Retinal imaging apparatus and method

Abstract

The present application provides a retinal imaging apparatus and a retinal imaging method. The apparatus comprises a light source detection module, a beam scanning module and an acquisition control module. The light source detection module comprises a light source module and a detection module, imaging light generated by the light source module is incident to the beam scanning module, and the beam scanning module comprises galvanometer scanners. A beam modulated by the beam scanning module enters an eyeball, and a feedback beam formed by the retina is incident to the detection module by means of the beam scanning module. The detection module comprises a bundle of collection optical fibers. The bundle of collection optical fibers comprises 2N+1 collection optical fibers, wherein at least some of the 2N collection optical fibers are symmetrically distributed by using one collection optical fiber as the center, and N is greater than or equal to 1. The acquisition control module is separately connected to the light source detection module and the beam scanning module. The apparatus can image a specific strong scattering and weak reflection microstructure on the human retina, and possesses good intrinsic contrast, improving the comprehensiveness of information acquisition and imaging contrast.

Description

Retinal imaging device and method thereof

[0001] The present application claims priority to the Chinese patent application No. CN202410729198.0, filed on June 6, 2024, and entitled "Retinal imaging device and method thereof", the content of which is incorporated herein by reference in its entirety. TECHNICAL FIELD

[0002] The present application relates to the technical field of retinal imaging, in particular to a retinal imaging device and method thereof. BACKGROUND

[0003] The retina is an important component of the eye. Currently, retinal-related diseases are becoming more and more common worldwide. Therefore, a high-resolution retinal imaging device is of great significance for the diagnosis and efficacy evaluation of retinal-related diseases.

[0004] Liang Junzhong et al. (Liang et al. "Supernormal vision and high-resolution retinal imaging through adaptive optics", J. Opt. Soc. Am. A / Vol. 14, No. 11 / Nov. 1997) proposed a reflective adaptive optics retinal imaging device, which can dynamically detect in real time, compensate for human eye aberrations, and improve the lateral resolution by an order of magnitude, achieving the effect of observing retinal photoreceptor cells and microvessels. However, the imaging contrast of the device is low, and the reflective imaging lacks good endogenous contrast for specific strong scattering and weak reflection microstructures on the human retina, such as blood vessel walls, red blood cells, and photoreceptor cell inner segments, limiting the comprehensiveness of the obtained information. SUMMARY

[0005] Therefore, the present application provides a retinal imaging device and a retinal imaging method, as follows:

[0006] A retinal imaging device, comprising: a light source detection module, a light beam scanning module, and an acquisition control module, the light source detection module comprising a light source module and a detection module, the light source module generating imaging light incident to the light beam scanning module, the light beam scanning module comprising a scanning galvanometer;

[0007] The modulated light beam of the light beam scanning module enters the eyeball, and the feedback light beam formed by the retina is incident to the detection module through the light beam scanning module. The detection module comprises a collection optical fiber bundle, and the collection optical fiber bundle comprises 2N+1 collection optical fibers, wherein 2N collection optical fibers are symmetrically distributed at least in part around one collection optical fiber, and N≥1.

[0008] The acquisition control module is connected with the light source detection module and the light beam scanning module respectively.

[0009] Optionally, the light beam scanning module further comprises a wavefront modulator; the detection module detects the feedback light beam through two light paths, wherein the first light path comprises the collection fiber bundle, and the second light path comprises a wavefront sensor.

[0010] Optionally, the detection module further comprises an insertable beamlet assembly, and the feedback light beam enters the collection fiber bundle through the beamlet assembly.

[0011] Optionally, the light source module comprises one or more light sources and a signal transmission path corresponding to each light source, and the imaging light generated by the light source enters the light beam scanning module through the signal transmission path.

[0012] Optionally, the signal transmission path is an optical fiber, the light source module comprises a plurality of light sources and a plurality of emission optical fibers, and the end faces of the plurality of emission optical fibers are located on a straight line.

[0013] Optionally, the light beam scanning module further comprises a plurality of optical conjugate components, the plurality of optical conjugate components form a plurality of eyeball pupil conjugate planes, and the scanning galvanometer, the eyeball and the light source module are located on different eyeball pupil conjugate planes respectively.

[0014] Optionally, the light beam scanning module further comprises a tracking galvanometer and / or a wavefront modulator, and the tracking galvanometer and / or the wavefront modulator, the scanning galvanometer, the eyeball and the light source module are located on different eyeball pupil conjugate planes respectively.

[0015] A retinal imaging method based on any one of the above-mentioned retinal imaging devices, the retinal imaging device comprising at least one working mode, the retinal imaging method comprising:

[0016] In the first working mode, imaging light is generated by the light source module, the imaging light generated by the light source module enters the light beam scanning module, the light beam modulated by the light beam scanning module enters the eyeball, and the feedback light beam formed by the reflection and scattering of the retina enters the detection module through the light beam scanning module, wherein the center collection fiber in the collection fiber bundle is used to collect the reflection signal, and at least part of the other 2N collection fibers in the collection fiber bundle is used to collect the scattering signal.

[0017] The confocal image of the retina is obtained based on the reflection signal obtained by the collection fiber bundle, and the non-confocal image of the retina is obtained based on the scattering signal obtained by the collection fiber bundle.

[0018] Optionally, the light source module comprises a plurality of light sources and a signal transmission path corresponding to each of the light sources, the imaging light generated by the light sources is incident to the light beam scanning module through the signal transmission path; the retinal imaging method further comprises:

[0019] In the second working mode, the imaging light is generated by the plurality of light sources in the light source module, the imaging light generated by the plurality of light sources is incident to the light beam scanning module, the light beam modulated by the light beam scanning module enters the eyeball, and the feedback light beam formed by the retina is incident to the plurality of collection optical fibers corresponding to the signal transmission path in the collection optical fiber bundle in the detection module through the light beam scanning module;

[0020] The confocal image of the retina is obtained based on the reflection signals in the feedback light beam obtained by the collection optical fiber bundle.

[0021] Optionally, the retinal imaging method further comprises:

[0022] In the third working mode, the beam shrinking assembly is inserted into the detection module, so that the feedback light beam formed by the retina is modulated by the beam shrinking assembly and then transmitted to the 2N+1 collection optical fibers of the collection optical fiber bundle;

[0023] The super-resolution confocal image of the retina is obtained based on the reflection signals in the feedback light beam obtained by the collection optical fiber bundle.

[0024] When the retinal imaging device provided by the embodiment of the application works in the first working mode, the imaging light generated by the light source module is incident to the light beam scanning module, enters the eyeball after being modulated by the light beam scanning module, and the feedback light beam formed by the reflection and scattering of the retina is incident to the detection module through the light beam scanning module, and is output to the acquisition control module through the detection module, wherein the reflection signals from the retina in the feedback light beam are collected by the center collection optical fiber (one collection optical fiber in the center region of the collection optical fiber bundle is the center collection optical fiber, and the other 2N collection optical fibers are non-center collection optical fibers) in the collection optical fiber bundle, and the scattering signals from the retina in the feedback light beam are collected by the non-center collection optical fibers in the collection optical fiber bundle, that is, at least part of the symmetrically distributed collection optical fibers (that is, the surrounding collection optical fibers) other than the center collection optical fiber in the collection optical fiber bundle, the specific strong scattering and weak reflection microstructure on the human eye retina, such as blood vessel wall, red blood cell, and inner segment of photoreceptor cell, can be imaged, which has good endogenous contrast and improves the comprehensiveness of the acquired information and the imaging contrast. BRIEF DESCRIPTION OF DRAWINGS

[0025] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the related art, the following will briefly introduce the drawings needed to be used in the embodiments or prior art description. Obviously, the drawings in the following description only constitute the embodiments of the present application, and for those skilled in the art, other drawings can also be obtained without creative effort based on the provided drawings.

[0026] The structures, proportions, sizes, etc. shown in the drawings of the present specification are only used to cooperate with the content disclosed in the present specification, to be understood and read by those skilled in the art, and do not have technical significance, so any modification of the structure, change of the proportional relationship or adjustment of the size, which does not affect the effects and purposes that can be achieved by the present application, should still fall within the scope of the technical content disclosed by the present application.

[0027] Fig. 1 is a schematic diagram of an optical path of a retinal imaging device provided by an embodiment of the present application when working in a first working mode;

[0028] Fig. 2 is a schematic diagram of the structure of a collection fiber bundle in a retinal imaging device provided by an embodiment of the present application;

[0029] Fig. 3 is a schematic diagram of the structure of a collection fiber bundle in a retinal imaging device provided by another embodiment of the present application;

[0030] Fig. 4 is a schematic diagram of fundus scanning when a retinal imaging device provided by an embodiment of the present application works in the first working mode;

[0031] Fig. 5 is a schematic diagram of signal distribution in a collection fiber bundle when a retinal imaging device provided by an embodiment of the present application works in the first working mode;

[0032] Fig. 6 is a schematic diagram of an optical path of a retinal imaging device provided by an embodiment of the present application when working in a second working mode;

[0033] Fig. 7 is a schematic diagram of signal distribution in a collection fiber bundle when a retinal imaging device provided by an embodiment of the present application works in the second working mode;

[0034] Fig. 8 is a schematic diagram of fundus scanning when a retinal imaging device provided by an embodiment of the present application works in the second working mode;

[0035] Fig. 9 is a schematic diagram of the structure of a retinal imaging device provided by an embodiment of the present application, in which a beam-reducing assembly is not located in a first optical path;

[0036] Fig. 10 is a schematic diagram of the structure of a retinal imaging device provided by an embodiment of the present application, in which a beam-reducing assembly is located in a first optical path;

[0037] Fig. 11 is a diagram of signal distribution in a collection fiber bundle of a retinal imaging device according to an embodiment of the present application when the device is working in a third working mode;

[0038] Fig. 12 is a diagram of a structure of a collection control module of a retinal imaging device according to an embodiment of the present application. DETAILED DESCRIPTION

[0039] The embodiments of the present application will be described in detail below with reference to the drawings. It should be noted that the embodiments described below are only some of the embodiments of the present application, but not all of them. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without creative efforts fall within the scope of the present application.

[0040] Various modifications and changes can be made to the present application without departing from the spirit and scope of the present application. Thus, the present application intends to cover all modifications and changes falling within the scope of the corresponding claims (the claimed technical solutions) and their equivalents. It should be noted that the embodiments provided by the embodiments of the present application can be combined with each other without contradiction.

[0041] In order to make the above-mentioned purposes, features and advantages of the present application more obvious and easy to understand, the present application will be further described in detail below with reference to the drawings and specific embodiments.

[0042] As described in the background section, the imaging contrast of the existing adaptive optical retinal imaging device is low. The reflection imaging of specific strong scattering and weak reflection microstructures on the human eye retina, such as blood vessel walls, red blood cells, and photoreceptor inner segments, lacks good endogenous contrast, which limits the comprehensiveness of the obtained information.

[0043] In addition, the existing adaptive optical retinal imaging device also has the following problems: 1. trade-off between resolution and signal-to-noise ratio. Due to the confocal principle, achieving higher resolution means lower signal-to-noise ratio. For the dense cone cells near the fovea of the human eye, it is difficult to obtain high signal-to-noise ratio signals; 2. slow imaging speed. The imaging speed is limited by the mechanical performance of the galvanometer scanning, and it is difficult to observe high-speed dynamic information such as ocular fundus blood flow in real time.

[0044] In view of the above, the embodiment of the present application provides a retinal imaging device, as shown in Fig. 1, which comprises a light source detection module 100, a light beam scanning module 200 and a collection control module 300; wherein the light source detection module 100 comprises a light source module 101 and a detection module 110, the imaging light generated by the light source module 101 is incident to the light beam scanning module 200, the light beam scanning module 200 comprises a scanning galvanometer; the modulated light beam of the light beam scanning module 200 enters the eyeball, and the feedback light beam formed by the retina is incident to the detection module 110 through the light beam scanning module 200, the detection module 110 comprises a collection optical fiber bundle 106, as shown in Fig. 2, the collection optical fiber bundle 106 comprises 2N+1 collection optical fibers, wherein 2N collection optical fibers are symmetrically distributed at least in part with one collection optical fiber as the center, and N≥1; the collection control module 300 is connected with the light source detection module 100 and the light beam scanning module 200 respectively.

[0045] Optionally, in an embodiment of the present application, the 2N collection optical fibers are circularly symmetrically arranged with one collection optical fiber as the center, and as shown in Fig. 2, the optical fibers can be closely arranged or arranged at intervals, but the present application does not make any limitation thereon, and in other embodiments of the present application, the 2N+1 collection optical fibers can also be arranged in other ways, such as rectangular arrangement, as shown in Fig. 3, and the present application does not make any limitation thereon, and the specific arrangement is determined according to the situation. It should be noted that the 2N collection optical fibers do not require all to be symmetrically distributed, but only a part of them needs to be symmetrically distributed, such as only one group of optical fibers which are symmetrically arranged with the center optical fiber as the point, and the arrangement positions of the remaining optical fibers are not limited.

[0046] When the retinal imaging device provided in the embodiments of the present application works in the first working mode, the imaging light generated by the light source module 101 is incident to the light beam scanning module 200, is modulated by the light beam scanning module 200, and then enters the eyeball. The feedback light beams formed by the reflection and scattering of the retina are incident to the detection module 110 through the light beam scanning module 200, and are output to the collection control module 300 through the detection module 110. In the feedback light beams, the reflection signals from the retina are collected by the central collection optical fiber (one of the collection optical fibers in the central region of the collection optical fiber bundle is the central collection optical fiber, and the other 2N collection optical fibers are non-central collection optical fibers) in the collection optical fiber bundle. The scattering signals from the retina in the feedback light beams are collected by at least part of the non-central collection optical fibers, i.e., at least part of the other 2N collection optical fibers (i.e., the surrounding collection optical fibers) in the collection optical fiber bundle except the central collection optical fiber. In the 2N collection optical fibers, the surrounding collection optical fibers symmetrically distributed are a group (for example, in FIG. 2, every two surrounding collection optical fibers symmetrically distributed with the central collection optical fiber as the center are a group). Therefore, when the collection control module 300 obtains the non-confocal image based on the scattering signals of the feedback light beams (hereinafter referred to as the “non-confocal imaging mode” in the embodiments), the signals output by each group of surrounding collection optical fibers can be differentially subtracted to obtain the scattering light signals enhanced in a specific direction, and then the signals of multiple groups are filtered and superimposed (for example, in FIG. 2, there are three groups of signals), and finally the enhanced signals from the scattering bodies in the fundus are restored. Therefore, the embodiments can image the specific strong scattering and weak reflection microstructures on the human retina, such as the blood vessel wall, the red blood cell, and the inner segment of the photoreceptor cell, and have good endogenous contrast, thereby improving the comprehensiveness of the obtained information and the imaging contrast.

[0047] It should be noted that in the above embodiments, the collection control module 300 of the retinal imaging device provided in the embodiments of the present application can also obtain the confocal image of the retina through the reflection signals transmitted by the central collection optical fiber.

[0048] On the basis of any of the above embodiments, in an embodiment of the present application, the light source module 101 includes at least one light source and at least one signal transmission path, and the signal transmission path corresponds to the light source one by one, that is, the light source module 101 includes one or more light sources and the signal transmission path corresponding to the light source one by one. The imaging light generated by the light source is incident to the light beam scanning module through the signal transmission path. Specifically, in an embodiment of the present application, the light source is an infrared light source, which can be an infrared laser, an infrared band super radiation light emitting diode, or a super-continuum laser, and the present application does not make any limitation thereon, which is determined according to the specific situation.

[0049] It should be noted that, if the light source module 101 comprises one light source and one signal transmission path, when the retinal imaging device works in the non-confocal imaging mode, the imaging light emitted by the light source is output through the corresponding signal transmission path and is incident on the light beam scanning module 200; if the light source module comprises at least two light sources and at least two signal transmission paths, the imaging light emitted by one of the light sources in the light source module is output through the corresponding signal transmission path and is incident on the light beam scanning module 200. Optionally, the light source that generates the imaging light is the light source located at the center position among the at least two light sources, but the present application does not make a limitation in this regard, and the specific arrangement is determined according to the situation.

[0050] Optionally, in an embodiment of the present application, the signal transmission path is an optical fiber, and the light source module 101 comprises a plurality of light sources and a plurality of emission optical fibers, the end faces of the plurality of emission optical fibers are located on a straight line, so that when the retinal imaging device works in a second working mode (hereinafter referred to as the “confocal imaging mode” in this embodiment), the imaging light is generated by the plurality of light sources and is output through the corresponding signal transmission path, thereby improving the scanning speed of the retinal imaging device working in the confocal imaging mode, and further improving the imaging speed of the retinal imaging device. It should be noted that, in the embodiment of the present application, the plurality of light sources are at least two light sources, and the plurality of emission optical fibers are at least two emission optical fibers. It should also be noted that, in this embodiment, the emission optical fiber and the collection optical fiber are only named for the purpose of distinguishing optical fibers with different uses, and are both optical fibers (light guide fibers).

[0051] Specifically, in an embodiment of the present application, the light source module 101 comprises three light sources and three emission optical fibers, so as to improve the scanning speed of the retinal imaging device working in the confocal imaging mode, thereby improving the imaging speed of the retinal imaging device, and avoiding that the large number of light sources and emission optical fibers leads to a large volume of the light source detection module and affects the application of the retinal imaging device. However, the present application does not make a limitation in this regard, and in other embodiments of the present application, the light source module 101 can also comprise other numbers of light sources and emission optical fibers and adopt other arrangement modes, as long as the signals of the emission optical fibers in the light source module 101 can correspond to the signals of the collection optical fibers in the collection optical fiber bundle in the detection module 110.

[0052] As can be seen from the above, the retinal imaging device provided in the embodiments has the functions of non-confocal imaging mode and confocal imaging mode, and most of the optical paths are shared, and the switching between the non-confocal imaging mode and the confocal imaging mode can be realized only by controlling the number of light sources in the working state in the light source module 101, so that the volume of the retinal imaging device is small, the optical path switching when working in different modes is easy to adjust, and in the confocal imaging mode, the number of light sources in the working state in the light source module 101 is large, and the imaging speed is fast.

[0053] On the basis of any of the above embodiments, in an embodiment of the present application, as shown in FIG. 1, the light beam scanning module 200 further comprises a wavefront modulator 208; the probe module 110 detects the feedback light beam in two optical paths, wherein the first optical path comprises the collection fiber bundle 106, and the second optical path comprises a wavefront sensor 109. It should be noted that in the present embodiment, the wavefront modulator 208 is used to modulate the wavefront phase of the imaging light incident on the light beam scanning module 200, to compensate for the aberration of the imperfect eye and improve the resolution of retinal imaging. Specifically, in an embodiment of the present application, the wavefront modulator 208 can be a deformable mirror, a spatial light modulator, a transmissive compensation mirror, a reflective compensation mirror or other devices, and the present application does not limit this, which is determined according to the specific situation.

[0054] On the basis of the above embodiments, in an embodiment of the present application, as shown in FIG. 1, the light source probe module 100 further comprises a collimating lens 102, a first light splitter 103 and a second light splitter 104 located on the light path of the light output by the light source module 101, wherein the collimating lens 102 collimates the light output by the light source module 101 to form a parallel collimated light beam transmitted to the first light splitter 103, and the light beam is transmitted to the second light splitter 104 through the first light splitter 103, and then the second light splitter 104 reflects to form a scanning light beam incident on the light beam scanning module 200.

[0055] On the basis of the above-mentioned embodiments, in one embodiment of the present application, the first beam splitter 103 is further configured to reflect the feedback light beam, and the second beam splitter 104 is further configured to reflect and transmit the feedback light beam. In this embodiment, the first light path is a light path formed by the reflection of the feedback light beam by the first beam splitter, and the second light path is a light path formed by the transmission of the feedback light beam by the second beam splitter. In particular, in operation, the feedback light beam is first transmitted to the second beam splitter 104, and then reflected and transmitted by the second beam splitter 104. The part reflected by the second beam splitter 104 is transmitted to the first beam splitter 103, and then reflected by the first beam splitter 103 to the collection fiber bundle 106 in the first light path, transmitted to the detector assembly 107 through the collection fiber bundle 106, and then output to the acquisition control module 300 through the detector assembly 107. The part transmitted by the second beam splitter 104 is transmitted to the wavefront sensor 109 in the second light path, and then transmitted to the acquisition control module 300 through the wavefront sensor 109.

[0056] In particular, in operation of the retinal imaging device, the feedback light beam is transmitted to the wavefront sensor 109 through the second beam splitter 104 when it is incident on the light source detection module 100 through the beam scanning module 200, so that the wavefront information in the feedback light beam can be obtained through the wavefront sensor 109, a wavefront point array is generated and transmitted to the acquisition control module 300, and the acquisition control module 300 can control the compensation value of the wavefront modulator 208 to achieve real-time aberration compensation and improve the resolution of the retinal imaging device. In one embodiment of the application, the wavefront sensor is a Hartmann-Shack wavefront sensor, but the present application is not limited thereto, and the specific type can be determined according to the situation. It should be noted that in this embodiment, the wavefront sensor is in an operating state regardless of the mode in which the retinal imaging device is operated.

[0057] Optionally, on the basis of the above-mentioned embodiments, in one embodiment of the present application, the light source detection module 100 further comprises a collection lens 105 located on the first light path, and the collection lens 105 is located between the first beam splitter 103 and the collection fiber bundle 106.

[0058] On the basis of any of the above embodiments, in an embodiment of the present application, the light beam scanning module 200 comprises a plurality of optical conjugate assemblies, which form a plurality of eyeball pupil conjugate planes, and the scanning galvanometer, the eyeball and the light source module are respectively located on different eyeball pupil conjugate planes. Optionally, in an embodiment of the present application, the optical conjugate assembly is a mirror group, which can be a spherical mirror group, and of course a transmission mirror group can also be used, but the present application does not limit this, and the specific selection is determined according to the situation. The retinal imaging device provided in the embodiment of the present application is described below by taking the optical conjugate assembly as a mirror group as an example.

[0059] On the basis of the above embodiment, in an embodiment of the present application, the light beam scanning module further comprises a tracking galvanometer 209 and / or a wavefront modulator 208, and the tracking galvanometer 209 and / or the wavefront modulator 208, the scanning galvanometer (including the first scanning galvanometer 206 and / or the second scanning galvanometer 207), the eyeball and the light source module are respectively located on different eyeball pupil conjugate planes. Among them, the scanning galvanometer is used to realize the scanning of the scanning light beam, and the tracking galvanometer is used to realize the tracking of the scanning light beam.

[0060] Specifically, as shown in FIG. 1, in an embodiment of the present application, the light beam scanning module 200 comprises a first optical conjugate assembly 201, a second optical conjugate assembly 202, a third optical conjugate assembly 203, a fourth optical conjugate assembly 204 and a fifth optical conjugate assembly 205; wherein the first scanning galvanometer 206 is placed on the eyeball pupil conjugate plane between the first optical conjugate assembly 201 and the second optical conjugate assembly 202, the second scanning galvanometer 207 is placed on the eyeball pupil conjugate plane between the second optical conjugate assembly 202 and the third optical conjugate assembly 203, and the tracking galvanometer 209 is placed on the eyeball pupil conjugate plane of the fourth optical conjugate assembly 204 and the fifth optical conjugate assembly 205. It should be noted that in the present embodiment, the first scanning galvanometer 206 is used to realize horizontal scanning, i.e. horizontal direction scanning, the second scanning galvanometer 207 is used to realize vertical scanning, i.e. vertical direction scanning, and the tracking galvanometer 209 is used to track the eye when the position of the eyeball changes, to compensate for the horizontal scanning path and improve the accuracy of tracking. In specific work, the first scanning galvanometer 206 and the second scanning galvanometer 207 form a two-dimensional scan on the retina, and the signal of each point of the scan is spliced to become part of an image; the horizontal direction tracking signal acts on the tracking galvanometer 209, and the vertical direction tracking signal and the vertical scanning signal superimpose on the second scanning galvanometer 207, thereby realizing fundus scanning and eye movement tracking.

[0061] In another embodiment of the present application, the light beam scanning module comprises a first optical conjugate component, a second optical conjugate component, a third optical conjugate component, a fourth optical conjugate component and a fifth optical conjugate component; wherein a first scanning galvanometer is placed on the eyeball pupil conjugate surface between the first optical conjugate component and the second optical conjugate component, and a second scanning galvanometer is not arranged in the light beam scanning module, so that the light beam scanning module only realizes horizontal direction scanning, at this time, the scanning mode of the light beam scanning module is a line scanning mode, so that the light beam scanning module can obtain high-speed transverse scanning line scanning image information, which is generally used for obtaining dynamic information of the fundus, such as blood flow velocity measurement, etc.

[0062] It should be noted that in the present embodiment, as shown in FIG. 1, the wavefront modulator 208 is located on the eyeball pupil conjugate surface between the third optical conjugate component 203 and the fourth optical conjugate component 204, and the wavefront modulator 208 is used to compensate for aberration, so as to reduce the probability of distortion or blur during imaging due to aberration of an imperfect eye.

[0063] It should be noted that in other embodiments of the present application, the positions of the first scanning galvanometer, the second scanning galvanometer, the tracking galvanometer and the wavefront modulator can also be exchanged, as long as the first scanning galvanometer, the second scanning galvanometer, the tracking galvanometer and the wavefront modulator are respectively located on different eyeball pupil conjugate surfaces.

[0064] Optionally, in an embodiment of the present application, the acquisition control module 300 comprises a computing module such as a PC (Personal Computer), and in particular operation, the acquisition control module 300 collects light signals output from the collection optical fiber bundle 106 through the detector assembly 107, and according to the control signals of the first scanning galvanometer 206 and / or the second scanning galvanometer 207, obtains the positions of these light signals on the retina, and generates images by computing and processing these light signals. It should be noted that the acquisition control module 300 can also control the light path state of the light beam scanning module 200 based on the light signals output by the detector assembly 107, so as to realize eye movement tracking.

[0065] The light source described below includes three light sources as an example, in combination with the working mode, the process of the retinal imaging device provided by the embodiment of the application working in the non-confocal imaging mode and the confocal imaging mode is described. In order to facilitate the description, the light source in the center of the three light sources in the light source module is recorded as the center light source, the emission optical fiber in the middle of the three emission optical fibers is recorded as the center emission optical fiber, the device adopts the optical system of AOSLO (adaptive optical scanning laser confocal ophthalmoscope), the non-confocal imaging mode collects the scattering image as the non-confocal scattering imaging mode, and the confocal imaging mode is the multi-point scanning AOSLO mode. Optionally, in the embodiment, the acquisition control module includes a data acquisition unit, a calculation unit and a control component; wherein the data acquisition unit is used to acquire the signal output by the light source detection assembly, the calculation unit is used to process the signal output by the light source detection assembly, and in the non-confocal scattering imaging mode, a scattering image can be generated, and in the confocal imaging mode, an AOSLO image is generated.

[0066] Specifically, in the non-confocal scattering imaging mode, as shown in FIG. 1, the center light source in the light source module 101 emits light, which is transmitted to the collimating lens 102 through the center emission optical fiber. After being collimated by the collimating lens 102, parallel collimated light is formed and shot to the first beam splitter 103. After being transmitted by the first beam splitter 103, it is transmitted to the second beam splitter 104. After being reflected by the second beam splitter 104, the incident light beam scanning module 200 is entered. In turn, each optical conjugate assembly, scanning galvanometer and tracking galvanometer in the light beam scanning module 200 are modulated, and the light beam is shot into the pupil and the retina. After the action of the retina, the feedback light beam is shot into the light beam scanning module 200, and is transmitted along the reverse direction of the transmission direction of the imaging light, until it is shot out of the light beam scanning module 200, enters the light source detection module 100, is reflected by the second beam splitter 104 to the first beam splitter 103, is reflected by the first beam splitter 103, and is shot to the collection lens 105. After being collected by the collection lens 105, it is collected on the collection optical fiber bundle 106, and then is shot to the detector assembly 107 through the collection optical fiber bundle 106. Finally, it is transmitted to the acquisition control module 300 through the detector assembly 107.

[0067] It should be noted that in the non-confocal scattering imaging mode, only the central light source and its corresponding central emission optical fiber in the light source module emit imaging light, which is incident on the pupil, is reflected and scattered by the retina to form a feedback light beam, which is transmitted to the collection lens, and when transmitted to the collection optical fiber bundle, the scattering signal is collected by the non-central collection optical fibers in the collection optical fiber bundle, i.e. the surrounding collection optical fibers symmetrically arranged with the central collection optical fiber in the collection optical fiber bundle, and then transmitted to the detector assembly through the collection optical fiber bundle, and output to the acquisition control module through the detector assembly. As shown in FIG. 4, FIG. 4 is a schematic diagram of light scanning of the fundus in the non-confocal scattering imaging mode. As shown in FIG. 5, taking the collection optical fiber bundle including 9 collection optical fibers as an example, the collection optical fiber bundle includes 9 collection optical fibers, and the positive and negative signs in FIG. 5 represent the differential mode in the non-confocal scattering imaging mode, wherein two surrounding collection optical fibers symmetrically arranged form a group, and the acquisition control module differentiates the signals output by each group of collection optical fibers to obtain scattering light signals enhanced in a specific direction, and then filters and superimposes three groups of signals, and calculates the complete image according to the galvanometer control signal to restore the complete image, i.e. to obtain the scattering image. Of course, the confocal image can also be obtained by the reflected signal collected by the central collection optical fiber.

[0068] It should be further noted that in the confocal imaging mode, as shown in FIG. 6, each light source in the light source module 101 emits light, and the light emitted by each light source is transmitted to the collimating lens 102 through its corresponding emission optical fiber. After collimated by the collimating lens 102, parallel collimated light is formed and is incident on the first beam splitter 103, is transmitted to the second beam splitter 104 after being transmitted through the first beam splitter 103, is reflected by the second beam splitter 104, and is incident on the beam scanning module 200. The incident light beam is modulated by each optical conjugate assembly, the scanning galvanometer and the tracking galvanometer in the beam scanning module 200 in turn, is incident on the pupil, interacts with the fundus (or retina) to form a feedback light beam, and is incident on the beam scanning module 200 along the reverse direction of the transmission direction of the imaging light, and is finally transmitted to the acquisition control module 300 through the detector assembly 107.

[0069] For example, when the light source module includes three light sources and three emission optical fibers, the reflected signals in the feedback light beams are collected by the corresponding three collection optical fibers in the collection optical fiber bundle, and the light signals collected by each collection optical fiber correspond to the imaging light emitted by one optical fiber at the light source, as shown in FIG. 7, where different fillings represent the signal distribution collected by different collection optical fibers, and correspond to a part of the scanning area on the retina. After the acquisition control module receives the signals output by the detector assembly, the feedback signals output by each collection optical fiber are combined to restore the confocal image, i.e., the fundus AOSLO image, as shown in FIG. 8, where different lines represent the scanning paths of different imaging lights.

[0070] It should be further noted that, in the present embodiment, the feedback signals received by the detector from the collection optical fiber bundle are the light signals output by the three collection optical fibers, which correspond to three different scanning areas on the retina. When the acquisition control module receives the light signals from the three collection optical fibers in the collection optical fiber bundle, the areas on the retina corresponding to the three light signals are calculated according to the size of the current scanning field angle (oscillating mirror vibration amplitude), and then the images of these areas are spliced to form a complete AOSLO image. Through this multi-point scanning mode, the retina imaging speed can be increased to 3 times the original speed under the same oscillating mirror vibration frequency.

[0071] As can be seen, in the present application, when the light source module includes at least two light sources and their corresponding at least two emission optical fibers simultaneously emit imaging light, the acquisition control module can obtain the images of at least two scanning areas at the same time, thereby improving the speed of obtaining the fundus AOSLO image. Since the retina imaging device works in the confocal imaging mode, the acquisition control module can obtain the images of at least two scanning areas at the same time, and therefore, this imaging mode can also be called a multi-point scanning imaging mode.

[0072] On the basis of any of the above embodiments, in an embodiment of the present application, as shown in FIGS. 9 and 10, the retina imaging device further includes a pluggable beam-reducing assembly 108, which, in the present embodiment, is inserted into the first light path, and the feedback light beam enters the collection optical fiber bundle 106 after passing through the beam-reducing assembly 108.

[0073] In the embodiment, the retinal imaging device further comprises a third working mode (hereinafter referred to as "super-resolution imaging mode" in the embodiment), in which the beam-reducing assembly 108 is arranged in the first light path, i.e. between the first beam splitter 103 and the collection lens 105, to modulate the light beam reflected by the first beam splitter 103 towards the collection lens 105. In the non-confocal imaging mode and the multi-point scanning imaging mode, the beam-reducing assembly 108 is not arranged in the first light path, i.e. not between the first beam splitter 103 and the collection lens 105, so that the feedback light beam reflected by the first beam splitter 103 can directly enter the collection lens 105.

[0074] Optionally, in an embodiment of the present application, the detection module further comprises a control module (not shown in the figure) for controlling the movement of the beam-reducing assembly, to control the relative position of the beam-reducing assembly and the first light path. Specifically, the control module comprises a motor to control the movement of the module by the motor, but the present application is not limited thereto, and the specific implementation is determined according to the situation.

[0075] Optionally, in an embodiment of the present application, the beam-reducing assembly comprises a beam-reducing lens group, in the super-resolution imaging mode, the control module controls the beam-reducing lens group to move to the light path between the first beam splitter and the collection lens, to modulate the light beam reflected by the first beam splitter towards the collection lens, in the non-confocal imaging mode and the confocal imaging mode, the control module controls the beam-reducing lens group to move out of the light path between the first beam splitter and the collection lens, so that the feedback light beam reflected by the first beam splitter can directly enter the collection lens.

[0076] Continuing as shown in FIG. 10, in the super-resolution imaging mode, the control module controls the beamlet assembly 108 to move to the light path between the first beam splitter 103 and the collection lens 105, the central light source in the light source module 200 emits light, which is transmitted to the collimating lens 105 through the central transmission optical fiber, and after collimation by the collimating lens 105, forms parallel collimated light to the first beam splitter 103, which is transmitted to the second beam splitter 104 after transmission through the first beam splitter 103, and after reflection by the second beam splitter 104, the incident light beam scans the module 200, and is modulated in turn by each optical conjugate assembly, scanning galvanometer and tracking galvanometer in the beam scanning module 200, and enters the pupil, and after acting on the fundus, forms a feedback light beam to the third beam splitter 401, which is transmitted to the beam scanning module 200 after transmission through the third beam splitter 401, and is transmitted in the opposite direction to the transmission direction of the imaging light, until it exits the beam scanning module 200, enters the light source detection module 100, is reflected by the second beam splitter 104 to the first beam splitter 103, and is reflected by the first beam splitter 103 to the beamlet assembly 108, which is modulated by the beamlet assembly 108 to form a beamlet after beamlet modulation, and is then transmitted to the collection lens 105, which converges to the collection optical fiber bundle 106, and then to the detector assembly 107 through the collection optical fiber bundle 106, and finally to the acquisition control module 300 through the detector assembly 107.

[0077] It should be noted that in the super-resolution imaging mode, the beamlet assembly in the present embodiment converges the beamlet after beamlet to increase the Airy disk radius, and the surrounding 2N optical fiber bundles in the collection optical fiber bundle no longer collect scattered light signals, but collect reflected light signals near the center of the optical axis. These signals, together with the reflected light signals collected by the central collection optical fiber, are superimposed and calculated by the acquisition control module to restore the super-resolution AOSLO image. Since each collection optical fiber has a core diameter of only about 0.2 times the Airy disk diameter, according to the principle of confocal imaging, its resolution will be the highest, and the light collection efficiency will be greatly reduced, thereby reducing the signal-to-noise ratio, but the 2N+1 optical fibers in the present embodiment collectively collect light signals, which overcomes this difficulty and improves the signal-to-noise ratio. As shown in FIG. 11, FIG. 11 shows the signal distribution of each collection optical fiber in the collection optical fiber bundle in the super-resolution imaging mode, wherein the circular ring shape represents the position and relative size of the Airy disk of the collection beam emitted by the collection lens.

[0078] Specifically, the collection control module receives feedback light signals from the 2N+1 collection fibers, and calculates and restores 2N+1 images according to the galvanometer control signal, specifically including: taking the image generated by the center collection fiber receiving signal as the reference, offsetting and correcting the 2N images according to the pre-designed offset, and then superimposing the 2N+1 images together to obtain an ultra-resolution AOSLO image with high signal-to-noise ratio and high resolution. It should be noted that taking the image generated by the center collection fiber receiving signal as the reference, the other 2N images each produce a pixel-level offset in different directions, and the offset is determined by the relative position relationship of the collection fibers on the collection fiber bundle. The offset = D / M (D is the distance from the surrounding collection fiber to the center collection fiber, and M is the magnification of the reflected light channel, i.e. M = image height on the collection fiber bundle / image height on the retina).

[0079] As can be seen, in the ultra-resolution imaging mode, the retinal imaging device provided by the embodiment of the application can obtain an ultra-high resolution confocal image and a higher signal-to-noise ratio when imaging the retina. For the dense cone cells near the fovea of the macula, a high signal-to-noise ratio signal can also be obtained.

[0080] Comparing the working processes of the retinal imaging device in the non-confocal imaging mode, the confocal imaging mode and the ultra-resolution imaging mode, it can be seen that the retinal imaging device can work in the three working modes and share most of the optical path. Only by controlling the light source in the working state in the light source module and the movement of the beam-reducing assembly can the three modes be replaced.

[0081] Considering that the existing retinal imaging device has a small single imaging range and can only cover a small area on the retina, it is difficult for the user to determine the specific position of the imaging area on the retina based on a single scan image. If the user wants to observe a lesion or cell tissue, it is difficult to determine whether the scan image is the region of interest, and it is also difficult to determine where the scan image should be moved to reach the region of interest. Only the traversal method can be used to find the region of interest, which requires a lot of time to find the region of interest on the retina, and the device operation steps are complex, which is low in clinical efficiency.

[0082] On the basis of any of the above embodiments, in an embodiment of the present application, as shown in FIG. 1, the retinal imaging device further comprises an fundus imaging module 400 for acquiring fundus images. Specifically, in an embodiment of the present application, the fundus imaging module comprises a fundus illumination light source (not shown in the figure) and a fundus camera 403, wherein the fundus illumination light source generates illumination light to illuminate the fundus, and the fundus camera 403 acquires fundus images. Optionally, the fundus illumination light source can be a fundus illumination LED. The fundus illumination light generated by the fundus illumination light source illuminates the fundus, and the fundus camera acquires the reflected light to generate real-time fundus images. The fundus imaging module 400 can also use a wide-field scanning laser ophthalmoscope or other optical system to achieve image acquisition.

[0083] It can be understood that, since the imaging area displayed by the fundus image is significantly larger than and contains the imaging area displayed by the scanning image, the position of the imaging area displayed by the scanning image on the retina can be obtained according to the fundus image, so that the user can determine whether the current scanning image is the region of interest, and can also obtain relative position information of the scanning image and the region of interest, to guide the user to directly and quickly find the region of interest on the retina. The retinal imaging device has simple operation steps and high clinical efficiency.

[0084] Optionally, in an embodiment of the present application, as shown in FIG. 1, the fundus imaging module 400 further comprises a fixation unit 406 for generating a fixation pattern to guide the fixation direction of the eyeball.

[0085] Optionally, the fixation unit 406 can be a display screen or an LED array, and the fixation unit 406 (such as a display screen) displays a fixation pattern (such as a bright cross), and the subject's eye is required to stare at the fixation pattern. If the position of the fixation pattern is adjusted, the subject's eyeball will be guided to rotate to change the fixation direction.

[0086] Optionally, in an embodiment of the present application, as shown in FIG. 1, the fundus imaging module 400 further comprises a pupil illumination light source 404 and a pupil camera 405, wherein the pupil illumination light source 404 generates pupil illumination light to illuminate the eyeball, and the pupil camera 405 acquires pupil images.

[0087] Optionally, the pupil illumination light source 404 can be a pupil illumination LED. The pupil illumination light source 404 emits light to illuminate the entire ocular surface, and the pupil camera 405 collects the light reflected by the pupil to generate real-time pupil images.

[0088] On the basis of any of the above embodiments, in an embodiment of the present application, the retinal imaging device can further comprise a moving component for adjusting the relative position of the optical axis of the retinal imaging device and the pupil, so as to align the optical axis of the retinal imaging device with the pupil.

[0089] Optionally, the moving component can be a headrest component for placing the head of the subject, and the movement of the moving component drives the movement of the head of the subject to adjust the relative position of the optical axis of the retinal imaging device and the pupil, so that the optical axis of the retinal imaging device is aligned with the pupil.

[0090] Optionally, the moving component is connected with the retinal imaging device to drive the movement of the retinal imaging device to adjust the relative position of the optical axis of the retinal imaging device and the pupil, so that the optical axis of the retinal imaging device is aligned with the pupil.

[0091] Optionally, the moving component can drive the movement of the head of the subject and the movement of the retinal imaging device to adjust the relative position of the optical axis of the retinal imaging device and the pupil, so that the optical axis of the retinal imaging device is aligned with the pupil.

[0092] When the moving component is a headrest component, the headrest component can be a three-axis headrest motor, and the headrest component control unit can be a motor controller, which controls the three-axis headrest motor to drive the movement of the head of the subject to achieve the purpose of aligning the optical axis of the retinal imaging device with the pupil.

[0093] It can be understood that in the embodiment, the fundus illumination light source, the fundus camera and the fixation unit in the fundus imaging module in combination with the light beam scanning module can realize the rapid positioning of the imaging light beam on the fundus of the region of interest on the retina, greatly improving the scanning efficiency. Moreover, the pupil illumination light source, the pupil camera and the moving component can realize the alignment of the optical axis of the retinal imaging device with the pupil, ensuring the efficient and accurate scanning of the eye of the subject and improving the clinical efficiency.

[0094] Optionally, as shown in FIG. 1, the fundus imaging module can further include a third beam splitter 401 and a fourth beam splitter 402, so that the light beam emitted by the fundus illumination light source enters the eyeball, and the imaging light beam emitted by the light beam scanning module 200 enters the eyeball, and the light beam reflected from the fundus is collected by the fundus camera 403, the pupil camera 405 and the light beam scanning module 200. In the embodiment, the fundus illumination light source is located near the fundus camera, so that the signal emitted by the fundus illumination light source and the signal received by the fundus camera can use the same optical path, but the present application is not limited thereto, and in other embodiments of the present application, more beam splitters can be added according to the needs to separate the fundus illumination light source and the fundus camera 403 into two paths, separate the fixation unit 406 and the pupil camera 405 into two paths, and combine the pupil illumination light source to the main light path, etc., which is determined according to the specific circumstances.

[0095] As shown in FIG. 12, on the basis of any of the above embodiments, in an embodiment of the present application, the acquisition control module 300 comprises a data acquisition unit 301, a calculation unit 302, a control component; wherein the data acquisition unit 301 has four input ends and one output end, the four input ends of the data acquisition unit 301 are respectively used for acquiring the signals output by the detector assembly 107, the wavefront sensor 109, the pupil camera 405 and the fundus camera 403, the output end of the data acquisition unit 301 is connected with the calculation unit 302, and is used for outputting the acquired signals to the calculation unit 302, the calculation unit 302 processes the received signals and outputs them to the control component to control the working of each component of the retinal imaging device and control the working of the retinal imaging device.

[0096] Specifically, the control component comprises a scanning galvanometer control unit 303, a wavefront modulator controller 304, a light source controller 305, a motor controller 306 and a fixation unit controller 307, wherein the scanning galvanometer control unit 303 is used for controlling the working of the first scanning galvanometer 206, the second scanning galvanometer 207 and the tracking galvanometer 209, the wavefront modulator controller 304 is used for controlling the working of the wavefront modulator 208, the light source controller 305 is used for controlling the working of the light source module, the fundus illumination light source and the pupil illumination light source, the motor controller 306 is used for controlling the control module to control the movement of the beam shrinking assembly, and the fixation unit controller 307 is used for controlling the working of the fixation unit.

[0097] Specifically, when the retinal imaging device works, the wavefront point array detected by the wavefront sensor is acquired by the data acquisition unit and sent to the calculation unit, the calculation unit calculates the aberration based on the wavefront point array detected by the wavefront sensor, generates a correction signal, controls the wavefront compensation amount of the wavefront modulator through the wavefront modulator controller, corrects the aberration of the retinal imaging system, improves the resolution of the retinal imaging system, and achieves the retinal imaging resolution of the super high-definition cell level.

[0098] The fundus reflection signal and / or scattering signal reflected by the second beam splitter and collected by the detector assembly is sent to the data acquisition unit for acquisition, the calculation unit processes the signal acquired by the data acquisition unit based on the working mode of the retinal imaging device, generates a real-time video-level frame rate fundus image, and calculates the direction and speed of the eye movement based on the real-time fundus image in real time, applies the eye tracking signal to the galvanometer (the first scanning galvanometer, the second scanning galvanometer and / or the tracking galvanometer) through the galvanometer controller, so that the real-time fundus image moves in the same direction and at the same speed as the eye, and the purpose of eye movement tracking and real-time image stabilization is achieved.

[0099] The pupil camera collects the pupil image of the subject in real time, the calculation unit observes the pupil offset through the pupil image, controls the three-axis head motor through the motor controller, moves the head of the subject, and aligns the head of the subject with the light path;

[0100] The fundus camera collects the infrared fundus image of the subject in real time, and the operator of the retinal imaging device can confirm the relative position of the collected small area on the fundus by observing the infrared fundus image of the subject, thereby playing a role of navigation on the retina;

[0101] The light source controller controls the infrared light source in the light source module to emit a light beam from a plurality of optical fibers or an optical fiber according to the imaging mode selected by the operator of the retinal imaging device, and the motor controller controls whether to move the beam shrinking assembly in front of the collection lens according to the selected imaging mode.

[0102] In summary, the retinal imaging device provided by the embodiments of the present application combines the multi-point scanning imaging mode (i.e. the confocal imaging mode) with the super-resolution imaging mode and the non-confocal imaging mode, and can realize the mutual compatibility of the three functions of high-speed AOSLO imaging, super-resolution AOSLO imaging and non-confocal scattering imaging with a simple structure, and solves the two problems of slow imaging speed and single imaging mode of the current AOSLO device.

[0103] Moreover, the retinal imaging device provided by the embodiments of the present application can realize the super-resolution AOSLO function by adding a set of movable beam shrinking assembly, so that the AOSLO can improve the resolution while retaining sufficient signal strength, and solves the problem that the imaging resolution and signal-to-noise ratio of the current AOSLO device are mutually limited.

[0104] Therefore, the retinal imaging device provided by the present application realizes the simple switching of the above three AOSLO modes through the control loop of the hardware system.

[0105] In addition, the retinal imaging device provided by the embodiments of the present application shares most of the optical path during the switching of the three imaging functions, and has a simple structure and a small size.

[0106] Correspondingly, the embodiments of the present application also provide a retinal imaging method applied to the retinal imaging device provided by any of the above embodiments, and the retinal imaging device includes at least one working mode. Specifically, the retinal imaging method includes:

[0107] In the first working mode (non-confocal imaging mode), the light source module generates imaging light, the imaging light generated by the light source module is incident to the light beam scanning module, the light beam modulated by the light beam scanning module enters the eyeball, and the feedback light beam formed by the reflection and scattering of the retina is incident to the detection module through the light beam scanning module, wherein the central collection optical fiber in the collection optical fiber bundle of the detection module is used to collect the reflection signal, and at least part of the other 2N collection optical fibers in the collection optical fiber bundle of the detection module is used to collect the scattering signal;

[0108] The confocal image of the retina is obtained based on the reflection signal obtained by the collection optical fiber bundle, and the non-confocal image of the retina is obtained based on the scattering signal obtained by the collection optical fiber bundle.

[0109] Optionally, in an embodiment of the present application, the light source module comprises a plurality of light sources and a signal transmission path corresponding to each light source, and the imaging light generated by the light source is incident to the light beam scanning module through the signal transmission path; the retinal imaging method further comprises:

[0110] In the second working mode (confocal imaging mode), the plurality of light sources in the light source module generate imaging light, the imaging light generated by the plurality of light sources is incident to the light beam scanning module, the light beam modulated by the light beam scanning module enters the eyeball, and the feedback light beam formed by the retina is incident to the plurality of collection optical fibers corresponding to the signal transmission path in the collection optical fiber bundle in the detection module through the light beam scanning module;

[0111] The confocal image of the retina is obtained based on the reflection signal in the feedback light beam obtained by the collection optical fiber bundle.

[0112] Optionally, in an embodiment of the present application, the retinal imaging device further comprises a super-resolution imaging mode, and correspondingly, in this embodiment, the imaging method further comprises:

[0113] In the super-resolution imaging mode (i.e. the third working mode), the beam-reducing assembly is inserted into the detection module, so that the feedback light beam formed by the retina is modulated by the beam-reducing assembly and then transmitted to the 2N+1 collection optical fibers of the collection optical fiber bundle; and the super-resolution confocal image of the retina is obtained based on the reflection signal in the feedback light beam obtained by the collection optical fiber bundle.

[0114] It should be noted that the principle of the retinal imaging method provided in the embodiments of the present application is the same as the principle of the retinal imaging device provided in the above-mentioned embodiments of the present application, and the specific description can be referred to the description of the retinal imaging device part. Herein, no longer be described.

[0115] The various embodiments described in this specification are intended to be illustrative only and are not intended to limit the scope of the application in any way. Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The materials, methods, and examples provided herein are illustrative only and are not intended to be limiting. Other features of the application will be apparent from consideration of the specification and the drawings in which:

[0116] It has to be noted that, in the description of the application, the description of the figures and the embodiments is illustrative in nature and not restrictive. Like reference symbols in the figures of the specification do indicate like features in the figures. In the text, relational terms such as first and second and the like can merely be used by way of

[0117] The foregoing description of the disclosed embodiments enables a person skilled in the art to implement or use the application. Numerous modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein can be applied to other embodiments without departing from the spirit or scope of the application. Therefore, the present application is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A retinal imaging device, comprising: The light source detection module, the light beam scanning module and the acquisition control module are characterized in that the light source detection module comprises a light source module and a detection module, the imaging light generated by the light source module is incident to the light beam scanning module, the light beam scanning module comprises a scanning galvanometer; The modulated light beam of the light beam scanning module enters the eyeball, and the feedback light beam formed by the retina is incident to the detection module through the light beam scanning module, the detection module comprises a collection optical fiber bundle, and the collection optical fiber bundle comprises 2N+1 collection optical fibers, wherein 2N collection optical fibers are symmetrically distributed at least in part with one collection optical fiber as the center, and N≥1; The acquisition control module is connected with the light source detection module and the light beam scanning module respectively.

2. The retinal imaging device of claim 1, wherein, The light beam scanning module further comprises a wavefront modulator; the detection module detects the feedback light beam through two light paths, wherein the first light path comprises the collection optical fiber bundle, and the second light path comprises a wavefront sensor.

3. The retinal imaging device of claim 1, wherein, The detection module further comprises an insertable beamlet assembly, and the feedback light beam enters the collection optical fiber bundle through the beamlet assembly.

4. The retinal imaging apparatus according to claim 1 or 3, characterized by The light source module comprises one or more light sources and a signal transmission path corresponding to each light source, and the imaging light generated by the light source is incident to the light beam scanning module through the signal transmission path.

5. The retinal imaging device of claim 4, wherein, The signal transmission path is an optical fiber, the light source module comprises a plurality of light sources and a plurality of emission optical fibers, and the end faces of the plurality of emission optical fibers are located on a straight line.

6. The retinal imaging device of claim 1, wherein, The light beam scanning module further comprises a plurality of optical conjugate components, the plurality of optical conjugate components form a plurality of eyeball pupil conjugate planes, and the scanning galvanometer, the eyeball and the light source module are located on different eyeball pupil conjugate planes respectively.

7. The retinal imaging device of claim 6, wherein, The light beam scanning module further comprises a tracking galvanometer and / or a wavefront modulator, and the tracking galvanometer and / or the wavefront modulator, the scanning galvanometer, the eyeball and the light source module are located on different eyeball pupil conjugate planes respectively.

8. A method of retinal imaging, comprising: The retinal imaging device according to claim 1 or 2 comprises at least one working mode, and the retinal imaging method comprises: In the first working mode, the light source module generates imaging light, the imaging light generated by the light source module is incident to the light beam scanning module, the modulated light beam of the light beam scanning module enters the eyeball, and the feedback light beam formed by the reflection and scattering of the retina is incident to the detection module through the light beam scanning module, wherein the center collection optical fiber in the collection optical fiber bundle is used for collecting the reflection signal, and at least part of the other 2N collection optical fibers in the collection optical fiber bundle is used for collecting the scattering signal; The confocal image of the retina is obtained based on the reflection signal obtained by the collection optical fiber bundle, and the non-confocal image of the retina is obtained based on the scattering signal obtained by the collection optical fiber bundle.

9. The retinal imaging method of claim 8, wherein, The light source module comprises a plurality of light sources and a signal transmission path corresponding to each light source, and the imaging light generated by the light source is incident to the light beam scanning module through the signal transmission path; The retinal imaging method further comprises: In the second working mode, the imaging light is generated by using a plurality of light sources in the light source module, the imaging light generated by the plurality of light sources is incident to the light beam scanning module, the light beam modulated by the light beam scanning module enters the eyeball, and the feedback light beam formed by the retina is incident to a plurality of collection optical fibers corresponding to the signal transmission path in the collection optical fiber bundle in the detection module through the light beam scanning module; The confocal image of the retina is obtained based on the reflection signal in the feedback light beam obtained by the collection optical fiber bundle.

10. The retinal imaging method of claim 8, wherein, The retina imaging method further comprises: In the third working mode, the beam shrinking assembly is inserted into the detection module, so that the feedback light beam formed by the retina is modulated by the beam shrinking assembly and then transmitted to the 2N+1 collection optical fibers of the collection optical fiber bundle; The super-resolution confocal image of the retina is obtained based on the reflection signal in the feedback light beam obtained by the collection optical fiber bundle.

Images