A retinal imaging device

Abstract

The application discloses a retinal imaging device, comprising a light source detection module and a light beam scanning module, the light source detection module comprises a first light source module, a first detection module, a second light source module and a second detection module; the excitation light generated by the first 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 fluorescent light beam formed by exciting the retina is incident to the first detection module through the light beam scanning module, which is used for fluorescence imaging; the imaging light generated by the second light source module is incident to the light beam scanning module, the light beam entering the eyeball after being modulated by the light beam scanning module, and the feedback light beam formed by the retina is incident to the second detection module through the light beam scanning module, the second detection module comprises a collection optical fiber bundle, the collection optical fiber bundle comprises a plurality of collection optical fibers, and the plurality of collection optical fibers are used for collecting the reflected signal or part of the reflected signal and part of the scattered signal. The retinal imaging device can obtain various retinal images.

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. In order to more effectively diagnose and treat retinal-related diseases, the optimization of diagnostic devices is essential. In other words, high-resolution imaging devices for the retina are of great significance for the diagnosis and treatment evaluation of retinal-related diseases.

[0003] Taking the human retina as an example, the retina has a very complex structure. For instance, photoreceptor cells on the retina are the only cells in the human retina that can receive light stimulation and convert light signals into chemical signals. As the first line of defense for human vision, the structural morphology and density of photoreceptor cells directly affect the function of the human retina. The retinal pigment epithelium (RPE) is located below the photoreceptor cell layer and plays an important role in maintaining visual circulation, protection, and anti-oxidation. Therefore, its structure and function are crucial to normal vision. Changes in the RPE can lead to retinal diseases and impair normal retinal function. Retinal blood vessels are distributed in both the inner and outer layers of the retina and, like other blood vessels in the body, play a role in substance exchange and transport. Various retinal diseases, such as diabetic retinopathy (DR) and age-related macular degeneration (AMD), can cause changes in parameters such as the thickness and blood flow velocity of retinal blood vessels.

[0004] However, existing retinal imaging devices operate in a relatively simple mode and cannot obtain a variety of images of the retina. Utility Model Content

[0005] In view of the above problems, this application provides a retinal imaging device to achieve multiple imaging of the retina using the same retinal imaging device. The specific solution is as follows:

[0006] A retinal imaging device includes: a light source detection module and a beam scanning module, wherein the light source detection module includes a first light source module, a first detection module, a second light source module, and a second detection module; wherein,

[0007] The excitation light generated by the first light source module is incident on the beam scanning module, and after being modulated by the beam scanning module, it enters the eyeball, exciting the fluorescence beam formed by the retina and then being incident on the first detection module via the beam scanning module for fluorescence imaging.

[0008] The imaging light generated by the second light source module is incident on the beam scanning module. The beam beam modulated by the beam scanning module enters the eyeball. The feedback beam formed by the retina is incident on the second detection module through the beam scanning module. The second detection module includes a collection fiber bundle, which includes multiple collection fibers. The multiple collection fibers are used to collect the reflected signal from the retina, or a portion of the collection fibers are used to collect the reflected signal from the retina, and another portion of the collection fibers are used to collect the scattered signal from the retina.

[0009] Optionally, the collecting fiber bundle 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 2N+1 collecting fibers are used to collect the reflected signal from the retina, or the central collecting fiber is used to collect the reflected signal from the retina, and the 2N collecting fibers are used to collect the scattered signal from the retina.

[0010] Optionally, the 2N collecting optical fibers are symmetrically distributed with one collecting optical fiber as the center.

[0011] Optionally, the central collecting fiber is a double-clad fiber, which includes a core, a first cladding, and a second cladding. The core of the double-clad fiber is used to transmit the imaging light emitted by the second light source module, and the first cladding of the double-clad fiber is used to transmit the reflected signal from the retina. The reflected signal is transmitted to the second detection module via a coupling fiber for reflection imaging.

[0012] Optionally, the light source detection module further includes a first optical fiber, which includes a first double-clad optical fiber and a first coupling optical fiber;

[0013] The excitation light generated by the first light source module is transmitted through the core of the first double-clad optical fiber and incident on the beam scanning module. After being modulated by the beam scanning module, it enters the eyeball and excites the retina to form a fluorescent beam, which is then transmitted through the beam scanning module to the first double-clad optical fiber. The beam is then transmitted through the first cladding of the first double-clad optical fiber and the first coupling optical fiber to the first detection module for fluorescence imaging.

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

[0015] Optionally, the beam scanning module further includes a wavefront modulator; the second 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.

[0016] Optionally, the second detection module further includes: an insertable beam-shrinking assembly, through which the feedback beam enters the collecting fiber bundle, the collecting fiber bundle being used to collect reflected signals from the retina.

[0017] Optionally, the second 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.

[0018] Optionally, the signal transmission path is an optical fiber, the second light source module includes multiple light sources and multiple transmitting optical fibers, the end faces of the multiple transmitting optical fibers are located in a straight line; the collecting optical fiber bundle is used to collect the reflected signal from the retina.

[0019] This solution has the following advantages:

[0020] In the retinal imaging device provided in this application embodiment, the excitation light generated by the first light source module is incident on the beam scanning module, and after being modulated by the beam scanning module, it enters the eyeball. The fluorescent beam formed by exciting the retina is incident on the first detection module through the beam scanning module for fluorescence imaging. It can provide good imaging contrast for different structures on the retina (such as cells such as retinal pigment epithelial cells) and reflect their intrinsic physiological and chemical information.

[0021] In the retinal imaging device provided in this application embodiment, the imaging light generated by the second light source module is incident on the beam scanning module and modulated by the beam scanning module before entering the eyeball. The feedback beam from the retina is incident on the second detection module through the beam scanning module. The second detection module collects the reflection signal from the retina for reflection imaging, which provides better imaging contrast for highly reflective structures on the retina, such as photoreceptor cells and nerve fibers.

[0022] As can be seen from the above, the retinal imaging device provided in this application embodiment can obtain confocal scanning fluorescence images and confocal scanning reflectance images. Furthermore, the second detection module can not only collect reflectance signals from the retina to obtain confocal scanning reflectance images, but also collect scattering signals from the retina to obtain non-confocal scattering images. These are used for scattering imaging of specific strong scattering and weak reflection microstructures on the human retina, such as blood vessel walls, red blood cells, and photoreceptor cell segments, exhibiting good endogenous contrast and improving the comprehensiveness of retinal information acquisition and imaging contrast. In addition, the retinal imaging device provided in this application embodiment, when imaging fluorescent substances with different fluorescence spectra, only requires changing the laser wavelength generated by the first light source module to match the excitation wavelength of the fluorescent substance, achieving multi-wavelength broad-spectrum fluorescence imaging. It can image and measure both fluorescent substances on the human retina and artificially injected fluorophores, providing multiple means of observing physiological information of the human retina. Attached Figure Description

[0023] The above and other features, advantages, and aspects of the embodiments of this disclosure will become more apparent from the accompanying drawings and the following detailed description. Throughout the drawings, the same or similar reference numerals denote the same or similar elements. It should be understood that the drawings are schematic, and the originals and elements are not necessarily drawn to scale.

[0024] Figure 1 This application provides a schematic diagram of the structure of a retinal imaging device;

[0025] Figure 2 A schematic diagram of the structure of the first optical fiber in a retinal imaging device provided in this application;

[0026] Figure 3 A schematic diagram of the structure of the first double-clad fiber in the first optical fiber of a retinal imaging device provided in this application;

[0027] Figure 4 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;

[0028] Figure 5 A schematic diagram of the structure for collecting the fiber optic bundle in a retinal imaging apparatus provided in another embodiment of this application;

[0029] Figure 6 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 non-confocal imaging mode.

[0030] Figure 7This is a schematic diagram showing the corresponding signal distribution in the second light source module and the collecting fiber bundle when the retinal imaging device provided in one embodiment of this application is operating in high-speed imaging mode.

[0031] Figure 8 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 high-speed imaging mode.

[0032] Figure 9 This is another structural schematic diagram of a retinal imaging device provided in this application;

[0033] Figure 10 Another structural schematic diagram of a retinal imaging device provided in this application;

[0034] 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 this application during the super-resolution imaging mode.

[0035] Figure 12 This application provides a schematic diagram of the acquisition control module in a retinal imaging device.

[0036] Figure 13 This is a schematic diagram illustrating the working process of a retinal imaging device provided in this application.

[0037] Figure label:

[0038] Light source detection module-100; First light source module-101; First optical fiber-102; First double-clad optical fiber-1021; First coupling optical fiber-1022; First detection module-103; First collimating element-104; Second light source module-105; Second detection module-106; Collecting lens-1061; Collecting fiber bundle-1062; Second detection assembly-1063; Wavefront sensor-1064; Beam converging assembly-1065; First beam splitter-107; Second collimating element-108; Second beam splitter-109; Dichroic mirror-110; Beam scanning module-200; First optical conjugate assembly-201; Second optical conjugate assembly-202; Third light source module-100; Components: 203 (Optical Conjugate Component); 204 (Fourth Optical Conjugate Component); 205 (Fifth Optical Conjugate Component); 206 (First Scanning Mirror); 207 (Second Scanning Mirror); 208 (Wavefront Modulator); 209 (Tracking Mirror); 300 (Acquisition Control Module); 400 (Fundus Imaging Module); 401 (Third Beam Splitter); 402 (Fourth Beam Splitter); 403 (Fundus Camera); 404 (Pupil Illumination Source); 405 (Pupil Camera); 406 (Fixed Fixation Unit); 301 (Data Acquisition Unit); 302 (Computation Unit); 303 (Scanning Mirror Control Unit); 304 (Wavefront Modulator Controller); 305 (Light Source Controller); 307 (Fixed Fixation Unit Controller); 306 (Motor Controller). Detailed Implementation

[0039] 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.

[0040] 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.

[0041] 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.

[0042] As described in the background section, existing retinal imaging devices operate in a relatively limited mode and are unable to acquire a variety of images of the retina.

[0043] 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 and a beam scanning module 200. The light source detection module 100 includes a first light source module 101, a first detection module 103, a second light source module 105, and a second detection module 106.

[0044] The excitation light generated by the first light source module 101 is incident on the beam scanning module 200, and after being modulated by the beam scanning module 200, it enters the eyeball. The fluorescence beam formed by exciting the retina is incident on the first detection module 103 through the beam scanning module 200 for fluorescence imaging.

[0045] The imaging light generated by the second light source module 105 is incident on the beam scanning module 200. The beam, modulated by the beam scanning module 200, enters the eyeball. The feedback beam formed by the retina is incident on the second detection module 106 via the beam scanning module 200. The second detection module 106 includes a collection fiber bundle 1062, which includes multiple collection fibers. The multiple collection fibers are used to collect the reflected signal from the retina, or a portion of the collection fibers are used to collect the reflected signal from the retina, and another portion of the collection fibers are used to collect the scattered signal from the retina.

[0046] It should be noted that, in the embodiments of this application, all of the plurality of collecting optical fibers can be used to collect the reflected signals of the retina for reflective imaging, or a portion can be used to collect the reflected signals of the retina for reflective imaging, and another portion can be used to collect the scattered signals of the retina for scattering imaging.

[0047] In the retinal imaging device provided in this application embodiment, the excitation light generated by the first light source module is incident on the beam scanning module, and after being modulated by the beam scanning module, it enters the eyeball. The fluorescent beam formed by exciting the retina is incident on the first detection module through the beam scanning module for fluorescence imaging. It can provide good imaging contrast for different structures on the retina (such as cells such as retinal pigment epithelial cells) and reflect their intrinsic physiological and chemical information.

[0048] In the retinal imaging device provided in this application embodiment, the imaging light generated by the second light source module is incident on the beam scanning module and modulated by the beam scanning module before entering the eyeball. The feedback beam from the retina is incident on the second detection module through the beam scanning module. The second detection module collects the reflection signal from the retina for reflection imaging, which provides better imaging contrast for highly reflective structures on the retina, such as photoreceptor cells and nerve fibers.

[0049] In the retinal imaging device provided in this application embodiment, a feedback beam formed by retinal reflection and scattering is incident on the second detection module through the beam scanning module. The reflected signal from the retina in the feedback beam is collected by a portion of the collecting fiber bundle for reflection imaging to obtain a confocal scanning reflection image of the retina. The scattered signal from the retina in the feedback beam is collected by another portion of the collecting fiber bundle for scatter imaging. 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 retinal information acquisition and imaging contrast.

[0050] Furthermore, the retinal imaging device provided in this application embodiment can image fluorescent substances with different fluorescence spectra simply by changing the laser wavelength generated by the first light source module to match the excitation wavelength of the fluorescent substance, thereby realizing fluorescence imaging with multiple wavelengths and a wide spectrum. It can image and measure fluorescent substances on the human retina and artificially injected fluorophores, providing a variety of means to observe physiological information of the human retina.

[0051] Based on the above embodiments, in one embodiment of this application, the following continues... Figure 1 As shown, the retinal imaging device further includes an acquisition control module 300, which is used to form a fluorescence image of the retina based on the detection signal of the first detection module 103, and to form a reflection image and / or a scattering image of the retina based on the detection signal of the second detection module 106.

[0052] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 As shown, the light source detection module also includes a first optical fiber 102, such as... Figure 2 As shown, the first optical fiber includes a first double-clad optical fiber 1021 and a first coupling optical fiber 1022. The excitation light generated by the first light source module 101 is transmitted through the core of the first double-clad optical fiber 1021 and incident on the beam scanning module 200. After being modulated by the beam scanning module 200, it enters the eyeball and excites the fluorescence beam formed by the retina. The fluorescence beam is incident on the first double-clad optical fiber 1021 through the beam scanning module 200 and transmitted to the first detection module 103 through the first cladding of the first double-clad optical fiber 1021 and the first coupling optical fiber 1022 for fluorescence imaging. This provides good imaging contrast for different structures on the retina (such as retinal pigment epithelial cells) and reflects their intrinsic physiological and chemical information.

[0053] Optionally, the first coupling fiber is a multimode fiber, and the first detection module includes a first detector for collecting fluorescence signals, but this application does not limit this and it depends on the specific circumstances.

[0054] As can be seen from the above, the retinal imaging device provided in this application embodiment utilizes a first optical fiber to realize the transmission of excitation light emitted by the first light source module and the transmission of the fluorescence beam formed by exciting the retina, such as... Figure 2 and Figure 3 As shown, the first optical fiber 102 includes a first double-clad optical fiber 1021 and a first coupling optical fiber 1022. The first double-clad optical fiber 1021 includes a core A, a first cladding B, and a second cladding C. The core A is located in the central region of the first cladding B, and the second cladding C wraps around the outer surface of the first cladding B. The core A of the first double-clad optical fiber 1021 is used to transmit the single-mode excitation light emitted by the first light source module 101, and the first cladding B is used to transmit the fluorescence beam that excites the retina to form a multimode fluorescence beam. The end face of the first cladding B is very small, typically a small aperture with a radius of several hundred micrometers, which can meet the requirements of a confocal aperture and exclude light signals other than the focal point of the fundus. The radius of the core A at its center is very small and has almost no impact. Therefore, in the retinal imaging device provided in this application embodiment, the end face of the core A and the end face of the first cladding B of the first double-clad optical fiber 1021 respectively serve as the light emission point of the excitation light and the confocal aperture for fluorescence collection, thereby satisfying the optical conjugate position and forming a self-confocal structure. Its self-confocal surface is as follows: Figure 2 Position D in the first light source module is used, and the light emission point of the light source and the confocal aperture maintain a constant relative position. This prevents positional changes between the collection aperture and the light emission point of the light source due to vibration, collision, thermal expansion and contraction of the retinal imaging device. This significantly reduces the requirements for adjustment accuracy and stability when the retinal imaging device achieves fluorescence confocal imaging during use. It should be noted that in this embodiment, the second cladding layer C provides a refractive index difference, forming a refractive index difference with the first cladding layer B. This allows the fluorescence signal to be transmitted through total internal reflection in the first cladding layer B, preventing light transmitted within the first cladding layer B from exiting the second cladding layer C and improving the collection efficiency of the fluorescence signal.

[0055] It should be noted that, since the dimensions of the core and the first cladding in the first double-clad fiber are relatively small at the end face of the first optical fiber, in one embodiment of this application, based on the above embodiments, the following continues... Figure 1As shown, the light source detection module 100 further includes a first collimating element 104, which is located in the transmission optical path of the excitation light output from the first optical fiber 102. In this embodiment, the first collimating element 104 is used to collimate the excitation light output from the first optical fiber 102 before it enters the beam scanning module 200, so that when the excitation light is emitted from the beam scanning module 200 and enters the eye, it can cover the area to be imaged. Similarly, the first collimating element 104 is also used to converge the fluorescence beam output from the beam scanning module 200 before it enters the first optical fiber 102, so that the fluorescence beam output from the beam scanning module 200 can be incident on the first cladding B of the smaller diameter first double-clad optical fiber 1021, and then collected by the first detection module 103 after being transmitted through the first cladding B of the first double-clad optical fiber 1021 and the first coupling optical fiber 1022.

[0056] Optionally, in one embodiment of this application, the first collimating element may be an achromatic lens, a self-focusing lens, or an off-axis parabolic mirror, etc. This application does not limit this, and the specific choice depends on the circumstances.

[0057] Specifically, in one embodiment of this application, the first light source module includes a laser for generating fluorescent excitation light. It should be noted that, optionally, in this embodiment, the laser can be a beam combiner laser capable of generating multiple wavelengths of laser light simultaneously, or it can be a tuned laser. This application does not limit this, and it depends on the specific circumstances.

[0058] It should be noted that in this embodiment, the fluorescent substance is located on the retina of the eye. It can be naturally present in the eye, such as lipofuscin, carotene, or melanin, or it can be artificially injected into the bloodstream and reach the retina via blood circulation, such as indocyanine green or sodium fluorescein. Different fluorescent substances generally have unique fluorescence excitation and emission spectra. Roughly speaking, after irradiation with a laser of a certain wavelength 'a', a fluorescence signal of another wavelength 'b' will be generated. Each fluorescent substance has a different distribution of 'a' and 'b'.

[0059] The retinal imaging device provided in this application transmits excitation light through the core of the first double-clad optical fiber and fluorescence through the first cladding of the first double-clad optical fiber. That is, different signal transmission channels are used to transmit excitation light and fluorescence respectively. Thus, when performing fluorescence-based imaging, the stability of the confocal structure is maintained without the need for additional structures to separate excitation light and fluorescence. Therefore, when imaging fluorescent substances with different fluorescence spectra, the retinal imaging device provided in this application only needs to change the wavelength of the light source generated by the first light source module to match the excitation wavelength of the fluorescent substance. This achieves fluorescence imaging with multiple wavelengths and a wide spectrum, and can image and measure fluorescent substances on the human retina and artificially injected fluorophores, providing a variety of means to observe the physiological information of the human retina.

[0060] Furthermore, the retinal imaging device provided in this application transmits excitation light through the core of the first double-clad optical fiber and transmits fluorescence through the first cladding of the first double-clad optical fiber. That is, it uses different signal transmission channels to transmit excitation light and fluorescence respectively, so that the excitation light emitted by the first light source module can be transmitted entirely through the core of the first double-clad optical fiber to the beam scanning module for exciting the fluorescent material on the retina, thereby improving the utilization rate of the light emitted by the first light source module. At the same time, since the core diameter of the first double-clad optical fiber is very small, most of the fluorescence signal generated by exciting the fluorescent material on the retina will enter the first detection module through the first cladding for fluorescence imaging, thereby improving the light utilization rate of the fluorescence formed by the excitation light illuminating the retina.

[0061] Therefore, the retinal imaging device provided in this application embodiment utilizes the first optical fiber to transmit excitation light and fluorescence. While maintaining the stability of the confocal structure, it can also significantly reduce light waste and improve light utilization, which brings great convenience to weak light signal imaging such as retinal fluorescence imaging.

[0062] Based on any of the above embodiments, in one embodiment of this application, such as Figure 4 As shown, the collecting fiber bundle includes 2N+1 collecting fibers, wherein at least a portion of the 2N collecting fibers are symmetrically distributed around a central collecting fiber, and N≥1, so that the collecting fiber bundle can collect reflected signals and / or scattered signals. Specifically, in this embodiment, when the collecting fiber bundle is used to collect the reflected signal of the retina, all 2N+1 collecting fibers are used to collect the reflected signal of the retina; or a portion of the collecting fibers in the collecting fiber bundle are used to collect the reflected signal of the retina, and another portion of the collecting fibers are used to collect the scattered signal of the retina, that is, the central collecting fiber in the 2N+1 collecting fibers is used to collect the reflected signal of the retina, and the 2N collecting fibers are used to collect the scattered signal of the retina.

[0063] Optionally, in one embodiment of this application, the 2N collecting optical fibers are symmetrically distributed around a single collecting optical fiber. Specifically, the 2N collecting optical fibers can be arranged symmetrically in a circle around a single collecting optical fiber, and so on. Figure 4 As 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 5 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.

[0064] For ease of description, the operating mode of the retinal imaging device is defined as follows: when a portion of the collecting fiber bundle is used to collect the reflected signal from the retina and another portion is used to collect the scattered signal from the retina, the operating mode of the retinal imaging device is defined as the first operating mode; when all the collecting fibers in the collecting fiber bundle are used to collect the reflected signal from the retina, the operating mode of the retinal imaging device is defined as the second operating mode.

[0065] When the retinal imaging device provided in this embodiment operates in the first working mode, the imaging light generated by the second light source module is incident on the beam scanning module, modulated by the beam scanning module, and enters the eyeball. A feedback beam is formed by reflection and scattering from the retina and incident on the second detection module via the beam scanning module. 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 4 The surrounding collecting fibers are symmetrically distributed around the central collecting fiber (forming a group of two surrounding collecting fibers), so that when the retinal imaging device obtains a non-confocal scattering image based on the scattering signal of the feedback beam (hereinafter referred to as "non-confocal imaging mode"), it can perform differential subtraction on the signals output by each group of surrounding collecting fibers to obtain a scattered light signal enhanced in a specific direction, and then filter and superimpose multiple groups of signals (e.g., Figure 4The device generates three sets of signals, ultimately reconstructing the enhanced signal from the retinal scattering body. 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, exhibiting good endogenous contrast and improving the comprehensiveness of information acquisition and imaging contrast. Simultaneously, the retinal imaging device also obtains a confocal scanning reflection image of the retina by collecting the reflected signals transmitted via a central optical fiber.

[0066] Optionally, based on any of the above embodiments, in one embodiment of this application, the central collecting optical fiber is a common optical fiber, and the process continues as follows: Figure 1 As shown, the light source detection module 100 further includes a first beam splitter 107 located on the output light path of the second light source module 105. In this embodiment, the second detection module 106 includes a collecting lens 1061, a collecting fiber bundle 1062, and a second detection component 1063 located on the light path formed by the reflection of the reflected beam by the first beam splitter 107. In specific operation, the incident light emitted by the second light source module 105 is transmitted through the first beam splitter 107 to the beam scanning module 200. After being modulated by the beam scanning module 200, it enters the eyeball, is reflected by the retina, and forms a reflected beam that returns to the beam scanning module 200. It is transmitted in the opposite direction to the transmission direction of the incident light until it enters the light source detection module 100, is reflected by the first beam splitter 107, and enters the second detection module 106. It is collected by the collecting lens 1061 in the second detection module 106, and after passing through the collecting fiber bundle 1062, it is received by the second detection component 1063 to form a reflected image and / or a scattered image of the retina.

[0067] Optionally, based on the above embodiments, in one embodiment of this application, the following continues... Figure 1 As shown, the light source detection module 100 further includes a second collimating element 108 located between the second light source module 105 and the first beam splitter 107, used to collimate the light emitted by the second light source module 105 before directing it toward the first beam splitter 107. Specifically, in one embodiment of this application, the second collimating element is a lens, a mirror, a graded refractive index lens, etc., and the first beam splitter can be a beam splitter, but this application does not limit this and it depends on the specific circumstances.

[0068] In another embodiment of this application, the central collecting optical fiber is a double-clad optical fiber, which includes a core, a first cladding, and a second cladding. The core of the double-clad optical fiber is used to transmit imaging light emitted by the second light source module, and the first cladding is used to transmit the reflected signal from the retina. The reflected signal is transmitted to the second detection module via a coupling optical fiber for reflection imaging. It should be noted that, compared to using ordinary optical fiber for the central collecting optical fiber, when the central collecting optical fiber is double-clad, the second detection module does not include a collecting lens. However, this application does not limit this, and it depends on the specific circumstances.

[0069] Optionally, in one embodiment of this application, the imaging light is infrared light or visible light, etc. The infrared light can be an infrared laser, and the second light source module can be an infrared superluminescent diode or a supercontinuum laser, etc. This application does not limit this, and it depends on the specific situation.

[0070] It should be noted that different fluorescent substances have different excitation wavelengths. Each fluorescent substance will only produce a strong fluorescence signal when excited by excitation light of its corresponding wavelength. Therefore, when the second light source module emits infrared laser to obtain the reflection image of the retina, the fluorescence signal generated by the retina under the illumination of the infrared laser will be very weak and will not affect the formation of the reflection image of the retina.

[0071] 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 second detection module detects the feedback beam through two optical paths, wherein the first optical path includes the collecting fiber bundle 1062, and the second optical path includes a wavefront sensor 1064. 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 transmission compensating mirror, a reflection compensating mirror, or other beam control devices. This application does not limit this; the specific choice depends on the circumstances.

[0072] Optional, continue as follows Figure 1As shown, the light source detection module 100 further includes a second beam splitter 109 located on the optical path of the light output from the second light source module 105. In this embodiment, the second beam splitter 109 reflects the light beam transmitted by the first beam splitter 107 to form a scanning beam that is incident on the beam scanning module 200, and reflects and transmits the feedback beam. In this embodiment, the first optical path is the optical path formed by the reflection of the feedback beam by the second beam splitter 109, and the second optical path is the optical path formed by the transmission of the feedback beam by the second beam splitter 109. Specifically, the second beam splitter 109 can be a beam splitter.

[0073] In specific operation, the feedback beam is first transmitted to the second beam splitter 109, where it is reflected and transmitted. The portion reflected by the second beam splitter 109 is transmitted to the first beam splitter 107, and then reflected by the first beam splitter 107 to the collecting fiber bundle 1062 in the first optical path. The collecting fiber bundle 1062 transmits the beam to the second detection component 1063, and then outputs it to the acquisition control module 300. The portion transmitted by the second beam splitter 109 is transmitted to the wavefront sensor 1064 in the second optical path, and then transmitted to the acquisition control module 300 via the wavefront sensor 1064.

[0074] In specific work, continue as follows Figure 1 As shown, the incident light output from the second light source module 105 is incident on the second beam splitter 109, reflected by the second beam splitter 109 to the beam scanning module 200, and modulated by the beam scanning module 200 before entering the eyeball; the reflected beam formed by the retina is transmitted in the beam scanning module 200 in the reverse direction along the transmission direction of the incident light until it exits the beam scanning module 200 and enters the light source detection module 100, where it is reflected and transmitted by the second beam splitter 109; wherein, the portion reflected by the second beam splitter 109 is directed towards the first beam splitter 107, and after passing through the first beam splitter 109... The light beam is reflected into the first optical path and directed towards the collecting lens 1061, the collecting fiber bundle 1062, and the second detection component 1063 to form a retinal image. The portion transmitted by the second beam splitter 109 enters the second optical path and is directed towards the wavefront sensor 1064 to obtain wavefront information in the reflected beam, generate a wavefront dot matrix, and transmit it to the acquisition control module 300. This allows the acquisition control module 300 to control the compensation value of the wavefront modulator 208 to achieve real-time aberration compensation and improve the resolution of the retinal imaging device.

[0075] Specifically, in one embodiment of the application, the wavefront sensor is a Hartmann-Shack wavefront sensor, but this application does not limit it and it depends on the specific circumstances.

[0076] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 As shown, the second light source module 105 includes at least one light source and at least one signal transmission path. The signal transmission path corresponds one-to-one with the light source. That is, the second light source module 105 includes one or more light sources and signal transmission paths corresponding one-to-one with the light sources. The imaging light generated by the light source in the second light source module 105 is incident on the beam scanning module 200 through the signal transmission path.

[0077] It should be noted that if the light source module includes one light source and one signal transmission path, when the retinal imaging device operates in non-confocal imaging mode, the imaging light emitted by the light source in the second light source module is output through its corresponding signal transmission path and incident on the beam scanning module; if the second light source module includes at least two light sources and at least two signal transmission paths, when the retinal imaging device operates in non-confocal imaging mode, the imaging light emitted by one of the light sources in the second light source module is output through its corresponding signal transmission path and incident on the beam scanning module. 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.

[0078] Optionally, in one embodiment of this application, the signal transmission path is an optical fiber. The second light source module includes multiple light sources and multiple transmitting optical fibers, the end faces of which are aligned in a straight line. When the retinal imaging device operates in a second working mode (hereinafter referred to as "confocal imaging mode"), imaging light is generated by the multiple light sources in the second light source module and output through their corresponding signal transmission paths, thereby improving the scanning speed of the retinal imaging device in confocal imaging mode and consequently improving the imaging speed of the retinal imaging device. It should be noted that in this embodiment, the multiple light sources in the second light source module are at least two light sources, and the multiple transmitting optical fibers are at least two transmitting optical fibers. In this case, the collecting fiber bundle 1062 is used to collect the reflected signal from the retina. It should also be noted that in this embodiment, the terms "transmitting fiber" and "collecting fiber" are merely names used to distinguish optical fibers for different purposes; both are optical fibers (optical guide fibers).

[0079] Specifically, in one embodiment of this application, the second light source module 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. Furthermore, while improving the imaging speed of the retinal imaging device, it avoids an excessive number of light sources and transmitting optical fibers in the second light source module, which would result in a large size of the 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 second light source module may also 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 second light source module correspond to the signals from the collecting optical fibers in the collecting optical fiber bundle of the second detection module.

[0080] As can be seen from the above, when the retinal imaging device provided in this application embodiment realizes the two functions of non-confocal imaging mode and confocal imaging mode, it uses most of the optical path. The switching between non-confocal imaging mode and confocal imaging mode can be realized by simply controlling the number of light sources in the light source module 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 that are in working state is larger, and the imaging speed is faster.

[0081] Based on any of the above embodiments, in one embodiment of this application, the beam scanning module includes: a plurality of optical conjugate components, a scanning galvanometer, and a tracking galvanometer. The plurality of optical conjugate components form a plurality of pupil conjugate surfaces, such as N optical conjugate components forming N+1 pupil conjugate surfaces, where N is an integer not less than 1. The eyeball, the scanning galvanometer, the tracking galvanometer, the first light source module, and the second light source module are respectively located on different pupil conjugate surfaces. It should be noted that when the beam scanning module includes a wavefront modulator, the wavefront modulator, the eyeball, the scanning galvanometer, the tracking galvanometer, the first light source module, and the second light source module are respectively located on different pupil conjugate surfaces. The scanning galvanometer is used to scan the scanning beam, and the tracking galvanometer is used to track the scanning beam. It should be noted that in this embodiment, the scanning beam includes: the beam formed after the excitation light enters the beam scanning module, and / or the beam formed after the imaging light enters the beam scanning module.

[0082] The beam scanning module provided in this application embodiment is described below, taking the beam scanning module including a wavefront modulator as an example.

[0083] Specifically, in one embodiment of this application, the optical conjugate component is a mirror assembly, which can be a spherical mirror assembly or a transmission mirror assembly, such as a lens assembly or a parabolic mirror assembly, or other optical elements capable of realizing the above-mentioned optical conjugate relationship; however, this application does not limit this, and it depends on the specific circumstances. The following description uses a mirror assembly as an example to illustrate the retinal imaging device provided in the embodiments of this application.

[0084] Specifically, continue as follows Figure 1 As 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 to compensate for the lateral scanning path to improve the tracking accuracy. In specific operation, the first scanning galvanometer 206 and the second scanning galvanometer 207 are used to form a two-dimensional scan on the retina. 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 movement tracking, so as to adjust the incident direction of the beam in time to track the original scanning position when the human eye moves.

[0085] 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 the beam scanning module does not have a second scanning galvanometer, so that the beam scanning module only performs horizontal scanning. In this case, 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.

[0086] 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.

[0087] It should also be noted that in other embodiments of this application, the scanning galvanometer and the tracking galvanometer may also be the same set of galvanometers, such as the tracking galvanometer and the second scanning galvanometer being integrated into one galvanometer, or the tracking galvanometer and the first scanning galvanometer being integrated into the same galvanometer. This application does not limit this, and it depends on the specific circumstances.

[0088] Optionally, in one embodiment of this application, the acquisition control module 300 includes a computing module, such as a PC (Personal Computer). In specific operation, the acquisition control module 300 collects the optical signals output from the collecting fiber bundle 1062 via the second detection component 1063 and the optical signals output from the first detection module 103, 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, and calculates and processes these optical signals to generate corresponding adaptive optical fundus images. Specifically, the acquisition control module receives scattered light signals from the surrounding 2N optical fibers in the collecting fiber bundle, where each pair of mutually centrosymmetrical fibers forms a group, for a total of N groups. The acquisition control module performs differential subtraction on the signals within each group to obtain a scattered light signal enhanced in a specific direction. The N groups of signals are filtered and superimposed, and then the complete image is calculated and reconstructed based on the galvanometer control signals, thus obtaining an adaptive optics non-confocal scattering image. The acquisition control module receives reflected light signals from the central collecting fiber in the collecting fiber bundle, and then calculates and reconstructs a complete image based on the control signals of the scanning galvanometer and / or tracking galvanometer, thus obtaining an adaptive optics confocal scanning reflection image. The acquisition control module receives fluorescence signals from the first detection component, and then calculates and reconstructs a complete image based on the control signals of the scanning galvanometer and / or tracking galvanometer, thus obtaining an adaptive optics confocal scanning fluorescence image.

[0089] 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 signal output by the second detection component 1063 and / or the optical signal output by the first detection module, so as to realize eye movement tracking.

[0090] 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 among the three transmitting fibers is referred to as the central transmitting fiber. The retinal imaging 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. 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. The data acquisition unit is used to acquire the signal output by the second detection component, and the computing unit is used to process the signal output by the second 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.

[0091] Specifically, in the nonfocal scattering imaging mode, such as Figure 1 As shown, the light emitted from the central light source in the second light source module 105 is transmitted to the second collimating element 108 via the central emitting optical fiber. After being collimated by the second collimating element 108, it forms parallel collimated light that is directed towards the first beam splitter 107. After being transmitted through the first beam splitter 107, it is transmitted to the second beam splitter 109. After being reflected by the second beam splitter 109, 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 109 to the first beam splitter 107. After being reflected by the first beam splitter 107, it is directed towards the collecting lens 1061. The collecting lens 1061 converges the beam onto the collecting fiber bundle 1062, and then the beam is directed towards the second detection component 1063. Finally, the beam is transmitted to the acquisition control module 300 via the second detection component 1063.

[0092] 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 second 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 second detection component through the collecting fiber bundle and output to the acquisition control module through the second detection component. Figure 6As shown, taking N as 4 and the collecting fiber bundle comprising 9 collecting fibers as an example, Figure 6 The positive and negative signs in the text represent 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. Finally, based on the galvanometer control signal, a complete image is calculated and reconstructed, thus obtaining an adaptive non-confocal scattering image. Alternatively, an adaptive confocal scanning reflection image can be obtained from the reflection signal collected by the central collecting fiber.

[0093] In the confocal imaging mode, each light source in the second light source module 105 emits light. The light emitted by each light source in the second light source module 105 is transmitted to the second collimating element 108 through its corresponding transmitting fiber. After being collimated by the second collimating element 108, it forms parallel collimated light that is directed towards the first beam splitter 107. After being transmitted through the first beam splitter 107, it is transmitted to the second beam splitter 109. After being reflected by the second beam splitter 109, it is incident on the beam scanning module 200 and is sequentially modulated by the optical conjugate components, scanning mirror, and tracking mirror in the beam scanning module 200. The light beam enters the pupil and interacts with the fundus (or retina) to form a feedback beam that enters the beam scanning module 200. It is transmitted in the opposite direction to the transmission direction of the imaging light until it exits the beam scanning module 200 and enters the light source detection module 100. It is reflected by the second beam splitter 109 to the first beam splitter 107. After being reflected by the first beam splitter 107, it is directed towards the collecting lens 1061. The collecting lens converges the light onto the collecting fiber bundle 1062, and then the light is transmitted through the collecting fiber bundle 1062 to the second detection component 1063. Finally, the light is transmitted through the second detection component 1063 to the acquisition control module 300.

[0094] Taking the second light source module, which includes three light sources and three transmitting optical fibers, as an example, when the second 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 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 and Figure 8 As shown, Figure 8 Different fillings represent the signal distribution collected by different collecting optical fibers, and also correspond to a part of the scanning area on the retina. After receiving the signal output by the second detection component, the acquisition control module synthesizes the signals corresponding to the feedback signals output by each collecting optical fiber to restore the confocal scanning reflection image, that is, the fundus AOSLO image.

[0095] It should be noted that, in this embodiment, since the feedback signal received by the second detection component 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.

[0096] Therefore, in this application, when the second light source module includes at least two light sources and their corresponding at least two transmitting 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.

[0097] 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 second detection module 106 further includes an insertable beam-shrinking component 1065. In this embodiment, the inserted beam-shrinking component 1065 is located in the first optical path, and the feedback beam enters the collecting fiber bundle 1062 after passing through the beam-shrinking component 1065.

[0098] 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 1065 is disposed in the first optical path, that is, in the optical path between the first beam splitter 107 and the collecting lens 1061, to perform beam-shrinking modulation on the beam emitted from the first beam splitter 107 to the collecting lens 1061. In the non-confocal imaging mode and the multi-point scanning imaging mode, the beam-shrinking component 1065 is not located in the first optical path, that is, not in the optical path between the first beam splitter 107 and the collecting lens 1061, so that the feedback beam reflected by the first beam splitter 107 can directly enter the collecting lens 1061.

[0099] Optionally, in one embodiment of this application, the second 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.

[0100] Optionally, in one embodiment of this application, the beam-shrinking assembly 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-splitting element and the collecting lens, and performs beam-shrinking modulation on the beam emitted by the first beam-splitting element 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-splitting element and the collecting lens, so that the feedback beam reflected by the first beam-splitting element can be directly input into the collecting lens.

[0101] Continue as Figure 10 As shown, in the super-resolution imaging mode, the control module controls the beam-shrinking assembly 1065 to move to the optical path between the first beam splitter 107 and the collecting lens 1061. The central light source in the second light source module 105 emits light, which is transmitted through the central emitting fiber to the second collimating element 108. After being collimated by the second collimating element 108, it forms parallel collimated light that is directed towards the first beam splitter 107. After being transmitted through the first beam splitter 107, it is transmitted to the second beam splitter 109. After being reflected by the second beam splitter 109, it is incident on the beam scanning module 200 and sequentially modulated by the optical conjugate components, scanning mirror, and tracking mirror in the beam scanning module 200. The light enters the pupil and interacts with the fundus to form a feedback beam that is directed towards the input beam scanning module 200. It propagates in the opposite direction to 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 109 to the first beam splitter 107, and then, after being reflected by the first beam splitter 107, is directed towards the beam-shrinking assembly 1065. The beam is then modulated by the beam-shrinking assembly 1065 to form a shrink beam, which then travels to the collecting lens 1061. The collecting lens 1061 converges the beam onto the collecting fiber bundle 1062, which then travels to the second detection assembly 1063. Finally, the beam is transmitted to the acquisition control module 300 via the second detection assembly 1063.

[0102] 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.

[0103] Specifically, the acquisition control module receives reflected light signals collected from 2N+1 collecting optical fibers, and calculates and reconstructs 2N+1 images based on the galvanometer control signal. This includes: using the image generated by the signal received from 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 from 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).

[0104] 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.

[0105] 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.

[0106] It should be noted that when no beam-shrinking component is inserted between the first beam-splitting element and the collecting lens, the adaptive optical confocal scanning reflection imaging and adaptive optical nonfocal scattering imaging of the retinal imaging device can be obtained simultaneously. When the beam-shrinking component is inserted between the first beam-splitting element and the collecting lens, the retinal imaging device can only perform adaptive optical confocal scanning reflection imaging to obtain a resolution-enhanced AOSLO image, but cannot obtain adaptive optical nonfocal scattering imaging.

[0107] It should also be noted that adaptive optics confocal scanning fluorescence imaging can be obtained simultaneously regardless of whether a beam-shrinking component is inserted between the first beam-splitting element and the collecting lens. For example, when no beam-shrinking component is inserted between the first beam-splitting element and the collecting lens, adaptive optics confocal scanning fluorescence imaging and adaptive optics confocal scanning reflection imaging / adaptive optics nonfocal scattering imaging can be obtained simultaneously. When the beam-shrinking component is inserted between the first beam-splitting element and the collecting lens, adaptive optics confocal scanning fluorescence imaging and super-resolution enhanced AOSLO images can be obtained simultaneously.

[0108] In addition, in this embodiment, the wavefront sensor is always in operation regardless of which mode the retinal imaging device is in.

[0109] Optionally, in one embodiment of this application, the first light source module and the second light source module emit light in a time-division manner, so that the retinal imaging device can obtain fluorescence imaging and reflection imaging / scattering imaging of the retina in a time-division manner.

[0110] In another embodiment of this application, the following continues... Figure 1 As shown, the light source detection module 100 further includes a dichroic mirror 110 located on the optical path formed by the collimating element 104 and the collimating beam of the first light source module 101. The dichroic mirror 110 is also located on the reflected optical path formed by the reflection of the beam of the second light source module 105 by the second beam splitter 109. In this embodiment, the first light source module 101 and the second light source module 105 can emit light simultaneously, that is, the retinal imaging device can be used for both fluorescence imaging and reflection imaging simultaneously.

[0111] In this embodiment, continue as follows Figure 1As shown, the excitation light emitted by the first light source module 101 is reflected by the dichroic mirror 110 to the beam scanning module 200. The beam scanning module 200 modulates the light incident on the eyeball, exciting the fluorescent material on the retina to generate a fluorescent signal. This signal then enters the beam scanning module 200 and exits in the opposite direction to the optical path of the excitation light, striking the dichroic mirror 110. It is then reflected by the dichroic mirror 110 to the first optical fiber 102 and received by the first detection module 103. Simultaneously, the light emitted by the second light source module 105 can be reflected by the second beam splitter 109 and then struck by the dichroic mirror 110. After transmission through the dichroic mirror 110, the light enters the beam scanning module 200. The reflected beam output by the beam scanning module 200 can also be transmitted through the dichroic mirror 110 to the second beam splitter 109. After reflection and transmission by the second beam splitter 109, the light is transmitted to the second detection component 1063 and the wavefront sensor 1064. The wavefront sensor 1064 transmits the wavefront information in the reflected beam to the acquisition control module 300, which controls the compensation value of the wavefront modulator 208 and performs real-time aberration compensation on the fluorescence signal and the reflected light signal. After compensation, high-resolution retinal fluorescence image and retinal reflection / scattering image can be obtained respectively.

[0112] It should be noted that a dichroic mirror is an important optical component used in laser technology. It separates light beams according to wavelength, capable of separating light of specific wavelengths. The incident light emitted by the second light source module is of a single wavelength, such as infrared or visible light. Therefore, when the fluorescence signal generated by the excitation light emitted by the first light source module and the reflected signal generated by the incident light emitted by the second light source module travel along the same signal transmission path to the dichroic mirror, the dichroic mirror can separate the reflected signals. This allows the process of forming a reflected image based on the reflected signal and the process of forming a fluorescence image based on the fluorescence signal to occur simultaneously.

[0113] Optionally, in this embodiment, the acquisition control module also obtains the wavefront information of reflected light from the retina fundus through the wavefront sensor, and controls the wavefront modulator in the beam scanning module according to the wavefront information to compensate for the wavefront aberration of the human eye, improve the resolution of the retinal imaging device, and enable both AO fluorescence images and AOSLO images to observe images with the resolution of human eye fundus cell size.

[0114] 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.

[0115] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 As 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.

[0116] 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.

[0117] 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.

[0118] 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.

[0119] Optionally, in one embodiment of this application, the following continues... Figure 1As 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.

[0120] 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.

[0121] 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.

[0122] Optionally, the movable component can be a headrest component, used to place the subject's head. The movement of the movable component moves the subject's head 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.

[0123] 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.

[0124] Alternatively, the moving part 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.

[0125] 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.

[0126] 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.

[0127] Optional, such as Figure 1As 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.

[0128] like Figure 12 As 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 five input terminals and one output terminal. The five input terminals of the data acquisition unit 301 are respectively used for signals output by the first detection module 103, the second detection component 1063, the wavefront sensor 1064, 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.

[0129] 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 first light source module, the second light source module, the fundus illumination source, and the pupil illumination source. The motor controller 306 controls the control modules to control the movement of the beam-constricting assembly. The fixation unit controller 307 controls the operation of the fixation unit.

[0130] 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.

[0131] The fundus reflection signal and / or scattering signal reflected by the second beam splitter collected by the second detection component are sent to the data acquisition unit for acquisition. The calculation unit processes the signals 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, obtaining an adaptive optics confocal reflection image, an adaptive optics nonfocal scattering image, or a super-resolution adaptive optics confocal reflection image. Based on the real-time fundus image, the direction and speed of eye movement are calculated in real time. Eye tracking signals are applied to the galvanometers (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.

[0132] The fluorescence signals emitted from the fundus collected by the first detection component are acquired by the data acquisition unit. The calculation unit then stitches together the position signals of the galvanometers (first scanning galvanometer, second scanning galvanometer, and / or tracking galvanometer) to generate a real-time fundus fluorescence image. Alternatively, multiple fluorescence images can be superimposed to generate a single fluorescence image, resulting in an adaptive optics confocal scanning fluorescence image. It should be noted that eye tracking is performed simultaneously during this process.

[0133] 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.

[0134] 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.

[0135] 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.

[0136] The working process of the retinal imaging device provided in this application embodiment is described below with reference to a specific embodiment.

[0137] In this embodiment, as Figure 13 As shown, the working process of the retinal imaging device includes:

[0138] First, after the subject's head is placed on the headrest, the retinal imaging device automatically aligns with the subject's pupil (corresponding to the pupil camera-3D headrest motor control circuit). Figure 13 The camera is aligned with the subject's pupil until a fundus camera image and a blurred AOSLO image appear; then, the user selects a ROI (Region of Interest) on the fundus camera image (corresponding to...). Figure 13 (Based on the selected ROI in the navigation), the acquisition and control module automatically calculates the corresponding fixed-view coordinates, which are displayed by the fixed-view unit; then the wavefront sensor automatically adjusts the exposure, and the user clicks on adaptive optics correction (corresponding to...). Figure 13 (Click to enable AO in the middle), the wavefront modulator first performs low-order aberration pre-compensation (corresponding to) Figure 13 (The deformable mirror in the middle) then enters the adaptive optics closed-loop control loop and remains there until the shooting ends.

[0139] Once adaptive optics correction is successfully activated, the blurry AOSLO image becomes clear. The retinal imaging device automatically enters a focus search, locates the photoreceptor layer, and automatically adjusts the exposure. Users can observe the real-time process of the AOSLO image becoming clearer and the exposure adjusting. Of course, since the search accuracy is not absolutely perfect, users can manually fine-tune the focus to achieve the optimal image state. Afterward, different modes can be selected based on the fundus structures of interest to the user (receptor cells, blood vessels, RPE, etc.).

[0140] Optionally, the retinal imaging device is selected by default to "AOSLO" mode, in which adaptive optics confocal scanning reflectance imaging (corresponding to...) Figure 13 Reflection imaging in [the context of] and adaptive optics nonfocal scattering imaging (corresponding to [other methods]) Figure 13 Scattering imaging is enabled by default (users can also manually enable adaptive optics confocal scanning fluorescence imaging). Figure 13 (In the fluorescence imaging mode), at which point all three imaging modalities are working simultaneously, clicking "Start Shooting" immediately activates the real-time tracking function of the AOSLO image, and then immediately begins recording a short video segment. The computational unit then performs post-processing, registering and overlaying the recorded video to generate an AOSLO image of the fundus and a fundus scattering image (if fluorescence imaging is enabled, an AO fluorescence image will also be generated). Figure 13 (Generate images / videos in the corresponding mode).

[0141] If the user selects the "High-speed AOSLO Imaging" mode (corresponding to...) Figure 13In high-speed imaging (e.g., during retinal imaging), the light source controller in the acquisition control module of the retinal imaging device will activate the multi-point light source in the second light source module. At this time, the computational unit of the adaptive optics non-confocal scattering mode will automatically shut down (adaptive optics confocal scanning fluorescence imaging can still work, or can be manually turned off). Click "Start Shooting," and the real-time tracking function of the AOSLO image will immediately start, followed by video recording. After recording ends, the computational unit performs post-processing, registering and overlaying the recorded video to generate an AOSLO preview image and a high-frame-rate AOSLO video stream (corresponding to...). Figure 13 (Generate images / videos in the corresponding mode).

[0142] If the user selects the "Super-resolution Imaging" mode (corresponding to...) Figure 13 In super-resolution imaging (UOSLO), the control module of the retinal imaging device will control the motor to insert a beam-shrinking component in the optical path. At this time, the computing unit of the adaptive optics non-confocal scattering mode will automatically shut down (adaptive optics confocal scanning fluorescence imaging can still work, or can be manually turned off). Click "Start Shooting," and the real-time tracking function of the AOSLO image will be immediately activated. Then, a short video recording will begin immediately, and the computing unit will perform post-processing, image registration and overlay on the recorded video to generate a resolution-enhanced AOSLO image (corresponding to...). Figure 13 (Generate images / videos in the corresponding mode).

[0143] After the data collection is complete, users can click to enter the analysis interface to view all the images or videos just acquired (corresponding to...). Figure 13 (Click to enter analysis), and can control the computing unit in the acquisition control module to automatically segment cell images, output a series of quantitative parameters such as cell density and regularity, or perform corresponding parameter analysis on blood vessel and blood flow images, such as thickness and flow velocity, and generate corresponding analysis reports (corresponding to...). Figure 13 The calculation generates quantization parameters.

[0144] In summary, the retinal imaging device provided in this application embodiment can realize adaptive optics confocal scanning reflectance imaging, adaptive optics nonfocal scattering imaging, and adaptive optics confocal scanning fluorescence imaging, expanding the imaging modalities of the retinal imaging device. Adaptive optics confocal scanning reflectance imaging provides good imaging contrast for highly reflective structures on the retina, such as photoreceptor cells and nerve fibers, and can be used for functions such as photoreceptor cell counting and morphological analysis. Adaptive optics nonfocal scattering imaging has higher contrast in measuring blood vessel walls and observing red blood cells and photoreceptor intracellular segments, and can be used for functions such as measuring blood vessel wall thickness, microvascular flow velocity, and red blood cell measurement. Adaptive optics confocal scanning fluorescence imaging can image blood flow and target fluorescent substances in the RPE, and can be used for RPE cell counting and morphological analysis, retinal pigment distribution analysis, etc., thereby enhancing the diagnostic capabilities of the retinal imaging device for different retinal disease manifestations, making the retinal imaging device provided in this application embodiment advantageous in various application scenarios.

[0145] In addition, the retinal imaging device provided in this application embodiment shares most of the optical path in hardware when realizing adaptive optical confocal scanning reflection imaging, adaptive optical nonfocal scattering imaging and adaptive optical confocal scanning fluorescence imaging. The three imaging modes can be simultaneously or separately imaged by only the adjustment of the acquisition control module.

[0146] 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.

[0147] It should be noted that, in the description of this application, the accompanying drawings and embodiments are illustrative rather than restrictive. It should also be noted that, 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 limitations, 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.

[0148] 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, characterized in that, include: The system includes a light source detection module and a beam scanning module. The light source detection module comprises a first light source module, a first detection module, a second light source module, and a second detection module. The excitation light generated by the first light source module is incident on the beam scanning module, and after being modulated by the beam scanning module, it enters the eyeball, exciting the fluorescence beam formed by the retina and then being incident on the first detection module via the beam scanning module for fluorescence imaging. The imaging light generated by the second light source module is incident on the beam scanning module. The beam beam modulated by the beam scanning module enters the eyeball. The feedback beam formed by the retina is incident on the second detection module through the beam scanning module. The second detection module includes a collection fiber bundle, which includes multiple collection fibers. The multiple collection fibers are used to collect the reflected signal from the retina, or a portion of the collection fibers are used to collect the reflected signal from the retina, and another portion of the collection fibers are used to collect the scattered signal from the retina.

2. The retinal imaging device according to claim 1, characterized in that, The collecting fiber bundle 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 2N+1 collecting fibers are used to collect the reflected signal from the retina, or the central collecting fiber is used to collect the reflected signal from the retina, and the 2N collecting fibers are used to collect the scattered signal from the retina.

3. The retinal imaging device according to claim 2, characterized in that, The 2N collecting optical fibers are symmetrically distributed with one collecting optical fiber as the center.

4. The retinal imaging device according to claim 2, characterized in that, The central collecting fiber is a double-clad fiber, which includes a core, a first cladding, and a second cladding. The core of the double-clad fiber is used to transmit the imaging light emitted by the second light source module, and the first cladding of the double-clad fiber is used to transmit the reflected signal from the retina. The reflected signal is transmitted to the second detection module via a coupling fiber for reflection imaging.

5. The retinal imaging device according to claim 1, characterized in that, The light source detection module further includes a first optical fiber, which includes a first double-clad optical fiber and a first coupling optical fiber; The excitation light generated by the first light source module is transmitted through the core of the first double-clad optical fiber and incident on the beam scanning module. After being modulated by the beam scanning module, it enters the eyeball and excites the retina to form a fluorescent beam, which is then transmitted through the beam scanning module to the first double-clad optical fiber. The beam is then transmitted through the first cladding of the first double-clad optical fiber and the first coupling optical fiber to the first detection module for fluorescence imaging.

6. The retinal imaging device according to claim 1, characterized in that, The beam scanning module includes: multiple optical conjugate components, a scanning galvanometer, and a tracking galvanometer. The multiple optical conjugate components form multiple pupil conjugate surfaces. The eyeball, the scanning galvanometer, the tracking galvanometer, the first light source module, and the second light source module are respectively located on different pupil conjugate surfaces.

7. The retinal imaging device according to claim 6, characterized in that, The beam scanning module further includes a wavefront modulator; the second 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.

8. The retinal imaging device according to claim 1, characterized in that, The second detection module further includes an insertable beam-shrinking assembly, through which the feedback beam enters the collecting fiber bundle, the collecting fiber bundle being used to collect reflected signals from the retina.

9. The retinal imaging device according to any one of claims 1 to 8, characterized in that, The second 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.

10. The retinal imaging device according to claim 9, characterized in that, The signal transmission path is an optical fiber. The second light source module includes multiple light sources and multiple transmitting optical fibers, the end faces of which are located in a straight line. The collecting optical fiber bundle is used to collect reflected signals from the retina.

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