optical path component of an embodiment of the application;

FIG. 6 illustrates the structure of a fixation optical assembly of one embodiment of the present application;

FIG. 7 shows a configuration of an anterior ocular segment camera assembly according to an embodiment of the present application

Fig. 8 shows a specific structure of a shutter switching-based ophthalmic measurement system according to an embodiment of the present application.

Detailed Description

In order to make the technical problems, technical solutions and advantageous effects to be solved by the embodiments of the present application more clearly apparent, the present application is further described in detail below with reference to fig. 1 to 8 and the embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present application and are not intended to limit the present application.

It will be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or be indirectly on the other element. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or be indirectly connected to the other element. The connection may be for fixation or for circuit connection.

It will be understood that the terms "length," "width," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," and the like, refer to an orientation or positional relationship indicated in the drawings that is solely for the purpose of facilitating the description of the embodiments and simplifying the description, and do not indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and thus should not be considered as limiting the application.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of the embodiments of the present application, "a plurality" means two or more unless specifically defined otherwise.

Referring to fig. 1 and 8, the present embodiment provides a shutter switching based ophthalmic measurement system for measuring an eye to be measured; wherein, the eye to be detected is human eye. The system includes a body module 100 and a detection module 10.

Referring to fig. 1 and 2, the body module 100 includes a light source 1101, a coupler 1103, a reference arm, a detector 1141, and a computer 1143.

The light source 1101 is a weak coherent light source, and outputs light of about near infrared light.

The coupler 1103 is a fiber optic coupler.

The reference arm includes a reference arm optical path lens 1121 and a reference arm mirror 1123.

The detection module 10, which may also be referred to as a sample arm, forms a detection light path, i.e. a measurement light path, during operation. In this embodiment, referring to fig. 1 and fig. 2, the detection module 10 includes a polarization controller 1105, a collimating mirror 1107, an optical path switching scanning device 1109, an anterior segment OCT optical path component 150, a posterior segment OCT optical path component 130, and a shutter device 160. The optical path of the anterior segment OCT optical path component 150 is a part of the measurement optical path; the optical path of the posterior segment OCT optical path component 130 and the optical path of the shutter device 160 are also part of the measurement optical path; alternatively stated, the optical path of anterior segment OCT optical path component 150, the optical path of posterior segment OCT optical path component 130, and the optical path of shutter device 160 form at least a portion of the measurement optical path.

Wherein, the anterior segment OCT optical path component 150 is a first OCT optical path component. In other embodiments, posterior segment OCT optical path component 130 is a first OCT optical path component. It should be noted that posterior segment OCT optical path component 130 is optional in some embodiments.

Referring to fig. 1 and 2, the body module 100 provides reference light to the reference arm through a light source 1101 and measurement light to the detection module 10. Specifically, light output from the light source 1101 provides measurement light to the detection module 10, i.e., the sample arm, and reference light to the reference arm via the coupler 1103. The reference arm has a known length and reflects light back into the coupler 1103 through the reference arm mirror 1123. The detection module 10 supplies measurement light to the eye E to be examined. Light from the sample, i.e. light scattered back by the human eye, passes through the detection module 10, the polarization controller 1105 and light reflected back from the reference arm, and interferes in the coupler 1103. The interference light is detected by the detector 1141, processed by the computer 1143, and finally displayed as an OCT image of the sample to be detected, i.e., human eyes. In this process, the main body module 100 supplies measurement light to the optical path switching scanning device 1109 through the polarization controller 1105 and the collimator mirror 1107. The sample is scanned by the optical path switching scanning device 1109, and tomographic imaging of OCT is realized.

The anterior segment OCT optical path component 150 is used to measure the anterior segment of the human eye E.

The posterior segment OCT optical path component 130 is used to measure the posterior segment of the human eye E.

The optical path switching scanning device 1109 can perform optical path switching of the measurement light from the main body module 100 and can scan the human eye E. The optical path switching scanning device 1109 may be a one-dimensional optical path switching scanning device, and may be two-dimensional or even three-dimensional. Referring to fig. 1, the measurement light is divided into two paths after passing through the optical path switching scanning device 1109, one path of the measurement light is transmitted to the posterior segment OCT optical path component 130, and the other path of the measurement light is transmitted to the anterior segment OCT optical path component 150.

The optical path switching scanning device 1109 performs not only a scanning function but also an optical path switching function. The light path switching scanning device 1109 may adopt vibrating mirror or other high precision positioning structure to meet the requirement of fast switching and scanning of system light path.

In this embodiment, the optical path switching scanning device 1109 switches the optical path of the measuring light by reflecting the measuring light, that is, the optical path switching scanning device 1109 includes a mirror. The optical path switching scanner 1109 is controlled by the computer 1143 and can be located at a position for realizing the imaging of the anterior segment OCT or a position for realizing the imaging of the posterior segment OCT, so as to transmit the measuring light to the anterior segment OCT optical path component 150 or the posterior segment OCT optical path component 130. Specifically, the main body module 10 provides measurement light to the optical path switching scanning device 1109, and the measurement light is divided into two paths after passing through the optical path switching scanning device 1109, one path is directed to the posterior segment OCT optical path component 130, and the other path is directed to the anterior segment OCT optical path component 150 and the shutter device 160; then, the two lights are incident to the eye E to be measured.

Referring to fig. 2, the detection module 10 of the present embodiment further includes a third beam splitter 1307, a fifth beam splitter 1309, and an objective lens 1311. The fifth dichroic 1309 is a front dichroic mirror.

Referring to fig. 1 and 2, the anterior segment OCT optical path component 150 includes a plurality of mirrors to effect the turning of the optical path. Specifically, anterior segment OCT optical path component 150 includes first mirror 1501, first lens 1503, third mirror 1505, fifth mirror 1507, and third lens 1509.

Referring to fig. 1 and 5, the posterior segment OCT optical path component 130 includes an optical path adjusting unit 1301, a first spectroscope 1303, and a diopter adjusting unit 1305. The light adjustment range unit 1301 may be formed by a cube-corner prism, a right-angle prism, or two total reflection mirrors disposed perpendicular to each other. Referring to fig. 5, the light path adjusting unit 1301 changes the light path by translating up and down as shown. The first spectroscope 1303 is a posterior segment of the eye and a fixation spectroscope.

Referring to fig. 2, the shutter device 160 is a shutter-based device. At least a part of the shutter device 160 can be quickly inserted into and withdrawn from the measuring beam path, i.e. at least a part of the shutter device 160 can be quickly moved back and forth. When at least a portion of the shutter device 160 is inserted into the measurement optical path, the measurement optical path is changed from before, so that the measurement is irradiated to a portion of the human eye E, thereby allowing the ophthalmic measurement system to measure the portion; when at least a portion of the shutter device 160 is withdrawn from the measurement optical path, the measurement optical path is also changed from before, so that the measurement light is irradiated to another portion of the human eye E, thereby allowing the ophthalmic measurement system to measure the portion. In this way, the shutter device 160 can irradiate the measuring light to different parts of the human eye E, so that the ophthalmic measuring system can measure different parts of the human eye.

In the present embodiment, at least a part of the shutter device 160 is embodied in the form of an insertion mirror; illustratively, referring to fig. 2, the shutter device 160 includes two insertion mirrors, a phakic front surface insertion mirror 1601 and a corneal insertion mirror 1603, respectively. The ophthalmoscope 1601 is used for focusing and adjusting the optical path. Goniometer membrane insert mirror 1603 is also used for focusing and adjusting the optical path. Illustratively, the insert mirror of the shutter device 160 is a focusing lens.

In the present embodiment, referring to fig. 2, the shutter device 160 further includes a shutter switching mechanism 1610; the shutter switching mechanism 1610 is used to insert and extract the ophthalmoscope 1601 and the goniometric membrane insertion mirror 1603 into and from the measurement optical path. Illustratively, the shutter switching mechanism 1610 is a quick expansion mechanism connected to the ophthalmoscope 1601 and the goniometric lens 1603; wherein, the quick telescopic mechanism can be an electromagnetic telescopic mechanism, such as an electromagnet; when the shutter switching mechanism 1610 expands and contracts rapidly, the ophthalmoscope 1601 and/or the goniometric membrane insertion mirror 1603 are/is driven to expand and contract rapidly, so that the measurement optical path can be inserted and/or extracted. Alternatively, the shutter switching mechanism 1610 attracts or repels the ophthalmoscope 1601 and/or the goniometric membrane insertion mirror 1603 by magnetic force such that the ophthalmoscope 1601 and/or the goniometric membrane insertion mirror 1603 are inserted into and/or withdrawn from the measurement optical path in a defined direction, which may be achieved by a guide rail; that is, the shutter switching mechanism 1610 is a magnetic mechanism whose magnetic pole can be changed, such as by changing the direction of current to change the magnetic pole of a soft magnetic material. Alternatively, the shutter switching mechanism 1610 causes the ophthalmoscope 1601 and/or the goniometric membrane insertion mirror 1603 to be inserted into and/or extracted from the measurement optical path by rotating the ophthalmoscope 1601 and/or the goniometric membrane insertion mirror 1603; that is, the shutter switching mechanism 1610 is a rotatable mechanism.

In this embodiment, anterior segment OCT optical path component 150 is preferably used for OCT imaging of the posterior surface of the crystalline lens, i.e., the posterior surface of the crystalline lens of human eye E. At this time, referring to fig. 2, two pieces of the insertion mirror of the shutter device 160, that is, the anterior lens insertion mirror 1601 and the corneal insertion mirror 1603, are in positions away from the optical path of the anterior segment OCT optical path component 150. That is, when measuring the OCT image of the rear surface of the crystalline lens, the measuring light (may also be referred to as probe light) does not pass through the two pieces of insert lenses of the shutter device 160.

Referring to fig. 3, when measurement of the anterior lens OCT image is performed, an anterior lens insertion lens 1601 of the shutter device 160 is inserted into the optical path of the ophthalmic measurement system, specifically, into the anterior segment OCT optical path; that is, when measuring the OCT image of the lens front surface, the measurement light passes through the ophthalmoscope 1601. Thus, the optical device through which the measurement optical path passes includes an optical path switching scanning device 1109, a first mirror 1501, a first lens 1503, a third mirror 1505, a lens front surface insertion mirror 1601 of the shutter device 160, a fifth mirror 1507, a third lens 1509, a third beam splitter 1307, a fifth beam splitter 1309, and an objective lens 1311.

Specifically, referring to fig. 3, when the measurement of the OCT image of the front surface of the lens is performed, light emitted from the collimator lens 1107 is reflected by the optical path switching scanning device 1109; at this time, the optical path switching scanner 1109 is controlled by the computer 1143 and is located at a position for realizing the OCT imaging of the anterior segment of the eye; the light beam is reflected by the optical path switching scanning device 1109, then reflected by the first mirror 1501, transmitted through the first lens 1503 and the third mirror 1505, transmitted through the anterior lens surface insertion mirror 1601, reflected by the fifth mirror 1507, transmitted through the third lens 1509 and the third beam splitter 1307, reflected by the fifth beam splitter 1309 to the eye objective 1311, and finally converged near the anterior lens surface of the human eye lens by the human eye E. The detection beam of the anterior lens OCT imaging optical path system meets the condition that the OCT beam is focused near the anterior lens surface of the human eye; i.e. such that the measurement light is focused near the front surface of the lens of the human eye. At this time, the optical path switching scanning device 1109 is located at a position just making an included angle between a main optical axis of the incident light from the collimator lens 1107 and a main optical axis of the reflected light be β.

Referring to fig. 4, when measurement of a corneal OCT image is performed, both the ophthalmoscope 1601 and the keratoscope 1603 of the shutter device 160 are inserted into the anterior segment OCT optical path; that is, when measuring an OCT image of the cornea, measurement light passes through the ophthalmoscope 1601 and the keratoscope 1603. Thus, the optical device through which the optical path is measured includes an optical path switching scanning device 1109, a first mirror 1501, a first lens 1503, a third mirror 1505, a lens front surface insertion mirror 1601 and a cornea insertion mirror 1603 of the shutter device 160, a fifth mirror 1507, a third lens 1509, a third beam splitter 1307, a fifth beam splitter 1309, and an objective lens 1311.

Specifically, referring to fig. 4, when an OCT image of the cornea is performed, light emitted from the collimator lens 1107 is reflected by the optical path switching scanning device 1109; at this time, the optical path switching scanner 1109 is controlled by the computer 1143 and is located at a position for realizing the OCT imaging of the anterior segment of the eye; the light beam is reflected by the optical path switching scanning device 1109, sequentially passes through the first lens 1503 by reflection from the first mirror 1501, is transmitted therethrough, is reflected by the third mirror 1505, is transmitted through the anterior lens 1601 and the corneal lens 1603, is reflected by the fifth mirror 1507, is transmitted therethrough by the third lens 1509 and the third beam splitter 1307, is reflected by the fifth beam splitter 1309 to the eye objective 1311, and is finally converged to the cornea of a human eye. The detection beam of the cornea OCT imaging optical path system meets the condition that the OCT beam is focused near the cornea of the human eye; i.e. such that the measurement light is focused near the cornea of the human eye. At this time, the optical path switching scanning device 1109 is located at a position where an angle between the main optical axis of the incident light from the collimator lens 1107 and the main optical axis of the reflected light is β.

Referring to fig. 4 and 2, when OCT imaging is performed on the posterior lens surface of the human eye E after measurement of the OCT image of the cornea is completed, the anterior lens surface inserting lens 1601 and the corneal inserting lens 1603 are both extracted from the optical path of the first OCT optical path component, that is, the anterior segment OCT optical path component 150. It can be seen that at least a portion of the shutter device 160 can focus the measurement light at different depths of the anterior segment of the eye by insertion into and withdrawal from the measurement optical path.

Based on the above, the shutter device 160 is a device for measuring different depths of tissues of the human eye E, and particularly, a device for measuring different depths of tissues of the anterior segment of the human eye E.

It should be noted that, referring to fig. 2, the anterior-posterior relative positions of the anterior lens-measuring surface insertion mirror 1601 and the corneal insertion mirror 1603 are shown schematically; in other embodiments, the positions of the two may be reversed.

According to the above, when different parts of the anterior segment of the eye are measured, the measuring beam is focused on the parts of the human eye E with different depths, and the imaging resolution and the signal-to-noise ratio can be improved under the condition of limited cost.

In other embodiments, at least a portion of the shutter device 160, i.e., the insert lens, is used to measure a portion of the eye under test other than the anterior lens surface and the cornea.

In other embodiments: the shutter device 160 includes at least one insert mirror for focusing and at least one insert mirror for adjusting an optical path; alternatively, the shutter device 160 includes insert mirrors for focusing; alternatively, the shutter device 160 includes an insert mirror for adjusting the optical path length. The measurement light may also be concentrated at different parts of the eye to be measured, depending on the light source 1101 used. The insertion mirrors are matched with each other through the shutter switching mechanism 1610, specifically, the insertion mirrors are inserted into or pulled away from the measuring optical path, so that the measuring light is focused on parts of human eyes E with different depths, and the parts of the human eyes E with different depths are measured; for example, one insertion mirror is inserted into the measurement optical path, and the other insertion mirror is withdrawn from the measurement optical path; alternatively, all the insertion mirrors are inserted into the measurement beam path first and then withdrawn from the measurement beam path.

Referring to fig. 5, when the posterior segment OCT imaging is performed, light emitted from a collimator lens 1107 is reflected by an optical path switching scanning device 1109; at the moment, the optical path switching scanning device 1109 is controlled by the computer 1143 and is positioned at the position for realizing the OCT imaging of the posterior segment of the eye; after being reflected by the optical path switching scanning device 1109, the light beam passes through the light adjusting path unit 1301; the light beam is reflected by the first beam splitter 1303, then passes through the diopter adjustment device 1305 and the third beam splitter 1307, then is reflected by the fifth beam splitter 1309 to the eye objective 1311, and finally is converged to the fundus of the eye through the eye E. The measuring beam of the posterior segment OCT imaging optical path system meets the condition that the central line of the scanning beam is converged near the pupil of the human eye, and the OCT beam is focused on the fundus of the human eye at any moment. At this time, the optical path switching scanning device 1109 is located at a position just making an included angle between the main optical axis of the incident light from the collimator lens 1107 and the main optical axis of the reflected light be α. Aiming at different human eyes (with different diopters), the OCT light beam can be converged on the eye fundus of the human eyes by adjusting a refraction adjusting device 1305 of the eye fundus OCT imaging light path, namely the light beam is focused on the retina; therefore, the signal-to-noise ratio and the transverse resolution of the OCT image can be effectively improved when retina measurement is carried out.

According to the above, in this embodiment, the optical path switching scanning device 1109 capable of operating rapidly is matched with the shutter device 160, so that not only can the optical paths of the anterior segment and the posterior segment be switched rapidly, but also the scanning, focusing and optical path compensation of different depths of the anterior segment can be realized, and the definition and signal-to-noise ratio of the imaging at different depth positions of the anterior segment can be improved. The embodiment reasonably distributes the cost control and the signal-to-noise ratio of the front-section OCT signal acquisition and the back-section OCT signal acquisition, and can improve the OCT imaging quality of different-depth tissues of the anterior chamber of the eye under the condition of limited cost; the method can realize the detection of a plurality of optical parameters of human eyes, thereby meeting the requirements of measurement of different parts, obtaining accurate data of a plurality of important parameters of human eyes and meeting the requirements of clinical diagnosis of doctors.

The anterior segment OCT optical path component 150 shares the third beam splitter 1307, the fifth beam splitter 1309, and the ocular objective 1311 with the posterior segment OCT optical path component 130.

In other embodiments, anterior segment OCT optical path assembly 150 and posterior segment OCT optical path assembly 130 each comprise the aforementioned third spectroscope 1307, fifth spectroscope 1309, and the aforementioned objective lens 1311. That is, the aforementioned third spectroscope 1307, fifth spectroscope 1309, and the aforementioned objective lens 1311 are divided into the anterior segment OCT optical path component 150 and the posterior segment OCT optical path component 130.

Referring to fig. 1, the detection module 10 of the present embodiment further includes a fixation optical assembly 170. The optical path of fixation optics 170 is part of the measurement optical path of the ophthalmic measurement system.

Referring to fig. 6, the fixation optical assembly 170 includes a fixation light source 1701, a fifth lens 1703, a first spectroscope 1303, and a dioptric adjustment unit 1305. It can be seen that the fixation optical assembly 170 shares a part of the optical components with the posterior segment OCT optical path assembly 130, i.e., shares the first beam splitter 1303 and the diopter adjustment unit 1305.

The first spectroscope 1303 can transmit fixation light (wavelength 550nm) emitted from the fixation light source 1701 in the fixation optical assembly 170 and can reflect light output from the light source 1101.

The third beam splitter 1307 may reflect fixation light emitted from the fixation light source 1701 in the fixation optical assembly 170, and partially transmit and partially reflect light output from the light source 1101.

The fifth beam splitter 1309 can reflect not only the signal light emitted from the light source 1101 but also the fixation light (wavelength may be 550nm) emitted from the fixation light source 1701 in the fixation optical assembly 170.

The fixation light source 1701 is a fixation target (internal fixation target) for fixing the eye E of the subject. The fixation light source 1701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, etc.

The light emitted by the fixation optical assembly 170 is incident on the human eye E to be measured after passing through the posterior segment OCT optical path assembly 130. Specifically, light from the fixation light source 1701 passes through the fifth lens 1703, passes through the first spectroscope 1303, is diopter-adjusted by the diopter adjustment unit 1305, and after reflection by the third spectroscope 1307 and reflection by the fifth spectroscope 1309, the light is re-incident to the eye E through the objective lens 1311. Finally, the internal fixation index is projected to the fundus of the eye E of the subject. When fundus OCT imaging, namely posterior segment OCT imaging, is carried out, when different human eyes observe fixation points, the definition degrees of the fixation points are different, discomfort is caused to a tested person when the tested person fixes the vision, and the fixation and fixation of the tested person eyes are inconvenient. After the optical path of the fundus OCT is adjusted and bent by the refraction adjusting unit 1305, the fundus OCT can be focused on the retina of the fundus, namely, the human eyes can see the scanning line clearly. Because the posterior segment OCT optical path and the fixation optical path share the refraction adjusting unit 1305, the fixation sighting mark can be seen clearly for different human eyes.

Referring to fig. 1, the detection module 10 of the present embodiment further includes an anterior ocular segment camera assembly 190; the assembly can be used for photographing and previewing the anterior segment of the eye so as to guide a doctor to operate an instrument and enable the optical path of the probe to be aligned with the eye of a person to be detected. The optical path of the anterior ocular segment camera assembly 190 is part of the measurement optical path of the ophthalmic measurement system.

Referring to fig. 7, the anterior segment camera module 190 includes an illumination light source 1901, a seventh lens 1905, a seventh mirror 1907, a ninth lens 1909, and a camera unit 1911; the illumination light source 1901 is an infrared illumination light source.

The fifth beamsplitter 1309 is also capable of transmitting illumination light from an illumination light source 1901 in the anterior segment camera assembly 190.

The light emitted by the illumination light source 1901 is irradiated to the anterior chamber of the eye E to be detected, and the light is reflected or scattered by the anterior chamber tissue; the return light passes through the objective lens 1311 and the fifth beam splitter 1309, then passes through the seventh lens 1905, is reflected by the seventh mirror 1907, passes through the ninth lens 1909, and is finally captured by the imaging unit 1911.

The examiner fixes the head of the examinee using the lower jaw support unit (not shown), and fixes the eye of the examinee to the fixation mark of the fixation system, that is, the fixation mark of the fixation optical assembly 170. Then, the examiner controls the movement of the chin rest, the probe, and the like by the operation lever while observing the display screen of the computer 1143, so that the anterior segment of the eye E of the examinee enters the imaging unit 1911 and an image of the anterior segment is displayed on the display screen of the computer 1143.

In other embodiments, the anterior segment camera assembly 190 further comprises a fifth beamsplitter 1309 and an eye objective 1311. As can be seen, the anterior segment imaging assembly 190 shares at least a part of optical components with the anterior segment OCT optical path assembly 150, the posterior segment OCT optical path assembly 130, and the fixation optical assembly 170, that is, shares the fifth spectroscope 1309 and the objective lens 1311, so that the optical path can be simplified.

In the embodiment of the present application, the optical path switching is realized by controlling the optical path switching scanning device 1109 and the shutter device 160 through the computer, so that OCT imaging of different parts of human eyes can be realized. The posterior segment OCT optical path component 130 can obtain important parameters of human eye structures such as retina thickness and the like; the anterior segment OCT optical path component 150 can obtain OCT images of the anterior and posterior surfaces of a cornea and a crystalline lens by matching with the anterior segment OCT imaging shutter device 160 with different depth tissues, so that important parameters of human eye structures such as the anterior and posterior surface curvature of the cornea, the thickness of the cornea, the anterior chamber depth, the thickness of the crystalline lens, the anterior and posterior surface curvature of the crystalline lens and the like can be obtained; the anterior segment OCT optical path component 150 is matched with the posterior segment OCT optical path component 130, so that important parameters of human eye structures such as the length of an eye axis can be obtained; the anterior segment camera assembly 190 can obtain important parameters of the human eye structure such as white-to-white distance, pupil diameter and the like.

The shutter device-combined fast switching anterior-posterior segment OCT imaging system of the embodiment of the application comprises: on one hand, the OCT system has a quick switching function, can realize measurement on parts of objects at different depths, can improve the detection range (front and back imaging) of the OCT system, has stable switching system and accurate positioning, and does not influence the signal-to-noise ratio of the system; on the other hand, the OCT imaging system can realize the respective focusing of light beams at different positions, can realize high-quality OCT imaging of different parts aiming at human eyes with different eyesight, and has higher transverse resolution. The OCT system can obtain a plurality of parameter data of the human eye, such as corneal curvature, corneal thickness, anterior chamber depth, lens thickness, lens surface curvature, eye axial length, white-to-white distance, pupil diameter and the like. The embodiment of the application can focus on tissues of different depths of a human eye, such as a cornea, a front surface of a crystalline lens, a rear surface of the crystalline lens and a retina respectively, so that the signal-to-noise ratio and the resolution of OCT detection of different tissues can be improved.

In the embodiment of the present application, the switching scanning device 119 capable of fast operating cooperates with the shutter device 160, so that not only the fast switching of the front and rear optical paths can be realized, but also the scanning of the front and rear sections can be realized. Meanwhile, the shutter device 160 is adopted, so that the tissues focused at different depths of the anterior chamber of the human eye in the anterior segment measuring process can be realized, and the signal-to-noise ratio in the anterior-posterior segment OCT measuring process is improved. The lens inserted by the shutter device 160 not only realizes the optical path adjusting function, but also has the function of changing the focusing position, can expand the detection depth of the OCT system, and can solve the problem that OCT imaging of the detection depth from the cornea to the back surface of the crystalline lens cannot be realized.

The embodiment of the application also has the following characteristics.

The probe light path requires OCT imaging of different parts of human eye, but the scanning mode and focusing position adopted by the probe light path are different, so the light path adopted by measurement is different. During fundus OCT imaging, the central line of a scanning beam is required to be converged at the pupil of a human eye, and an OCT beam at any moment is incident to the human eye in parallel; when the anterior segment of the eye is imaged, the OCT light beam at any time is required to be focused on tissues of different depths of the anterior segment of the eye.

The equal optical path surface is positioned on the retina of the human eye during the OCT imaging of the fundus, the equal optical path surface is positioned on the cornea during the imaging of the cornea, the equal optical path surface is positioned on the front surface of the crystalline lens during the imaging of the front surface of the crystalline lens, the equal optical path surface is positioned on the rear surface of the crystalline lens during the imaging of the rear surface of the crystalline lens, and the OCT imaging of different parts can be realized without adjusting the optical path of the reference arm.

The refraction compensation can be carried out aiming at human eyes with different eyesight, and human eye imaging at different parts is realized.

The optical path for fixing the vision of the human eyes is provided, and the fixation of the vision of the left eye and the right eye can be met.

Because the probe optical path design abandons the traditional fundus imaging optical path (such as a color fundus camera, an LSLO and the like), the anterior segment camera assembly 190 guides a doctor to operate the instrument and can be used for measuring the diameter of the pupil and the white-to-white distance.

And the fast and accurate switching device is adopted, so that fast OCT imaging of different parts of human eyes can be realized.

On the basis of OCT imaging of different parts of human eyes, the rapid and accurate measurement of the axial length of the eye, the anterior chamber depth, the lens thickness and the like can be realized without moving a reference arm.

The fixation optical path and the posterior segment OCT share the refraction adjusting unit, so that moving parts of the fixation optical path can be reduced, the fixation optical path and the posterior segment OCT optical path are confocal, and the fixation of the tested human eye and the acquisition of the fundus OCT image are facilitated.

Compared with a time domain system, the method has the advantages that a frequency domain optical coherence tomography technology is adopted, the scanning imaging speed is high, the imaging resolution is high, and the detection depth is shallow; compared with the scanning frequency domain optical coherence tomography, the scanning speed, the resolution ratio and the like are equivalent, the cost is much lower, and the detection depth is shallow.

The embodiment of the application adopts the method for rapidly switching scanning to realize rapid switching scanning of the front section and the rear section, almost realizes quasi-real time, can realize scanning of dozens of pictures per second, is high in speed, and can avoid the influence of irregular movement of human eyes, thereby accurately measuring the axial length of the human eyes.

According to the embodiment of the application, the front and back images are acquired by one-time measurement, so that the operation of a doctor is facilitated, the diagnosis speed can be increased, and the doctor-patient interaction experience can be improved; the other measurement realizes the detection of a plurality of human eye key parameters such as cornea, anterior chamber depth, eye axial length, corneal curvature, white to white and the like; its advantages are high cost, speed, precision and multiple functions.

The ophthalmologic measuring system in the embodiment of the application is a multifunctional ophthalmologic measuring system, is mainly used for measuring relevant optical parameters of the eyes of patients, is used for guiding the selection of parameters of intraocular lenses and the examination of the eyes of the patients, and can measure a plurality of ophthalmologic relevant parameters such as axial length, corneal curvature, anterior chamber depth, white-to-white distance and the like of the eyes. The ophthalmological measurement system of the embodiment of the application is mainly based on the optical coherence tomography technology; the optical coherence tomography technology is combined with the quick switching scanning of the front section and the rear section to realize the measurement of the axial length of the human eye, the measurement of the anterior chamber depth, the measurement of the crystal thickness and the measurement of the cornea thickness, and finally realize the measurement of a plurality of optical parameters of the human eye.

The foregoing is a further detailed description of the present application in connection with specific/preferred embodiments and is not intended to limit the present application to that particular description. For a person skilled in the art to which the present application pertains, several alternatives or modifications to the described embodiments may be made without departing from the concept of the present application, and these alternatives or modifications should be considered as falling within the scope of the present application.

Claims

1. An ophthalmic measurement system based on shutter switching, characterized by: the OCT optical path scanning device comprises a main body module, an optical path switching scanning device, a first OCT optical path component and a shutter device;

2. The ophthalmic measurement system of claim 1, wherein: the first OCT optical path component is an anterior segment OCT optical path component used for measuring the anterior segment of the eye to be measured; at least a portion of the shutter device is insertable into and withdrawable from the measurement optical path to focus measurement light at different depths of the anterior segment.

3. The ophthalmic measurement system of claim 1, wherein: at least a portion of the shutter device is an insert mirror.

4. The ophthalmic measurement system of claim 1, wherein: the shutter device includes a plurality of insert mirrors.

5. The ophthalmic measurement system of claim 4, wherein: the insertion mirror is used for focusing and/or adjusting an optical length; each of the insertion mirrors is insertable into and withdrawable from the measurement light path.

6. The ophthalmic measurement system of claim 4, wherein: the shutter device further comprises a shutter switching mechanism; the shutter switching mechanism is used for inserting and extracting the insertion mirror into and from the measurement optical path; and each insertion mirror is inserted into the measuring optical path or drawn out from the measuring optical path through the shutter switching mechanism, so that the measuring light is focused on the positions of the eye to be measured at different depths.

7. The ophthalmic measurement system of claim 4, wherein: the plurality of insertion lenses includes a phakic anterior surface insertion lens and a corneal insertion lens.

8. The ophthalmic measurement system of claim 1, wherein: at least a portion of the shutter device is insertable into and withdrawable from the optical path of the first OCT optical path component.

9. The ophthalmic measurement system of claim 2, wherein: the device also comprises a vision fixation optical component and a posterior segment OCT optical path component; the optical path of the fixation optical component is a part of the measuring optical path; the vision fixation optical component and the posterior segment OCT optical path component share a refraction adjusting unit.

10. The ophthalmic measurement system of claim 9, wherein: the device also comprises an anterior ocular segment camera shooting component; the optical path of the anterior ocular segment camera component is a part of the measuring optical path; the anterior segment imaging assembly shares at least a portion of the optical components with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly, and the fixation optical assembly.