Retina fluorescence imaging device

Abstract

The utility model discloses a retina fluorescence imaging device, and relates to the technical field of imaging. The retina fluorescence imaging device comprises 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 and a first optical fiber, and the first optical fiber comprises a first double-clad optical fiber and a first coupling optical fiber; excitation light generated by the first light source module is transmitted through a fiber core of the first double-clad optical fiber, enters the light beam scanning module, enters an eyeball after being modulated by the light beam scanning module, and excites a fluorescent light beam formed by a retina to enter the light source detection module through the light beam scanning module. And the optical signal is transmitted to the first detection module through the first cladding of the first double-cladding optical fiber and the first coupling optical fiber and is used for fluorescence imaging, so that the aim of optimizing the retina fluorescence imaging device is fulfilled.

Description

Technical Field

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

[0002] The retina is a vital component of the eye, and retinal diseases are becoming increasingly prevalent worldwide. To achieve more effective diagnosis and treatment of retinal diseases, the optimization of retinal imaging devices is essential; in other words, the optimization of retinal imaging devices is of great significance for the diagnosis and treatment evaluation of retinal diseases. Therefore, the optimization of retinal imaging devices has become a research hotspot in the field.

[0003] Like traditional confocal microscopes, fluorescence confocal imaging systems require a small detection device (such as a confocal aperture) that achieves optical conjugation with the light source and sample. This means the relative positions of the confocal aperture, the light source, and the sample must remain unchanged. Such devices often require extremely high adjustment precision and mechanical stability. Furthermore, existing fluorescence confocal imaging systems typically use dichroic mirrors or beam splitters to separate fluorescence and excitation light when achieving multi-wavelength broadband fluorescence imaging. Both approaches present their own technical challenges. With dichroic mirrors, the fluorescence spectrum is limited by their optical properties, requiring the selection of specific spectral combinations based on the mirror's transmission and reflection curves. Conversely, using beam splitters and filters instead of dichroic mirrors sacrifices fluorescence illumination and collection efficiency, significantly hindering weak-light signal imaging techniques like retinal fluorescence imaging. Utility Model Content

[0004] In view of the above problems, this application provides a retinal fluorescence imaging device to optimize the retinal fluorescence imaging device. The specific solution is as follows:

[0005] A retinal fluorescence imaging device includes: a light source detection module and a beam scanning module. The light source detection module includes a first light source module, a first detection module, and a first optical fiber. The first optical fiber includes a first double-clad optical fiber and a first coupling optical fiber.

[0006] 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 fluorescence beam formed by the retina. The excitation beam is then incident on the light source detection module through the beam scanning module and transmitted to the first detection module through the first cladding of the first double-clad optical fiber and the first coupling optical fiber for fluorescence imaging.

[0007] Optionally, the beam scanning module includes: multiple optical conjugate components and a scanning galvanometer, wherein the multiple optical conjugate components form multiple pupil conjugate surfaces, and the eyeball, the scanning galvanometer, and the first light source module are respectively located on different pupil conjugate surfaces.

[0008] Optionally, the beam scanning module further includes a beam phase modulation element located on different conjugate surfaces of the eyeball pupil; the light source detection module further includes a wavefront sensor.

[0009] Optionally, the beam scanning module further includes a tracking galvanometer located on different pupil conjugate surfaces of the eyeball.

[0010] Optionally, it may also include: an acquisition control module, at least for generating a fluorescence image based on the detection signal of the first detection module.

[0011] Optionally, the light source detection module further includes a second light source module and a second detection module, wherein,

[0012] The 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. The reflected beam formed by the retina is incident on the second detection module through the beam scanning module for reflection imaging.

[0013] Optionally, the light source detection module further includes: a first beam splitter located in the output light path of the second light source module;

[0014] The second detection module includes: a collecting lens, a confocal aperture, and a second detection component located on the optical path formed by the reflection of the reflected beam by the first beam splitter.

[0015] Optionally, the light source detection module further includes: a second beam splitter located on the transmission optical path of the first beam splitter, the second beam splitter being used to reflect the light generated by the second light source module to the beam scanning module;

[0016] The light source detection module also includes:

[0017] The first collimating element is located in the beam path of the first light source module;

[0018] A dichroic mirror is located on the optical path formed by the collimation of the beam from the first light source module by the first collimating element, and the dichroic mirror is also located on the reflected optical path formed by the reflection of the beam from the second light source module by the second beam splitting element.

[0019] Optionally, the light source detection module further includes a second optical fiber, which comprises a second double-clad optical fiber and a second coupling optical fiber; wherein,

[0020] The light generated by the second light source module is transmitted through the core of the second double-clad optical fiber and enters the beam scanning module. After being modulated by the beam scanning module, it enters the eyeball. The reflected beam formed by the retina is transmitted through the beam scanning module to the light source detection module, and then transmitted through the second cladding of the second double-clad optical fiber and the second coupling optical fiber to the second detection module for reflection imaging.

[0021] Optionally, the light source detection module further includes: a second beam splitter located on the light path output by the second light source module, used to reflect the light generated by the second light source module to the beam scanning module;

[0022] The light source detection module also includes:

[0023] The first collimating element is located in the beam path of the first light source module;

[0024] A dichroic mirror is located on the optical path formed by the collimation of the beam from the first light source module by the first collimating element, and the dichroic mirror is also located on the reflected optical path formed by the reflection of the beam from the second light source module by the second beam splitting element.

[0025] This solution has the following advantages:

[0026] In the retinal fluorescence imaging device provided in this application embodiment, 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 the fluorescence beam formed by exciting the retina is incident on the light source detection module through the beam scanning module. It is then transmitted to the first detection module through the first cladding of the first double-clad optical fiber and the first coupling optical fiber for fluorescence imaging. This device can provide good imaging contrast for different structures on the retina (such as cells in the retinal pigment epithelium) and reflect their intrinsic physiological and chemical information.

[0027] Moreover, the retinal fluorescence imaging device provided in this application embodiment utilizes a first optical fiber to transmit excitation light and fluorescence, which can not only significantly reduce light waste and improve light utilization, but also ensure that the light emission point of the light source and the fluorescence collection aperture (first cladding) are always in the same relative position in structure, forming a self-confocal structure. That is, the light emission point and the collection aperture are always kept in an optically conjugate position, avoiding the positional change of one of the collection aperture and the light emission point of the light source relative to the other due to vibration, collision, thermal expansion and contraction of the retinal fluorescence imaging device. This greatly reduces the requirements of the fluorescence confocal imaging device on adjustment accuracy and stability during use.

[0028] Furthermore, the retinal fluorescence 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. Attached Figure Description

[0029] 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.

[0030] Figure 1 This is a schematic diagram of the structure of a retinal fluorescence imaging device provided in this application;

[0031] Figure 2 A schematic diagram of the structure of the first optical fiber in a retinal fluorescence imaging device provided in this application;

[0032] Figure 3 A cross-sectional view of the first double-clad optical fiber in a structural schematic diagram of a retinal fluorescence imaging device provided in this application;

[0033] Figure 4 A schematic diagram of a partial structure of a retinal fluorescence imaging device provided in this application, in which the first optical fiber is replaced by a dichroic mirror;

[0034] Figure 5 A partial structural diagram of a retinal fluorescence imaging device provided in this application, in which the first optical fiber is replaced by a beam splitter;

[0035] Figure 6 This is a schematic diagram of another retinal fluorescence imaging device provided in this application. Detailed Implementation

[0036] 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.

[0037] 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 embodiments provided in this application can be combined with each other without contradiction.

[0038] 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.

[0039] As described in the background section, the optimization of retinal fluorescence imaging devices has become a research hotspot for those skilled in the art.

[0040] In view of this, embodiments of this application provide a retinal fluorescence imaging device, such as... Figure 1 As shown, it includes:

[0041] A light source detection module 100 and a beam scanning module 200, wherein the light source detection module 100 includes a first light source module 101, a first detection module 103, and a first optical fiber 102, as shown below. Figure 2 As shown, the first optical fiber 102 includes a first double-clad optical fiber 1021 and a first coupling optical fiber 1022; wherein,

[0042] 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 then incident on the light source detection module 100 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.

[0043] Optionally, the first coupling fiber 1022 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.

[0044] In the retinal fluorescence imaging device provided in this application embodiment, 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 the fluorescence beam formed by exciting the retina is incident on the light source detection module through the beam scanning module. It is then transmitted to the first detection module through the first cladding of the first double-clad optical fiber and the first coupling optical fiber for fluorescence imaging. This device can provide good imaging contrast for different structures on the retina (such as cells in the retinal pigment epithelium) and reflect their intrinsic physiological and chemical information.

[0045] Furthermore, in the retinal fluorescence imaging device provided in this application embodiment, the transmission of excitation light emitted by the first light source module and the transmission of the fluorescence beam formed by exciting the retina are realized using a first optical fiber. The first optical fiber 102 includes a first double-clad optical fiber 1021 and a first coupling optical fiber 1022, such as... Figure 2 and Figure 3 As shown, 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 meets the requirements of a confocal aperture and can 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 fluorescence 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 structure is maintained, and the light emission point of the light source and the confocal aperture always maintain a constant relative position. This avoids 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 fluorescence imaging device, greatly reducing the requirements for adjustment accuracy and stability of the fluorescence confocal imaging device during use. It should be noted that in this embodiment, the function of the second cladding layer C is to provide a refractive index difference, that is, to form a refractive index difference with the first cladding layer B, allowing the fluorescence signal to be transmitted in the first cladding layer B through total internal reflection. This prevents the light transmitted within the first cladding layer B from escaping through the second cladding layer C, improving the collection efficiency of the fluorescence signal.

[0046] 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 1 As 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.

[0047] 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.

[0048] 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.

[0049] 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'.

[0050] like Figure 4 As shown, a dichroic mirror can be replaced Figure 1The first optical fiber 102 in the retina transmits the light emitted by the first light source module 101, which excites the fluorescent material on the retina to generate a fluorescent signal. However, since a dichroic mirror is an optical element that can selectively reflect or transmit light according to the wavelength of light, replacing the first optical fiber 102 with a dichroic mirror can only be applied to the reflection or transmission of light of a few wavelengths, so that the retinal fluorescence imaging device can only realize the imaging of fluorescent signals of certain specific wavelengths.

[0051] In this embodiment, the retinal fluorescence imaging device transmits excitation light through the core of the first double-clad optical fiber 1021 and fluorescence through the first cladding of the first double-clad optical fiber 1021. 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, and no additional structure is needed to separate the excitation light and fluorescence. Therefore, the retinal fluorescence imaging device provided in this application embodiment can image fluorescent substances with different fluorescence spectra by simply changing the wavelength of the light source generated by the first light source module 101 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.

[0052] like Figure 5 As shown, the beam splitter can also be replaced. Figure 1 The first optical fiber 102 in the middle realizes the transmission of light emitted by the first light source module 101 to excite the fluorescent material on the retina to generate a fluorescent signal. However, the beam splitter can not only reflect light but also transmit light. As a result, when the light emitted by the excitation light source is transmitted to the beam scanning module through the beam splitter, some of the reflected light will be wasted. When the beam formed after exciting the retina is reflected to the detector direction by the beam splitter on the return path, some of the transmitted light will be wasted.

[0053] The retinal fluorescence imaging device provided in this application transmits excitation light through the core of the first double-clad optical fiber 1021 and transmits fluorescence through the first cladding of the first double-clad optical fiber 1021. That is, different signal transmission channels are used to transmit excitation light and fluorescence respectively, so that the excitation light emitted by the first light source module 101 can be transmitted entirely to the beam scanning module through the core of the first double-clad optical fiber 1021 to excite the fluorescent material on the retina, thereby improving the utilization rate of the light emitted by the first light source module 101. At the same time, since the core diameter of the first double-clad optical fiber 1021 is very small, most of the fluorescence signal generated by exciting the fluorescent material on the retina will enter the first detection module 103 through the first cladding for fluorescence imaging, thereby improving the light utilization rate of the fluorescence formed by the excitation light illuminating the retina.

[0054] Therefore, the retinal fluorescence imaging device provided in this application embodiment utilizes the first optical fiber 102 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.

[0055] 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 100 further includes a second light source module 105 and a second detection module 106. The light generated by the second light source module 105 is incident on 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 incident on the second detection module 106 through the beam scanning module 200 for reflection imaging. This allows the retinal fluorescence imaging device provided in this embodiment to provide not only fluorescence imaging of the retina but also reflection imaging of the retina.

[0056] 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 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 confocal aperture 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 then propagates 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, passes through the confocal aperture 1062, and is received by the second detection component 1063 to form a reflected image of the retina.

[0057] Optionally, based on the above embodiments, in one embodiment of this application, the following continues... Figure 1As shown, the light source detection module 100 further includes a 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 light emitted by the second light source module 105 is infrared light or visible light, etc., and the second collimating element is a collimating lens, such as an achromatic lens, a self-focusing lens, or an off-axis parabolic mirror, etc. The first beam splitter can be a beam splitter, but this application does not limit this; the specific choice depends on the circumstances.

[0058] In another embodiment of this application, such as Figure 6 As shown, the light source detection module 100 further includes a second optical fiber 112, which comprises a second double-clad optical fiber and a second coupling optical fiber. The incident light generated by the second light source module 105 is transmitted through the core of the second double-clad optical fiber in the second optical fiber 112, and then enters the beam scanning module 200. After being modulated by the beam scanning module 200, the light enters the eyeball. The reflected beam formed by the retina is transmitted through the beam scanning module 200 to the light source detection module 100, and then transmitted through the first cladding of the second double-clad optical fiber and the second coupling optical fiber in the second optical fiber 112 to the second detection module 106 for reflection imaging. In this embodiment, the second detection module includes a second detection component, but does not include a collecting lens and a confocal aperture.

[0059] In the retinal fluorescence imaging device provided in this application embodiment, the incident light generated by the second light source module is transmitted through the core of the second double-clad fiber in the second optical fiber and incident on the beam scanning module. After being modulated by the beam scanning module, it enters the eyeball. The reflected beam formed by the reflection of the retina is incident on the light source detection module through the beam scanning module and transmitted to the second detection module through the first cladding of the second double-clad fiber and the second coupling fiber in the second optical fiber for reflection imaging, so as to achieve the effect of observing retinal photoreceptor cells and microvessels and provide high image contrast.

[0060] Furthermore, in the retinal fluorescence imaging device provided in this application embodiment, a second optical fiber is used to transmit the incident light emitted by the second light source module and the reflected beam formed by the incident light after reflection by the retina. The second optical fiber includes a second double-clad optical fiber and a second coupling optical fiber. The second double-clad optical fiber includes a core, a first cladding, and a second cladding (structured the same as the first double-clad optical fiber 1021). The core is located in the central region of the first cladding, and the second cladding wraps around the outer surface of the first cladding. The core of the second double-clad optical fiber is used to transmit the incident light emitted by the second light source module, and the first cladding of the second double-clad optical fiber... The reflected beam formed by the reflection of the input light by the retina is used to transmit the input light. The core end face of the second double-clad fiber and the end face of the first cladding layer respectively serve as the light emission point and the confocal aperture for signal collection in the second light source module. This satisfies optical conjugate positions, forming self-confocal focusing. Furthermore, the light emission point and the confocal aperture maintain a constant relative position structurally, preventing positional changes between the collection aperture and the light emission point of the light source due to vibrations, collisions, thermal expansion and contraction of the retinal fluorescence imaging device. This significantly reduces the requirements for adjustment accuracy and stability of the retinal fluorescence imaging device during use. It should be noted that in this embodiment, the second cladding layer of the second double-clad fiber provides a refractive index difference, forming a refractive index difference with the first cladding layer. This allows the reflected signal to be transmitted through total internal reflection within the first cladding layer, preventing light transmitted within the first cladding layer from exiting the second cladding layer and improving the collection efficiency of the reflected signal.

[0061] It should be noted that, since the core and first cladding of the second double-clad fiber in the second optical fiber are relatively small on the end face of the second optical fiber, in one embodiment of this application, based on the above embodiments, the following continues... Figure 6 As shown, the light source detection module 100 further includes a third collimating element 113, which is located on the transmission optical path of the incident light output from the second optical fiber 112. In this embodiment, the third collimating element 113 is used to collimate the incident light output from the second optical fiber 112 before it enters the beam scanning module 200, so that when the incident light exits from the beam scanning module 200 and enters the eye, it can cover the area to be imaged. Similarly, the third collimating element 113 is also used to converge the reflected beam output from the beam scanning module 200 before it enters the second optical fiber 112, so that the reflected beam output from the beam scanning module 200 can enter the first cladding of the second double-clad optical fiber with a smaller diameter, and be collected by the second detection module 106 after transmission through the first cladding of the second double-clad optical fiber.

[0062] Optionally, in one embodiment of this application, the third 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.

[0063] It should be noted that, in Figure 1 In the retinal fluorescence imaging device shown, when the incident light emitted from the second light source module 105 is transmitted to the surface of the first beam splitter 107, in addition to transmission, there will also be some reflected light. Similarly, when the reflected light beam formed by retinal reflection is transmitted to the surface of the first beam splitter 107, in addition to being reflected to the second detection module 106, there will also be some transmitted light, resulting in some light wastage. Figure 6 In the retinal fluorescence imaging device shown, the incident light is transmitted through the core of the second double-clad fiber in the second optical fiber 112, and the reflected light is transmitted through the first cladding of the second double-clad fiber in the second optical fiber 112. That is, different signal transmission channels are used to transmit the incident light and the reflected light respectively, so that the incident light emitted by the second light source module 105 can be transmitted to the beam scanning module 200 through the core of the second double-clad fiber and enter the eyeball, which improves the utilization rate of the light emitted by the second light source module 105. At the same time, since the core diameter of the second double-clad fiber is very small, most of the reflected signal formed by the reflection of the retina will enter the second detection module 106 through the first cladding of the second double-clad fiber for reflection imaging, which improves the utilization rate of the reflected light formed by the incident light hitting the retina.

[0064] Therefore, the retinal fluorescence imaging device provided in this application embodiment utilizes a second optical fiber to transmit incident and reflected light, which can significantly reduce light waste and improve light utilization.

[0065] Optionally, in one embodiment of this application, the incident light is infrared light, which can be an infrared laser. 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.

[0066] 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.

[0067] As can be seen from the above, the retinal fluorescence imaging device provided in this application embodiment can be used for fluorescence imaging and also for reflection imaging.

[0068] Based on any of the above embodiments, in one embodiment of this application, such as Figure 1 and Figure 6 As shown, the retinal fluorescence imaging device further includes an acquisition control module 300, which is connected to the light source detection module 100 and the beam scanning module 200. In this embodiment, the acquisition control module 300 is at least used to acquire the signal detected by the first detection module 103, and based on the optical path state of the beam scanning module 200, to stitch the signals detected by the first detection module 103 to generate a fluorescence image; if the light source detection module 100 further includes a second light source module 105 and a second detection module 106, the acquisition control module 300 is also used to acquire the signal detected by the second detection module 106, and based on the optical path state of the beam scanning module 200, to stitch the signals detected by the second detection module 106 to generate an SLO image. The SLO image is a retinal image obtained through scanning laser ophthalmoscopy (SLO).

[0069] Optionally, in one embodiment of this application, the acquisition control module can also be used to superimpose multiple SLO images or fluorescence images to improve the signal-to-noise ratio.

[0070] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 and Figure 6 As 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, and a wavefront sensor 110 located on the optical path formed by the transmission of the reflected light beam by the second beam splitter 109. Specifically, the second beam splitter 109 can be a beam splitter.

[0071] Based on the above embodiments, in one embodiment of this application, the beam scanning module 200 includes a beam phase modulation element 208, which is used to modulate the wavefront phase of the excitation light and / or incident light incident on the beam scanning module 200 to compensate for eye aberrations, so as to combine adaptive optics (AO) technology with fluorescence confocal imaging and / or reflection confocal imaging to improve the resolution of retinal imaging.

[0072] It should be noted that the retinal fluorescence imaging device provided in this application combines adaptive optics technology and fluorescence confocal imaging and / or reflection confocal imaging. It can not only image highly reflective structures such as photoreceptor cell layers, but also improve the imaging contrast of structures with fluorescent substances in the retina, obtaining ultra-high-definition fundus fluorescence images with resolution down to the cellular level. This provides a means to finely observe specific physiological information of the human retina, which helps to screen fundus physiological lesions early and quickly.

[0073] 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 beam phase modulation device 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 fluorescence imaging device, so that both AO fluorescence images and AOSLO images can observe images with the resolution of human eye fundus cell size.

[0074] In specific work, continue as follows Figure 1 and Figure 6 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 enters the second detection module 100. 6. The light beam is transmitted to the acquisition control module 300 via the second detection module 106 to form a retinal image with super-resolution and high signal-to-noise ratio; the portion transmitted by the second beam splitter 109 is directed toward the wavefront sensor 110 to obtain wavefront information in the reflected beam through the wavefront sensor 110, generate a wavefront dot matrix, and transmit it to the acquisition control module 300, so that the acquisition control module 300 can control the compensation value of the beam phase modulation element 208 to achieve real-time aberration compensation and improve the resolution of the retinal fluorescence imaging device.

[0075] Specifically, in one embodiment of the application, the wavefront sensor is a Hartmann-Shack wavefront sensor, and the beam phase modulation element is a deformable mirror, a spatial light modulator, a transmissive compensating mirror, a reflective compensating mirror, or other devices, but this application does not limit it and it depends on the specific circumstances.

[0076] 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 fluorescence imaging device can obtain fluorescence imaging and reflection imaging of the retina in a time-division manner.

[0077] In another embodiment of this application, the following continues... Figure 1 and Figure 6 As shown, the light source detection module 100 further includes a dichroic mirror 111 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 111 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 fluorescence imaging device can be used for both fluorescence imaging and reflection imaging simultaneously.

[0078] In this embodiment, continue as follows Figure 1 and Figure 6 As shown, the excitation light emitted by the first light source module 101 is reflected by the dichroic mirror 111 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 111. It is then reflected by the dichroic mirror 111 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 111. After transmission through the dichroic mirror 111, it enters the beam scanning module 200. The reflected beam output by the beam scanning module 200 can also be transmitted through the dichroic mirror 111 to the second beam splitter 109. After reflection and transmission by the second beam splitter 109, the light is transmitted to the second detection module 106 and the wavefront sensor 110. The wavefront sensor 110 transmits the wavefront information in the reflected beam to the acquisition control module 300, which controls the compensation value of the beam phase modulation element 208 and performs real-time aberration compensation on the fluorescence signal and the reflected light signal. After compensation, high-resolution retinal fluorescence images and retinal reflection images can be obtained respectively.

[0079] 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.

[0080] Based on any of the above embodiments, in one embodiment of this application, the beam scanning module includes: a plurality of optical conjugate components and a scanning 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, and the light source modules (such as the first light source module and the second light source module) in the light source detection module are respectively located on different pupil conjugate surfaces. It should be noted that when the beam scanning module includes a beam phase modulation element, the beam phase modulation element, the eyeball, the scanning galvanometer, and the light source modules in the light source detection module are respectively located on different pupil conjugate surfaces.

[0081] The beam scanning module provided in this application embodiment is described below, taking the beam scanning module including a beam phase modulation element as an example.

[0082] 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, but this application does not limit it and it depends on the specific situation. The following description uses a mirror assembly as an example to illustrate the retinal fluorescence imaging device provided in this application embodiment.

[0083] Based on the above embodiments, in one embodiment of this application, the beam scanning module further includes a tracking galvanometer, wherein the tracking galvanometer, the scanning galvanometer, the beam phase modulation element, the eyeball, and the light source module in the light source detection module are respectively located on different conjugate surfaces of the pupil of the eyeball. 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 incident light enters the beam scanning module.

[0084] Specifically, continue as follows Figure 1 and Figure 6As shown, in one embodiment of this application, the beam scanning module 200 includes a first optical conjugate component 201, a second optical conjugate component 202, a third optical conjugate component 203, a fourth optical conjugate component 204, and a fifth optical conjugate component 205; wherein, a first scanning galvanometer 206 is placed on the pupil conjugate surface between the first optical conjugate component 201 and the second optical conjugate component 202, a second scanning galvanometer 207 is placed on the pupil conjugate surface between the second optical conjugate component 202 and the third optical conjugate component 203, and a tracking galvanometer 209 is placed on the pupil conjugate surface between the fourth optical conjugate component 204 and the fifth optical conjugate component 205. It should be noted that in this embodiment, the first scanning galvanometer 206 is used to perform lateral scanning, i.e., scanning in the horizontal direction, and the second scanning galvanometer 207 is used to perform longitudinal scanning, i.e., scanning in the vertical direction. The tracking galvanometer 209 is used to track the eye when the position of the eyeball changes and compensate for the lateral scanning path to improve tracking accuracy. In specific operation, the first scanning galvanometer 206 and the second scanning galvanometer 207 are used to form a two-dimensional scan on the retina, and the signals of each scanned point are stitched together to form part of the image; the horizontal tracking signal acts on the tracking galvanometer 209, and the vertical tracking signal is superimposed on the vertical scanning signal and acts on the second scanning galvanometer 207, simultaneously realizing fundus scanning and eye tracking.

[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 galvanometer, the second scanning galvanometer, the tracking galvanometer, and the beam phase modulation element can be interchanged, as long as the first scanning galvanometer, the second scanning galvanometer, the tracking galvanometer, and the beam phase modulation element are located on different conjugate surfaces of the pupil.

[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 the above embodiments, the acquisition control module is also used to monitor and calculate the movement of the acquisition area caused by eye movement in real time, and control the tracking galvanometer according to the calculation results so that the tracking galvanometer compensates for the displacement in real time.

[0089] Based on any of the above embodiments, in one embodiment of this application, the following continues... Figure 1 and Figure 6 As shown, the retinal fluorescence imaging device further includes a fundus imaging module 400 for acquiring fundus images. Specifically, in one embodiment of this application, the fundus imaging module 400 includes a fundus illumination source (not shown in the figure) and a fundus navigation detector 403. The fundus illumination source generates illumination light to illuminate the fundus, which is then reflected by the fundus and acquired by the fundus navigation detector to generate fundus images in real time. It should be noted that in this embodiment, the fundus navigation detector is used to collect the returned fundus signals to generate fundus images. This allows the operator to confirm the relative position of the small area acquired by the SLO (or AOSLO) image and the fluorescence image (or AO fluorescence image) on the fundus by observing the fundus image, thus playing a navigation role on the retina. The fundus navigation detector 403 can be a fundus camera or a confocal aperture, etc., and this application does not limit it; the specific choice depends on the situation.

[0090] 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 fluorescence imaging device is simple to operate and highly efficient in clinical practice.

[0091] Optionally, in one embodiment of this application, the following continues... Figure 1 and Figure 6 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.

[0092] 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.

[0093] Optionally, in one embodiment of this application, the following continues... Figure 1 and Figure 6 As shown, the fundus imaging module 400 also includes a pupil illumination source 404 and a pupil camera 405. The pupil illumination source 404 generates pupil illumination light to illuminate the eyeball, and the pupil camera 405 acquires pupil images.

[0094] 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.

[0095] Based on any of the above embodiments, in one embodiment of this application, the retinal fluorescence imaging device may further include a movable component for adjusting the relative position of the optical axis of the retinal fluorescence imaging device and the pupil, so that the optical axis of the retinal fluorescence imaging device is aligned with the pupil.

[0096] Optionally, the moving component can be a headrest component for placing the subject's head. 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, thereby aligning the optical axis of the retinal fluorescence imaging device with the pupil.

[0097] It is understood that, in this embodiment, the fundus illumination source, fundus navigation detector, and fixation unit in the fundus imaging module, combined with the beam scanning module, enable the imaging light to rapidly 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 in the fundus imaging module enable alignment of the optical axis of the retinal fluorescence imaging device with the pupil, ensuring efficient and accurate scanning of the subject's eyeball and improving clinical efficiency.

[0098] Optional, continue as follows Figure 1 and Figure 6As 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 scanning light beam emitted by the beam scanning module 200 enters the eyeball. The light beam reflected from the fundus is also collected by the fundus navigation detector 403, the pupil camera 405, and the beam scanning module 200. In this embodiment, the fundus illumination source is located near the fundus navigation detector 403, so that the signal emitted by the fundus illumination source and the signal received by the fundus navigation detector 403 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 navigation detector 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.

[0099] 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.

[0100] It should be noted that, in the description of this application, the accompanying drawings and embodiments are illustrative rather than restrictive. The same reference numerals throughout the embodiments identify the same structures. Additionally, for the purposes of understanding and ease of description, the thicknesses of some layers, films, panels, regions, etc., may be exaggerated. 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.

[0101] 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 fluorescence 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, and a first optical fiber. The first optical fiber 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 fluorescence beam formed by the retina. The excitation beam is then incident on the light source detection module through the beam scanning module and transmitted to the first detection module through the first cladding of the first double-clad optical fiber and the first coupling optical fiber for fluorescence imaging.

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

3. The retinal fluorescence imaging device according to claim 2, characterized in that, The beam scanning module further includes a beam phase modulation element located on different conjugate surfaces of the pupil; the light source detection module further includes a wavefront sensor.

4. The retinal fluorescence imaging device according to claim 3, characterized in that, The beam scanning module further includes a tracking galvanometer, which is located on different conjugate surfaces of the pupils of the eyeball.

5. The retinal fluorescence imaging device according to claim 1, characterized in that, Also includes: The acquisition and control module is used at least to generate a fluorescence image based on the detection signal from the first detection module.

6. The retinal fluorescence imaging device according to any one of claims 1 to 5, characterized in that, The light source detection module further includes a second light source module and a second detection module, wherein, The 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. The reflected beam formed by the retina is incident on the second detection module through the beam scanning module for reflection imaging.

7. The retinal fluorescence imaging device according to claim 6, characterized in that, The light source detection module further includes: a first beam splitter located on the output light path of the second light source module; The second detection module includes: a collecting lens, a confocal aperture, and a second detection component located on the optical path formed by the reflection of the reflected beam by the first beam splitter.

8. The retinal fluorescence imaging device according to claim 7, characterized in that, The light source detection module further includes: a second beam splitter located on the transmission optical path of the first beam splitter, the second beam splitter being used to reflect the light generated by the second light source module to the beam scanning module; The light source detection module also includes: The first collimating element is located in the beam path of the first light source module; A dichroic mirror is located on the optical path formed by the collimation of the beam from the first light source module by the first collimating element, and the dichroic mirror is also located on the reflected optical path formed by the reflection of the beam from the second light source module by the second beam splitting element.

9. The retinal fluorescence imaging device according to claim 6, characterized in that, The light source detection module further includes a second optical fiber, which comprises a second double-clad optical fiber and a second coupling optical fiber; wherein... The light generated by the second light source module is transmitted through the core of the second double-clad optical fiber and enters the beam scanning module. After being modulated by the beam scanning module, it enters the eyeball. The reflected beam formed by the retina is transmitted through the beam scanning module to the light source detection module, and then transmitted through the second cladding of the second double-clad optical fiber and the second coupling optical fiber to the second detection module for reflection imaging.

10. The retinal fluorescence imaging device according to claim 9, characterized in that, The light source detection module further includes: a second beam splitter located on the light path output by the second light source module, used to reflect the light generated by the second light source module to the beam scanning module; The light source detection module also includes: The first collimating element is located in the beam path of the first light source module; A dichroic mirror is located on the optical path formed by the collimation of the beam from the first light source module by the first collimating element, and the dichroic mirror is also located on the reflected optical path formed by the reflection of the beam from the second light source module by the second beam splitting element.

Images