Retinal imaging device

Abstract

The application provides a retinal imaging device, which comprises a light source detection module, a light beam scanning module and an acquisition control module, 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, 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, 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. The device can image the specific strong scattering and weak reflection microstructure on the human eye retina, has good endogenous contrast, and improves the comprehensiveness of acquired information and the imaging contrast.

Description

Technical Field

[0001] This application relates to the field of retinal imaging technology, and more particularly to a retinal imaging device. Background Technology

[0002] The retina is an important component of the eye, and retinal-related diseases are becoming increasingly common worldwide. Therefore, high-resolution imaging devices for the retina are of great significance for the diagnosis and treatment evaluation of retinal-related diseases.

[0003] Researchers 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 that can dynamically detect in real time, compensate for human eye aberrations, and improve lateral resolution by an order of magnitude, enabling the observation of retinal photoreceptor cells and microvessels. However, the device has low imaging contrast, and for specific microstructures on the human retina with strong scattering and weak reflection, such as blood vessel walls, red blood cells, and photoreceptor cell segments, the reflective imaging lacks good intrinsic contrast, limiting the comprehensiveness of the information acquired. Utility Model Content

[0004] In view of this, this application provides a retinal imaging device, the scheme of which is as follows:

[0005] A retinal imaging device includes: a light source detection module, a beam scanning module, and an acquisition control module. The light source detection module includes a light source module and a detection module. Imaging light generated by the light source module is incident on the beam scanning module. The beam scanning module includes a scanning galvanometer.

[0006] The beam modulated by the beam scanning module enters the eyeball, and the feedback beam formed by the retina is incident on the detection module through the beam scanning module. The detection module includes a collection fiber bundle, which includes 2N+1 collection fibers, wherein at least a portion of the 2N collection fibers are symmetrically distributed with one collection fiber as the center, and N≥1.

[0007] The acquisition and control module is connected to the light source detection module and the beam scanning module, respectively.

[0008] Optionally, the 2N collecting optical fibers are symmetrically distributed with one collecting optical fiber as the center.

[0009] Optionally, the beam scanning module further includes a wavefront modulator; the detection module detects the feedback beam in two optical paths, wherein the first optical path includes the collecting fiber bundle and the second optical path includes a wavefront sensor.

[0010] Optionally, the detection module further includes an insertable beam-shrinking assembly, through which the feedback beam enters the collecting fiber bundle.

[0011] Optionally, after the feedback beam passes through the beam-shrinking assembly, the reflected signal in the feedback beam is collected by all 2N+1 collecting fibers of the collecting fiber bundle.

[0012] Optionally, the light source module includes one or more light sources and a signal transmission path corresponding to each light source, wherein the imaging light generated by the light source is incident on the beam scanning module through the signal transmission path.

[0013] Optionally, the signal transmission path is an optical fiber, and the light source module includes multiple light sources and multiple transmitting optical fibers, the end faces of which are located on a straight line.

[0014] Optionally, the beam scanning module further includes: multiple optical conjugate components, which form multiple pupil conjugate surfaces, and the scanning galvanometer, the eyeball, and the light source module are respectively located on different pupil conjugate surfaces.

[0015] Optionally, the beam scanning module further includes: a tracking mirror and / or a wavefront modulator, wherein the tracking mirror and / or wavefront modulator, the scanning mirror, the eyeball, and the light source module are respectively located on different conjugate surfaces of the pupil of the eyeball.

[0016] Optionally, the retinal imaging device may further include a fundus imaging module for acquiring fundus images.

[0017] When the retinal imaging device provided in this application operates in the first working mode, the imaging light generated by the light source module is incident on the beam scanning module, modulated by the beam scanning module, and enters the eyeball. The feedback beam formed by reflection and scattering from the retina is incident on the detection module via the beam scanning module and output to the acquisition control module via the detection module. The reflected signal from the retina in the feedback beam is collected by the central collecting fiber in the collecting fiber bundle (the collecting fiber located in the central region of the collecting fiber bundle is the central collecting fiber, and the other 2N collecting fibers are non-central collecting fibers). The scattered signal from the retina in the feedback beam is collected by the non-central collecting fibers in the collecting fiber bundle, that is, at least a portion of the other 2N collecting fibers in the collecting fiber bundle excluding the central collecting fiber are symmetrically distributed (i.e., the surrounding collecting fibers). This device can image specific microstructures with strong scattering and weak reflection on the human retina, such as blood vessel walls, red blood cells, and photoreceptor cell segments, and has good endogenous contrast, improving the comprehensiveness of information acquisition and imaging contrast. Attached Figure Description

[0018] To more clearly illustrate the technical solutions in the embodiments of this application or related technologies, the drawings used in the description of the embodiments or prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of this application. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.

[0019] The structures, proportions, sizes, etc., shown in the accompanying drawings are only for the purpose of assisting those skilled in the art in understanding and reading the content disclosed in the specification, and are not intended to limit the implementation conditions of this application. Therefore, they have no substantial technical significance. Any modifications to the structure, changes in the proportions, or adjustments to the size, without affecting the effects and purposes that this application can produce, should still fall within the scope of the technical content disclosed in this application.

[0020] Figure 1 A schematic diagram of the optical path of a retinal imaging device provided in one embodiment of this application when it is operating in a first working mode;

[0021] Figure 2 This is a schematic diagram of the structure for collecting the optical fiber bundle in a retinal imaging device provided in one embodiment of this application;

[0022] Figure 3 A schematic diagram of the structure for collecting the fiber optic bundle in a retinal imaging apparatus provided in another embodiment of this application;

[0023] Figure 4A schematic diagram of a fundus scan of the retinal imaging device provided in one embodiment of this application when it is operating in a first working mode;

[0024] Figure 5 This is a schematic diagram of the signal distribution in the fiber optic bundle of the retinal imaging device provided in one embodiment of the present application when it is operating in a first working mode.

[0025] Figure 6 A schematic diagram of the optical path of a retinal imaging device provided in one embodiment of this application when it is operating in a second working mode;

[0026] Figure 7 This is a schematic diagram of the signal distribution in the fiber optic bundle of the retinal imaging device provided in one embodiment of the present application when it is operating in a second working mode.

[0027] Figure 8 A schematic diagram of a fundus scan of the retinal imaging device provided in one embodiment of this application operating in a second working mode;

[0028] Figure 9 This is a schematic diagram of a retinal imaging device provided in one embodiment of the present application, in which the beam-contraction component is not located in the first optical path;

[0029] Figure 10 This is a schematic diagram of the structure of a retinal imaging device provided in an embodiment of this application, in which the beam-contracting component is located in the first optical path.

[0030] Figure 11 This is a schematic diagram of the signal distribution in the fiber optic bundle of the retinal imaging device provided in one embodiment of the present application when it is operating in the third working mode;

[0031] Figure 12 This is a schematic diagram of the acquisition control module in a retinal imaging device provided in one embodiment of this application. Detailed Implementation

[0032] The embodiments of this application will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of this application without creative effort are within the scope of protection of this application.

[0033] Various modifications and variations can be made to this application without departing from its spirit or scope, which will be apparent to those skilled in the art. Therefore, this application is intended to cover modifications and variations falling within the scope of the corresponding claims (the claimed technical solutions) and their equivalents. It should be noted that the implementation methods provided in the embodiments of this application can be combined with each other without contradiction.

[0034] To make the above-mentioned objectives, features and advantages of this application more apparent and understandable, the application will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0035] As described in the background section, existing adaptive optics retinal imaging devices have low imaging contrast. For specific microstructures on the human retina with strong scattering and weak reflection, such as blood vessel walls, red blood cells, and photoreceptor cell segments, the reflection imaging lacks good intrinsic contrast, which limits the comprehensiveness of the information acquired.

[0036] In addition, existing adaptive optics retinal imaging devices also have the following problems: 1. The 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 signals with high signal-to-noise ratio; 2. Slow imaging speed. The imaging speed is limited by the mechanical performance of the galvanometer scanning, making it difficult to observe high-speed dynamic information such as fundus blood flow in real time.

[0037] In view of this, embodiments of this application provide a retinal imaging device, such as... Figure 1 As shown, the retinal imaging device includes: a light source detection module 100, a beam scanning module 200, and an acquisition control module 300; wherein, the light source detection module 100 includes a light source module 101 and a detection module 110, the imaging light generated by the light source module 101 is incident on the beam scanning module 200, and the beam scanning module 200 includes a scanning galvanometer; the beam modulated by the beam scanning module 200 enters the eyeball, and the feedback beam formed by the retina is incident on the detection module 110 via the beam scanning module 200, and the detection module 110 includes a collecting fiber bundle 106, such as... Figure 2 As shown, the collecting fiber bundle 106 includes 2N+1 collecting fibers, wherein at least a portion of the 2N collecting fibers are symmetrically distributed with one collecting fiber as the center, and N≥1; the acquisition control module 300 is connected to the light source detection module 100 and the beam scanning module 200 respectively.

[0038] Optionally, in one embodiment of this application, the 2N collecting optical fibers are arranged symmetrically in a circle with one collecting optical fiber as the center, and so on. Figure 2As shown, the optical fibers can be arranged closely or spaced apart, but this application is not limited to this. In other embodiments of this application, the 2N+1 collecting optical fibers can also be arranged in other ways, such as a rectangular arrangement, such as... Figure 3 As shown, this application does not impose any limitations on this, and the specific requirements depend on the circumstances. It should be noted that the 2N collecting optical fibers do not need to be all symmetrically distributed; it is sufficient if a portion of them are symmetrically distributed. For example, it may include only one set of optical fibers symmetrical about the central fiber, and the arrangement of the remaining optical fibers is not restricted.

[0039] When the retinal imaging device provided in this embodiment operates in the first working mode, the imaging light generated by the light source module 101 is incident on the beam scanning module 200, modulated by the beam scanning module 200, and enters the eyeball. The feedback beam, formed by reflection and scattering from the retina, is incident on the detection module 110 via the beam scanning module 200, and output to the acquisition control module 300 via the detection module 110. The reflected signal from the retina in the feedback beam is collected by the central collecting fiber in the collecting fiber bundle (one collecting fiber located in the central region of the collecting fiber bundle is the central collecting fiber, and the other 2N collecting fibers are non-central collecting fibers). The scattered signal from the retina in the feedback beam is collected by at least a portion of the non-central collecting fibers in the collecting fiber bundle, that is, at least a portion of the other 2N collecting fibers (i.e., the surrounding collecting fibers) excluding the central collecting fiber. The symmetrically distributed surrounding collecting fibers in the 2N collecting fibers form a group (e.g.,...). Figure 2 The surrounding collecting fibers are symmetrically distributed around the central collecting fiber (forming a group of two surrounding collecting fibers). This allows the acquisition control module 300 to obtain a non-confocal image based on the scattered signal of the feedback beam (hereinafter referred to as "non-confocal imaging mode") by differentially subtracting the signals output from each group of surrounding collecting fibers to obtain a scattered light signal enhanced in a specific direction. Then, multiple groups of signals are filtered and superimposed (e.g., ...). Figure 2 (There are three sets of signals), and finally the enhanced signal from the retinal scatterer is restored. Therefore, this embodiment can image specific strong scattering and weak reflection microstructures on the human retina, such as blood vessel walls, red blood cells, and photoreceptor cell segments, during retinal imaging. It has good endogenous contrast and improves the comprehensiveness of information acquisition and imaging contrast.

[0040] It should be noted that, in the above embodiments, the retinal imaging device provided in this application embodiment can also obtain a confocal image of the retina by collecting the reflected signal transmitted by the optical fiber at the center.

[0041] Based on any of the above embodiments, in one embodiment of this application, the light source module 101 includes at least one light source and at least one signal transmission path, wherein each signal transmission path corresponds one-to-one with a light source. That is, the light source module 101 includes one or more light sources and corresponding signal transmission paths, and the imaging light generated by the light source is incident on the beam scanning module through the signal transmission path. Specifically, in one embodiment of this application, the light source is an infrared light source, which can be an infrared laser, an infrared superluminescent diode, or a supercontinuum laser, etc. This application does not limit the specific type of light source and the choice depends on the specific circumstances.

[0042] It should be noted that if the light source module 101 includes a light source and a signal transmission path, when the retinal imaging device operates in non-confocal imaging mode, the imaging light emitted by the light source is output through its corresponding signal transmission path and incident on the beam scanning module 200; if the light source module includes 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 its corresponding signal transmission path and incident on the 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 this application does not limit this and it depends on the specific situation.

[0043] Optionally, in one embodiment of this application, the signal transmission path is an optical fiber, and the light source module 101 includes: multiple light sources and multiple transmitting optical fibers. The end faces of the multiple transmitting optical fibers are located on a straight line, so that when the retinal imaging device is operating in the second working mode (hereinafter referred to as "confocal imaging mode" in this embodiment), imaging light is generated by multiple light sources and output through their corresponding signal transmission paths, thereby improving the scanning speed of the retinal imaging device operating in confocal imaging mode, and thus improving the imaging speed of the retinal imaging device. It should be noted that in this embodiment, the multiple light sources are at least two light sources, and the multiple transmitting optical fibers are at least two transmitting optical fibers. It should also be noted that in this embodiment, the names "transmitting optical fiber" and "collecting optical fiber" are merely used to distinguish optical fibers for different purposes; both are optical fibers (optical guide fibers).

[0044] Specifically, in one embodiment of this application, the light source module 101 includes three light sources and three transmitting optical fibers to improve the scanning speed of the retinal imaging device when operating in confocal imaging mode. This improves the imaging speed of the retinal imaging device while avoiding an excessive number of light sources and transmitting optical fibers that would result in a large light source detection module and affect the application of the retinal imaging device. However, this application is not limited to this. In other embodiments of this application, the light source module 101 may include other numbers of light sources and transmitting optical fibers, and may employ other arrangements, as long as the signals from the transmitting optical fibers in the light source module 101 correspond to the signals from the collecting optical fibers in the collecting optical fiber bundle of the detection module 110.

[0045] As can be seen from the above, when the retinal imaging device provided in this application embodiment has both non-confocal imaging mode and confocal imaging mode, it shares most of the optical path. The switching between non-confocal imaging mode and confocal imaging mode can be achieved by controlling the number of light sources in the light source module 101 that are in working state. This makes the retinal imaging device smaller in size, and the switching of optical path when working in different modes is easy to adjust. In the confocal imaging mode, the number of light sources in the light source module 101 that are in working state is larger, and the imaging speed is faster.

[0046] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 As shown, the beam scanning module 200 further includes a wavefront modulator 208; the detection module 110 detects the feedback beam through two optical paths, wherein the first optical path includes the collecting fiber bundle 106, and the second optical path includes a wavefront sensor 109. It should be noted that, in this embodiment, the wavefront modulator 208 is used to modulate the wavefront phase of the imaging light incident on the beam scanning module 200, compensating for aberrations in the imperfect eye and improving the resolution of retinal imaging. Specifically, in one embodiment of this application, the wavefront modulator 208 can be a deformable mirror, a spatial light modulator, a transmissive compensating mirror, a reflective compensating mirror, or other devices; this application does not limit this, and the specific choice depends on the circumstances.

[0047] Based on the above embodiments, in one embodiment of this application, the following continues... Figure 1As shown, the light source detection module 100 further includes: a collimating lens 102, a first beam splitter 103, and a second beam splitter 104 located on the light path output by the light source module 101. The collimating lens 102 collimates the light output from the light source module 101 to form a parallel collimated beam that is transmitted to the first beam splitter 103, transmitted through the first beam splitter 103 to the second beam splitter 104, and then reflected by the second beam splitter 104 to form a scanning beam that is incident on the beam scanning module 200.

[0048] Based on the above embodiments, in one embodiment of this application, the first beam splitter 103 is further used to reflect the feedback beam, and the second beam splitter 104 is further used to reflect and transmit the feedback beam. In this embodiment, the first optical path is the optical path formed by the reflection of the feedback beam by the first beam splitter, and the second optical path is the optical path formed by the transmission of the feedback beam by the second beam splitter. In specific operation, the first optical path further includes a detector assembly 107. The feedback beam is first transmitted to the second beam splitter 104, and is reflected and transmitted by the second beam splitter 104. The portion 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 collecting fiber bundle 106 in the first optical path. It is then transmitted to the detector assembly 107 through the collecting fiber bundle 106, and then output to the acquisition control module 300 through the detector assembly 107. The portion transmitted by the second beam splitter 104 is transmitted to the wavefront sensor 109 in the second optical path, and then transmitted to the acquisition control module 300 through the wavefront sensor 109.

[0049] Specifically, while the retinal imaging device is operating, it continues as follows: Figure 1 As shown, when the feedback beam is incident on the light source detection module 100 via the beam scanning module 200, it can be transmitted through the second beam splitter 104 to the wavefront sensor 109. The wavefront sensor 109 obtains the wavefront information in the feedback beam, generates a wavefront dot matrix, and transmits it to the acquisition control module 300. This allows the acquisition control module 300 to control the compensation value of the wavefront modulator 208, achieving real-time aberration compensation and improving the resolution of the retinal imaging device. Specifically, in one embodiment of the application, the wavefront sensor is a Hartmann-Shack wavefront sensor, but this application does not limit this and the choice depends on the specific circumstances. It should be noted that in this embodiment, the wavefront sensor is always operational regardless of the operating mode of the retinal imaging device.

[0050] Optionally, based on the above embodiments, in one embodiment of this application, the following continues... Figure 1As shown, the light source detection module 100 also includes a collecting lens 105 located on the first optical path, the collecting lens 105 being located between the first beam splitter 103 and the collecting fiber bundle 106.

[0051] Based on any of the above embodiments, in one embodiment of this application, the beam scanning module 200 includes: a plurality of optical conjugate components, the plurality of optical conjugate components forming a plurality of pupil conjugate surfaces, and the scanning galvanometer, the eyeball, and the light source module being located on different pupil conjugate surfaces. Optionally, in one embodiment of this application, the optical conjugate components are a mirror group, specifically a spherical mirror group, or a transmission mirror group, but this application is not limited to this, and it depends on the specific situation. The following describes the retinal imaging device provided in the embodiment of this application using a mirror group as an example of optical conjugate components.

[0052] Based on the above embodiments, in one embodiment of this application, the beam scanning module further includes: a tracking mirror 209 and / or a wavefront modulator 208, wherein the tracking mirror 209 and / or wavefront modulator 208, the scanning mirror (including a first scanning mirror 206 and / or a second scanning mirror 207), the eyeball, and the light source module are respectively located on different conjugate surfaces of the pupil of the eyeball. The scanning mirror is used to scan the scanning beam, and the tracking mirror is used to track the scanning beam.

[0053] Specifically, continue as follows Figure 1As shown, in one embodiment of this application, the beam scanning module 200 includes a first optical conjugate component 201, a second optical conjugate component 202, a third optical conjugate component 203, a fourth optical conjugate component 204, and a fifth optical conjugate component 205; wherein, a first scanning galvanometer 206 is placed on the pupil conjugate surface between the first optical conjugate component 201 and the second optical conjugate component 202, a second scanning galvanometer 207 is placed on the pupil conjugate surface between the second optical conjugate component 202 and the third optical conjugate component 203, and a tracking galvanometer 209 is placed on the pupil conjugate surface between the fourth optical conjugate component 204 and the fifth optical conjugate component 205. It should be noted that in this embodiment, the first scanning galvanometer 206 is used to perform lateral scanning, i.e., scanning in the horizontal direction, and the second scanning galvanometer 207 is used to perform longitudinal scanning, i.e., scanning in the vertical direction. The tracking galvanometer 209 is used to track the eye when the position of the eyeball changes and compensate for the lateral scanning path to improve tracking accuracy. In specific operation, the first scanning galvanometer 206 and the second scanning galvanometer 207 form a two-dimensional scan on the retina, and the signals of each scanned point are stitched together to form part of the image; the horizontal tracking signal acts on the tracking galvanometer 209, and the vertical tracking signal is superimposed on the vertical scanning signal and acts on the second scanning galvanometer 207, simultaneously realizing fundus scanning and eye tracking.

[0054] In another embodiment of this application, the beam scanning module includes 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 pupil conjugate surface between the first optical conjugate component and the second optical conjugate component, and a second scanning galvanometer is not provided in the beam scanning module, so that the beam scanning module only performs horizontal scanning. At this time, the scanning mode of the beam scanning module is a line scanning mode, thereby enabling the beam scanning module to obtain high-speed horizontal scanning line scanning image information, which is generally used for acquiring fundus dynamic information, such as blood flow velocity measurement.

[0055] It should be noted that, in this embodiment, the following continues... Figure 1 As shown, the wavefront modulator 208 is located on the pupil conjugate surface of the eyeball between the third optical conjugate component 203 and the fourth optical conjugate component 204. The wavefront modulator 208 is used to compensate for aberrations in order to reduce the probability of distortion or blurring during imaging due to aberrations of the imperfect eye.

[0056] It should be noted that in other embodiments of this application, the positions of the first scanning mirror, the second scanning mirror, the tracking mirror, and the wavefront modulator can be interchanged, as long as the first scanning mirror, the second scanning mirror, the tracking mirror, and the wavefront modulator are located on different pupil conjugate surfaces of the eyeball.

[0057] Optionally, in one embodiment of this application, the acquisition control module 300 includes a computing module, such as a PC (Personal Computer). Specifically, the acquisition control module 300 collects optical signals from the collecting fiber bundle 106 output through the detector assembly 107, and obtains the positions of these optical signals on the retina according to the control signals of the first scanning mirror 206 and / or the second scanning mirror 207. It then processes these optical signals to generate an image. It should be noted that the acquisition control module 300 can also control the optical path state of the beam scanning module 200 based on the optical signals output by the detector assembly 107 to achieve eye movement tracking.

[0058] The following description uses three light sources as an example to illustrate the process of the retinal imaging device provided in this application operating in non-confocal imaging mode and confocal imaging mode, combined with the working modes. For ease of description, the light source located at the center of the three light sources in the light source module is referred to as the central light source, and the middle transmitting fiber of the three transmitting fibers is referred to as the central transmitting fiber. The device adopts an AOSLO (Adaptive Optical Scanning Laser Confocal Ophthalmoscope) optical system. The non-confocal imaging mode is used to acquire scattering images, which is called non-confocal scattering imaging mode, and the confocal imaging mode is called multi-point scanning AOSLO mode. Optionally, in this embodiment, the acquisition control module includes a data acquisition unit, a computing unit, and a control component; wherein, the data acquisition unit is used to acquire the signal output by the light source detection component, and the computing unit is used to process the signal output by the light source detection component. In the non-confocal scattering imaging mode, a scattering image can be generated, and in the confocal imaging mode, an AOSLO image can be generated.

[0059] Specifically, in the nonfocal scattering imaging mode, such as Figure 1As shown, the light emitted by the central light source in the light source module 101 is transmitted to the collimating lens 102 via the central emitting optical fiber. After being collimated by the collimating lens 102, it forms parallel collimated light that is directed towards the first beam splitter 103. After being transmitted through the first beam splitter 103, it is transmitted to the second beam splitter 104. After being reflected by the second beam splitter 104, it is incident on the beam scanning module 200. It is then modulated sequentially by the various optical conjugate components, scanning mirror, and tracking mirror in the beam scanning module 200, and enters the pupil. After interacting with the retina, it forms... The feedback beam enters the beam scanning module 200 and is transmitted in the opposite direction to the transmission direction of the imaging beam until it exits the beam scanning module 200 and enters the light source detection module 100. It is reflected by the second beam splitter 104 to the first beam splitter 103. After being reflected by the first beam splitter 103, it is directed towards the collecting lens 105. The collecting lens 105 converges the beam onto the collecting fiber bundle 106, and then the beam is directed towards the detector assembly 107 via the collecting fiber bundle 106. Finally, the beam is transmitted to the acquisition control module 300 via the detector assembly 107.

[0060] It should be noted that in this embodiment, in the non-confocal scattering imaging mode, only the central light source and its corresponding central emitting fiber emit imaging light in the light source module. This imaging light, when incident on the pupil, is reflected and scattered by the retina to form a feedback beam. This feedback beam is transmitted to the collecting lens. When transmitted to the collecting fiber bundle, the scattered signal is collected by the non-central collecting fibers in the collecting fiber bundle, i.e., the surrounding collecting fibers symmetrically arranged with respect to the central collecting fiber. The signal is then transmitted to the detector assembly through the collecting fiber bundle and output to the acquisition control module through the detector assembly. Figure 4 As shown, Figure 4 This is a schematic diagram of light scanning of the fundus in nonfocal scattering imaging mode. Figure 5 As shown, taking N as 4 and the collecting fiber bundle comprising 9 collecting fibers as an example, Figure 5 The positive and negative signs indicate the differential method in non-confocal scattering imaging mode. In this mode, two symmetrically distributed peripheral collecting fibers form a group. The acquisition control module performs differential subtraction on the signals output from each group of collecting fibers to obtain a scattered light signal enhanced in a specific direction. The three groups of signals are then filtered and superimposed, and the complete image is calculated and reconstructed based on the galvanometer control signal, thus obtaining the scattering image. Alternatively, a confocal image can be obtained from the reflected signal collected by the central collecting fiber.

[0061] It should also be noted that, in the confocal imaging mode, such as Figure 6As shown, each light source in the light source module 101 emits light. The light emitted by each light source is transmitted through its corresponding transmitting optical fiber to the collimating lens 102. After being collimated by the collimating lens 102, it forms parallel collimated light that is directed towards the first beam splitter 103. After being transmitted through the first beam splitter 103, it is transmitted to the second beam splitter 104. After being reflected by the second beam splitter 104, it is incident on the beam scanning module 200. It is then modulated sequentially by the optical conjugate components, scanning mirror, and tracking mirror in the beam scanning module 200, and enters the pupil, where it interacts with the fundus (…). After the beam is generated by the action of the retina, a feedback beam is formed and enters the beam scanning module 200. It is transmitted in the opposite direction to the transmission direction of the imaging beam until it exits the beam scanning module 200 and enters the light source detection module 100. It is reflected by the second beam splitter 104 to the first beam splitter 103. After being reflected by the first beam splitter 103, it is directed to the collecting lens 105. It is then focused by the collecting lens onto the collecting fiber bundle 106, and then directed to the detector assembly 107 via the collecting fiber bundle 106. Finally, it is transmitted to the acquisition control module 300 via the detector assembly 107.

[0062] Taking the light source module comprising three light sources and three transmitting optical fibers as an example, when the light source module includes three light sources and three transmitting optical fibers, the reflected signals in the feedback beam are collected by the corresponding three collecting optical fibers in the collecting optical fiber bundle. The light signal collected by each collecting optical fiber corresponds to the imaging light emitted by one of the optical fibers at the light source, such as... Figure 7 As shown, different fillers represent the signal distributions collected by different collecting fibers, and corresponding to a portion of the scanned area on the retina. After receiving the signal output by the detector assembly, the acquisition control module synthesizes the feedback signals from each collecting fiber to reconstruct a confocal image, i.e., a fundus AOSLO image, as shown. Figure 8 As shown, different lines represent different scanning paths of imaging light.

[0063] It should also be noted that, in this embodiment, since the feedback signal received by the detector from the collection fiber bundle is the optical signal output from the three collection fibers, and the optical signals output from these three collection fibers correspond to three different scanning areas on the retina, when the acquisition control module receives the optical signals from the three collection fibers in the collection fiber bundle, it calculates the areas on the retina corresponding to the three optical signals according to the size of the current scanning field of view (magnifying mirror vibration amplitude), and then stitches the images of these areas together to form a complete AOSLO image. Through this multi-point scanning method, the retinal imaging speed can be increased to 3 times the original speed at the same magnifying mirror vibration frequency.

[0064] Therefore, in this application, when the light source module includes at least two light sources and their corresponding at least two emitting optical fibers simultaneously emitting imaging light, the acquisition control module can acquire images of at least two scanning areas at the same time, improving the speed of acquiring fundus AOSLO images. Since the acquisition control module can acquire images of at least two scanning areas simultaneously when the retinal imaging device operates in confocal imaging mode, this imaging mode can also be called a multi-point scanning imaging mode.

[0065] Based on any of the above embodiments, in one embodiment of this application, such as Figure 9 and Figure 10 As shown, in the retinal imaging device, the detection module further includes an insertable beam-shrinking component 108. In this embodiment, the inserted beam-shrinking component 108 is located in the first optical path, and the feedback beam enters the collecting fiber bundle 106 after passing through the beam-shrinking component 108.

[0066] In this embodiment, the retinal imaging device further includes a third operating mode (hereinafter referred to as "super-resolution imaging mode"). In the super-resolution imaging mode, the beam-shrinking component 108 is disposed in the first optical path, that is, in the optical path between the first beam splitter 103 and the collecting lens 105, to perform beam-shrinking modulation on the beam emitted from the first beam splitter 103 to the collecting lens 105. In the non-confocal imaging mode and the multi-point scanning imaging mode, the beam-shrinking component 108 is not located in the first optical path, that is, not in the optical path between the first beam splitter 103 and the collecting lens 105, so that the feedback beam reflected by the first beam splitter 103 can directly enter the collecting lens 105.

[0067] Optionally, in one embodiment of this application, the detection module further includes a control module (not shown in the figure) for controlling the movement of the beam-shrinking component, so as to control the relative position of the beam-shrinking component and the first optical path. Specifically, the control module includes a motor to control the movement of the module through the motor, but this application is not limited thereto and depends on the specific circumstances.

[0068] Optionally, in one embodiment of this application, the beam-shrinking component includes: a beam-shrinking lens group. In the super-resolution imaging mode, the control module controls the beam-shrinking lens group to move to the optical path between the first beam splitter and the collecting lens, and performs beam-shrinking modulation on the beam emitted by the first beam splitter towards the collecting lens. In the non-confocal imaging mode and the confocal imaging mode, the control module controls the beam-shrinking lens group to move outside the optical path between the first beam splitter and the collecting lens, so that the feedback beam reflected by the first beam splitter can be directly input into the collecting lens.

[0069] Continue as Figure 10 As shown, in the super-resolution imaging mode, the control module controls the beam-shrinking component 108 to move to the optical path between the first beam splitter 103 and the collecting lens 105. The light emitted by the central light source in the light source module 200 is transmitted through the central emitting fiber to the collimating lens 105. After being collimated by the collimating lens 105, it forms parallel collimated light that is directed towards the first beam splitter 103. After being transmitted through the first beam splitter 103, it is transmitted to the second beam splitter 104. After being reflected by the second beam splitter 104, it is incident on the beam scanning module 200 and sequentially modulated by the various optical conjugate components, scanning mirror, and tracking mirror in the beam scanning module 200. The light then enters the pupil and interacts with the fundus. The feedback beam is directed towards the third beam splitter 401, and after being transmitted by the third beam splitter 401, it enters the beam scanning module 200. It is transmitted in the opposite direction to the transmission direction of the imaging beam until it exits the beam scanning module 200 and enters the light source detection module 100. It is reflected by the second beam splitter 104 to the first beam splitter 103. After being reflected by the first beam splitter 103, it is directed towards the beam-shrinking assembly 108. The beam-shrinking assembly 108 modulates the beam to form a beam-shrinking beam, which is then directed towards the collecting lens 105. The collecting lens 105 converges the beam onto the collecting fiber bundle 106, which then travels through the collecting fiber bundle 106 to the detector assembly 107. Finally, the beam is transmitted through the detector assembly 107 to the acquisition control module 300.

[0070] It should be noted that in this embodiment, in the super-resolution imaging mode, the beam condensed by the beam-shrinking component becomes larger in radius after being converged by the collecting lens. The surrounding 2N fiber bundles in the collecting fiber bundle no longer collect scattered light signals, but instead collect reflected light signals near the center of the optical axis. These signals, along with the reflected light signals collected by the central collecting fiber, are superimposed and calculated by the acquisition control module to reconstruct the super-resolution AOSLO image. Since the core diameter of each collecting fiber is only about 0.2 times the diameter of the Airy disk, according to the principle of confocal imaging, its resolution will reach its maximum, but the light collection efficiency will be greatly reduced, thereby reducing the signal-to-noise ratio. However, in this embodiment, the 2N+1 fibers collecting the light signal together overcome this difficulty and can improve the signal-to-noise ratio. Figure 11 As shown, Figure 11 A schematic diagram of the signal distribution collected by each collecting fiber in the collecting fiber bundle is shown in super-resolution imaging mode, wherein the annular shape represents the position and relative size of the Airy disk of the collecting beam emitted from the collecting lens.

[0071] Specifically, the acquisition control module receives feedback optical signals from 2N+1 collecting optical fibers, and calculates and reconstructs 2N+1 images based on the galvanometer control signals. This includes: using the image generated by the signal received by the central collecting fiber as a reference, performing offset correction on the 2N images according to a pre-designed offset, and then superimposing the 2N+1 images to obtain a super-resolution AOSLO image with both high signal-to-noise ratio and high resolution. It should be noted that, using the image generated by the signal received by the central collecting fiber as a reference, the other 2N images each exhibit pixel-level offsets in different directions. These offsets are determined by the relative positions of the collecting fibers in the fiber bundle, and the offset = D / M (where D is the distance from the surrounding collecting fibers to the central collecting fiber, and M is the magnification of the reflected light channel, i.e., M = image height on the fiber bundle / image height on the retina).

[0072] Therefore, in the super-resolution imaging mode, the retinal imaging device provided in this application embodiment can obtain ultra-high resolution confocal images and a high signal-to-noise ratio when imaging the retina. It can also obtain high signal-to-noise ratio signals for the dense cone cells near the fovea of ​​the eye.

[0073] Comparing the working processes of the retinal imaging device in non-confocal imaging mode, confocal imaging mode, and super-resolution imaging mode, it can be seen that the retinal imaging device can work in all three modes and share most of the optical path. The three modes can be switched by controlling the light source in the light source module and the movement of the beam shortening component.

[0074] Given that existing retinal imaging devices have a small imaging range per image, covering only a small area on the retina, users cannot determine the exact location of the imaging area on the retina based on a single scan image. If a user has a lesion or cell tissue that they want to observe, they cannot determine whether the scan image is the region of interest, nor can they determine where the scan image should be moved to reach the region of interest. They can only search by traversing the area, which takes a lot of time to find the region of interest on the retina. In addition, the operation of the device is complicated and has low clinical efficiency.

[0075] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1As shown, the retinal imaging device further includes a fundus imaging module 400 for acquiring fundus images. Specifically, in one embodiment of this application, the fundus imaging module includes a fundus illumination source (not shown in the figure) and a fundus camera 403. The fundus illumination source generates illumination light to illuminate the fundus, and the fundus camera 403 acquires the fundus images. Optionally, the fundus illumination source can be a fundus illumination LED. The fundus illumination light generated by the fundus illumination source illuminates the fundus, and after reflection from the fundus, it is acquired by the fundus camera to generate fundus images in real time. The fundus imaging module 400 can also employ an optical system such as a wide-field scanning laser ophthalmoscope to acquire images.

[0076] This means that, because the imaging area displayed in the fundus image is significantly larger than and includes the imaging area displayed in the scanned image, the location of the imaging area on the retina can be obtained from the fundus image. Therefore, the user can determine whether the current scanned image is the region of interest (ROI) and obtain the relative position information between the scanned image and the ROI, guiding the user to directly and quickly locate the ROI on the retina. This retinal imaging device is simple to operate and highly efficient in clinical practice.

[0077] Optionally, in one embodiment of this application, the following continues... Figure 1 As shown, the fundus imaging module 400 further includes a fixation unit 406, which is used to generate a fixation pattern to guide the eye's gaze direction.

[0078] Optionally, the fixation unit 406 can be a display screen or an LED array. The fixation unit 406 (such as a display screen) will display a fixation pattern (such as a lit cross). The subject's eyes will be asked to stare at the fixation pattern. If the position of the fixation pattern is adjusted, the subject's eyes will be guided to rotate and change the direction of gaze.

[0079] Optionally, in one embodiment of this application, the following continues... Figure 1 As shown, the fundus imaging module 400 also includes a pupil illumination source 404 and a pupil camera 405. The pupil illumination source 404 generates pupil illumination light to illuminate the eyeball, and the pupil camera 405 acquires pupil images.

[0080] Optionally, the pupil illumination source 404 can be a pupil illumination LED. The light emitted by the pupil illumination source 404 illuminates the entire surface of the eye, and the pupil camera 405 collects the light reflected back through the pupil to generate a pupil image in real time.

[0081] Based on any of the above embodiments, in one embodiment of this application, the retinal imaging device may further include a movable component for adjusting 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.

[0082] Optionally, the movable component can be a headrest component, used to place the subject's head. The movement of the movable component drives the subject's head to move, thereby adjusting 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.

[0083] Alternatively, the moving component is connected to the retinal imaging device and moves 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.

[0084] Alternatively, the moving component can move both the subject's head and 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.

[0085] When the moving part 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. The motor controller controls the three-axis headrest motor to move the subject's head, so as to align the optical axis of the retinal imaging device with the pupil.

[0086] It is understood that, in this embodiment, the fundus illumination source, fundus camera, and fixation unit in the fundus imaging module, combined with the beam scanning module, enable the imaging beam to quickly locate the region of interest in the fundus on the retina, greatly improving scanning efficiency. Furthermore, the pupil illumination source, pupil camera, and moving parts enable alignment of the optical axis of the retinal imaging device with the pupil, ensuring efficient and accurate scanning of the subject's eyeball and improving clinical efficiency.

[0087] Optional, such as Figure 1 As shown, the fundus imaging module may further include a third beam splitter 401 and a fourth beam splitter 402, so that the light beam emitted by the fundus illumination source enters the eyeball, and the imaging light beam emitted by the beam scanning module 200 enters the eyeball. It also allows the light beam reflected from the fundus to be collected by the fundus camera 403, the pupil camera 405, and the beam scanning module 200. In this embodiment, the fundus illumination source is located near the fundus camera, so that the signal emitted by the fundus illumination source and the signal received by the fundus camera can share the same optical path. However, this application does not limit this. In other embodiments of this application, the fundus imaging module may add more beam splitters as needed, splitting the fundus illumination source and the fundus camera 403 into two paths, splitting the fixation unit 406 and the pupil camera 405 into two paths, merging the pupil illumination source into the main optical path, etc., depending on the specific situation.

[0088] like Figure 12As shown, based on any of the above embodiments, in one embodiment of this application, the acquisition control module 300 includes a data acquisition unit 301, a calculation unit 302, and a control component; wherein, the data acquisition unit 301 has four input terminals and one output terminal. The four input terminals of the data acquisition unit 301 are respectively used to acquire signals output by the detector component 107, the wavefront sensor 109, the pupil camera 405, and the fundus camera 403. The output terminal of the data acquisition unit 301 is connected to the calculation unit 302 and is used to output 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 operation of each component of the retinal imaging device, thereby controlling the operation of the retinal imaging device.

[0089] Specifically, the control components include a scanning mirror control unit 303, a wavefront modulator controller 304, a light source controller 305, a motor controller 306, and a fixation unit controller 307. The scanning mirror control unit 303 controls the operation of the first scanning mirror 206, the second scanning mirror 207, and the tracking mirror 209. The wavefront modulator controller 304 controls the operation of the wavefront modulator 208. The light source controller 305 controls the operation of the light source module, the fundus illumination source, and the pupil illumination source. The motor controller 306 controls the control module to control the movement of the beam-constricting assembly. The fixation unit controller 307 controls the operation of the fixation unit.

[0090] Specifically, when the retinal imaging device is working, the wavefront dot pattern detected by the wavefront sensor is acquired by the data acquisition unit and sent to the computing unit. The computing unit calculates the aberrations based on the wavefront dot pattern detected by the wavefront sensor, generates a correction signal, and then controls the wavefront compensation amount of the wavefront modulator through the wavefront modulation controller to correct the aberrations of the retinal imaging system, improve the resolution of the retinal imaging system, and achieve ultra-high-definition cell-level retinal imaging resolution.

[0091] The detector assembly collects the fundus reflection signal and / or scattering signal reflected by the second beam splitter and sends it to the data acquisition unit for acquisition. The computing unit processes the signal acquired by the data acquisition unit based on the working mode of the retinal imaging device to generate a real-time video-level frame rate fundus image. Based on the real-time fundus image, the computing unit calculates the direction and speed of eye movement in real time. The eye tracking signal is applied to the galvanometer (first scanning galvanometer, second scanning galvanometer and / or 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, achieving the purpose of eye tracking and real-time image stabilization.

[0092] The pupil camera acquires pupil images of the subject in real time. The calculation unit observes the pupil offset through the pupil images and controls the three-axis head support motor through the motor controller to move the subject's head to align the subject's head with the light path.

[0093] The fundus camera acquires infrared fundus images of the subject in real time. By observing the infrared fundus images of the subject, the operator of the retinal imaging device can confirm the relative position of the acquired small area on the fundus, which serves as a navigation tool on the retina.

[0094] The light source controller controls the infrared light source in the light source module to emit beams from multiple or one optical fiber according to the imaging mode selected by the operator of the retinal imaging device. The motor controller controls whether to move the beam-shrinking component in front of the collecting lens according to the selected imaging mode.

[0095] In summary, the retinal imaging device provided in this application combines multi-point scanning imaging mode (i.e., confocal imaging mode) with super-resolution imaging mode and non-confocal imaging mode. With a simple structure, it can achieve mutual compatibility of the three major functions of high-speed AOSLO imaging with multi-point scanning, super-resolution AOSLO imaging and non-confocal scattering imaging. At the same time, it solves the two problems of slow imaging speed and single imaging mode of current AOSLO devices.

[0096] Moreover, the retinal imaging device provided in this application embodiment can achieve super-resolution AOSLO function by adding a set of movable beam-shrinking components, so that AOSLO can improve the resolution while retaining sufficient signal strength, thus solving the problem of the mutual limitation between imaging resolution and signal-to-noise ratio of current AOSLO devices.

[0097] Therefore, it can be seen that the retinal imaging device provided in this application realizes simple switching between the above three AOSLO modes through the control loop of the hardware system.

[0098] Furthermore, the retinal imaging device provided in this application embodiment uses most of the optical path during the switching of the three imaging functions, and has a simple structure and small size.

[0099] Accordingly, this application also provides a retinal imaging method, applied to the retinal imaging device provided in any of the above embodiments, wherein the retinal imaging device includes at least one operating mode. Specifically, the retinal imaging method includes:

[0100] In the first working mode (non-confocal imaging mode), the light source module generates imaging light, which is incident on the beam scanning module. The beam modulated by the beam scanning module enters the eyeball, and the feedback beam formed by reflection and scattering from the retina is incident on the detection module via the beam scanning module. In the detection module, the central collecting fiber in the collecting fiber bundle is used to collect reflected signals, and at least a portion of the other 2N collecting fibers in the collecting fiber bundle of the detection module are symmetrically distributed to collect scattered signals.

[0101] A confocal image of the retina is obtained based on the reflected signal acquired from the collected fiber bundle, and a nonfocal image of the retina is obtained based on the scattered signal acquired from the collected fiber bundle.

[0102] Optionally, in one embodiment of this application, the light source module includes multiple light sources and signal transmission paths corresponding to each light source, and the imaging light generated by the light source is incident on the beam scanning module through the signal transmission paths; the retinal imaging method further includes:

[0103] In the second working mode (confocal imaging mode), imaging light is generated by multiple light sources in the light source module. The imaging light generated by the multiple light sources is incident on the beam scanning module. The beam modulated by the beam scanning module enters the eyeball. The feedback beam formed by the retina is incident on multiple collecting optical fibers in the collecting fiber bundle in the detection module that correspond to the signal transmission path through the beam scanning module.

[0104] A confocal image of the retina is obtained based on the reflected signal in the feedback beam acquired by the collected fiber bundle.

[0105] Optionally, in one embodiment of this application, the retinal imaging device further includes a super-resolution imaging mode; correspondingly, in this embodiment, the imaging method further includes:

[0106] In the super-resolution imaging mode (i.e., the third working mode), the beam-shrinking component is inserted into the detection module so that the feedback beam formed by the retina is modulated by the beam-shrinking component and then transmitted to the 2N+1 collecting fibers of the collecting fiber bundle; based on the reflected signal in the feedback beam obtained by the collecting fiber bundle, a super-resolution confocal image of the retina is obtained.

[0107] It should be noted that the principle of the retinal imaging method provided in this application embodiment is the same as the principle of the retinal imaging device provided in the above embodiments of this application, and can be found in the description of the retinal imaging device section. Further details will not be repeated here.

[0108] The various embodiments in this specification are described in a progressive, parallel, or combined manner. Each embodiment focuses on its differences from other embodiments, and similar or identical parts between embodiments can be referred to interchangeably. For the apparatuses disclosed in the embodiments, since they correspond to the methods disclosed in the embodiments, the descriptions are relatively simple, and relevant parts can be referred to the method section.

[0109] It should be noted that, in the description of this application, the accompanying drawings and embodiments are illustrative rather than restrictive. The same reference numerals throughout the embodiments identify the same structures. In this document, relational terms such as "first" and "second" are used merely to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that an article or device comprising a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such an article or device. Without further limitation, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in an article or device comprising the aforementioned element.

[0110] The above description of the disclosed embodiments enables those skilled in the art to make or use this application. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of this application. Therefore, this application is not 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: A light source detection module, a beam scanning module, and an acquisition control module are characterized in that the light source detection module includes a light source module and a detection module, the imaging light generated by the light source module is incident on the beam scanning module, and the beam scanning module includes a scanning galvanometer. The beam modulated by the beam scanning module enters the eyeball, and the feedback beam formed by the retina is incident on the detection module through the beam scanning module. The detection module includes a collection fiber bundle, which includes 2N+1 collection fibers, wherein at least a portion of the 2N collection fibers are symmetrically distributed with one collection fiber as the center, and N≥1. The acquisition and control module is connected to the light source detection module and the beam scanning module, respectively.

2. The retinal imaging device of claim 1, wherein, The 2N collecting optical fibers are symmetrically distributed with one collecting optical fiber as the center.

3. The retinal imaging device of claim 1, wherein, The beam scanning module also includes a wavefront modulator; the detection module detects the feedback beam in two optical paths, wherein the first optical path includes the collecting fiber bundle and the second optical path includes a wavefront sensor.

4. The retinal imaging device of claim 1, wherein, The detection module further includes an insertable beam-shrinking component, through which the feedback beam enters the collecting fiber bundle.

5. The retinal imaging device of claim 4, wherein, After the feedback beam passes through the beam-shrinking assembly, the reflected signal in the feedback beam is collected by all 2N+1 collecting fibers of the collecting fiber bundle.

6. The retinal imaging device of claim 1 or 5, wherein, The light source module includes one or more light sources and a signal transmission path corresponding to each light source. The imaging light generated by the light source is incident on the beam scanning module through the signal transmission path.

7. The retinal imaging device of claim 6, wherein, The signal transmission path is an optical fiber, and the light source module includes multiple light sources and multiple transmitting optical fibers, the end faces of which are located on a straight line.

8. The retinal imaging device of claim 1, wherein, The beam scanning module further includes: multiple optical conjugate components, which form multiple pupil conjugate surfaces, and the scanning galvanometer, the eyeball, and the light source module are located on different pupil conjugate surfaces.

9. The retinal imaging device of claim 8, wherein, The beam scanning module further includes a tracking mirror and / or a wavefront modulator, wherein the tracking mirror and / or wavefront modulator, the scanning mirror, the eyeball, and the light source module are respectively located on different conjugate surfaces of the pupil of the eyeball.

10. The retinal imaging device of claim 1, wherein, The retinal imaging device also includes a fundus imaging module for acquiring fundus images.

Images