Corneal endothelial cell meter light path system and corneal endothelial cell meter
By designing a multi-optical system, including imaging and thickness measurement branches, the imaging and measurement problems of corneal endothelial cells are solved, and efficient and clear corneal endothelial cell imaging and thickness measurement are achieved.
Patent Information
- Application Number
- CN202510367293.5
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2025-03-26
- Publication Date
- 2025-07-22
AI Technical Summary
The prior art is difficult to clearly image corneal endothelial cells and accurately measure thickness, especially due to their single-cell layer, high transparency and approximately spherical distribution, which makes imaging and measurement difficult.
A corneal endothelial cytometer optical path system is designed, including a first optical branch for imaging, a first auxiliary branch provides a light source, a second optical branch measures thickness and positiones the Z-axis, and a second auxiliary branch assists in measuring thickness, and simultaneous imaging and measurement are achieved through a multi-optical path design.
Clear imaging and accurate thickness measurement of corneal endothelial cells are achieved, and the two do not interfere with each other, and can be performed simultaneously, the device structure is compact and the power consumption is low.
Smart Images
Figure CN120345849A_ABST
Abstract
Description
Technical Field
[0001] The present invention relates to the technical field of ophthalmic medical devices, and particularly to an optical path system for a corneal endothelial cell meter and a corneal endothelial cell meter. Background Art
[0002] In the field of ophthalmic medical devices, the core function to be completed by a corneal endothelial cell meter is to clearly image corneal endothelial cells, and secondly to measure the corneal thickness.
[0003] The human cornea is a complex tissue with multiple layers of structure. Its inner surface is a non-renewable single-cell layer, namely the corneal endothelial cell layer. The indicators such as the number, density, size, and morphology of endothelial cells are closely related to the visual ability of the human eye. Since corneal endothelial cells are a single-cell layer, the cells are small and have very high transparency, and are in an approximately spherical distribution state. It is very difficult to clearly image and measure the thickness of them, and a special illumination and imaging optical path is required to achieve this. The imaging optical path scheme is the difficulty in the development of corneal endothelial cell meters. Summary of the Invention
[0004] The main object of the present invention is to propose an optical path system for a corneal endothelial cell meter and a corneal endothelial cell meter, aiming to provide an optical path system for a corneal endothelial cell meter and a corneal endothelial cell meter for imaging corneal endothelial cells of the human eye and measuring the corneal thickness.
[0005] To achieve the above object, the optical path system for a corneal endothelial cell meter proposed by the present invention includes:
[0006] A first optical branch for imaging corneal endothelial cells;
[0007] A first auxiliary branch, symmetrically arranged with the first optical branch, for providing a light source when the first optical branch images corneal endothelial cells;
[0008] A second optical branch for measuring the corneal thickness and human eye Z-axis positioning; and,
[0009] A second auxiliary branch for providing a signal light source to assist the second optical branch in measuring the corneal thickness and human eye Z-axis positioning.
[0010] In an embodiment, the first optical branch sequentially includes a first camera, a first filter, a first reflector, a first imaging objective lens, a first slit diaphragm, a first beam splitter, a first wedge prism, and a second imaging objective lens;
[0011] The first auxiliary branch sequentially includes a first illumination light source, a first condenser, a second slit diaphragm, a second beam splitter, a second wedge prism, and an illumination objective lens;
[0012] Wherein, the first light source and the first camera are synchronously arranged.
[0013] In one embodiment, the second slit diaphragm is conjugate to the corneal endothelial cell layer.
[0014] In one embodiment, the second optical branch includes a second camera and is sequentially connected and shares the first beam splitter, the first wedge prism, and the second imaging objective lens;
[0015] The second auxiliary branch sequentially includes a second illumination light source, a second condenser lens, and a first small hole diaphragm, and is sequentially connected and shares the second beam splitter, the second wedge prism, and the illumination objective lens;
[0016] Wherein, the second optical branch and the second auxiliary branch cooperate to measure the corneal thickness, and the second light source and the second camera are synchronously arranged.
[0017] In one embodiment, the corneal endothelial cell meter optical path system further includes a third optical branch for imaging the anterior surface of the human eye;
[0018] The third optical branch includes a third camera, a second filter, a circular aperture diaphragm, a third imaging objective lens, a third beam splitter, and a fourth beam splitter.
[0019] In one embodiment, the corneal endothelial cell meter optical path system further includes a supplementary light branch, and the supplementary light branch includes:
[0020] A first supplementary light branch, sequentially including a third illumination light source and a first collimating lens, connected to the fourth beam splitter;
[0021] A second supplementary light branch, sequentially including a fourth illumination light source and a second collimating lens; and,
[0022] A third supplementary light branch, sequentially including a fifth illumination light source and a third collimating lens;
[0023] Wherein, the second supplementary light branch and the third supplementary light branch are symmetrically arranged.
[0024] In one embodiment, the corneal endothelial cell meter optical path system further includes a first infrared supplementary light lamp and a second infrared supplementary light lamp, and the first infrared supplementary light lamp and the second infrared supplementary light lamp are symmetrically distributed along the optical axis of the third optical branch.
[0025] In one embodiment, the corneal endothelial cell meter optical path system further includes a fourth optical branch for human eye fixation;
[0026] The fourth optical branch sequentially includes a light source lamp board, an adjustable lens, a second small hole diaphragm, a second reflector, and a fixation lens, and is sequentially connected and shares the third beam splitter and the fourth beam splitter.
[0027] The present invention also provides a corneal endothelial cell meter, which includes the corneal endothelial cell meter optical path system as described in any one of the above.
[0028] Among them, the corneal endothelial cell meter optical path system includes:
[0029] A first optical branch for imaging corneal endothelial cells;
[0030] A first auxiliary branch, symmetrically arranged with the first optical branch, for providing a light source when the first optical branch images corneal endothelial cells;
[0031] A second optical branch for measuring corneal thickness; and,
[0032] A second auxiliary branch for assisting the second optical branch in measuring corneal thickness and for positioning the human eye along the Z-axis.
[0033] The technical solution of the present invention uses the first optical branch to image corneal endothelial cells, and at the same time, the first auxiliary branch symmetrically arranged with the first optical branch provides a light source when imaging corneal endothelial cells; then uses the second optical branch to measure corneal thickness, and the second auxiliary branch is used for positioning the human eye along the Z-axis of the optical path and assisting the second optical branch in measuring corneal thickness. With such a setting, the corneal endothelial cell meter optical path system can not only image corneal endothelial cells but also measure their thickness, and the two do not interfere with each other and can be carried out simultaneously. BRIEF DESCRIPTION OF THE DRAWINGS
[0034] In order to more clearly illustrate the technical solutions in the embodiments of the present invention or in the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the following drawings are only some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can be obtained based on the structures shown in these drawings.
[0035] Figure 1 FIG. is a schematic structural diagram of an embodiment of the corneal endothelial cell meter optical path system provided by the present invention.
[0036] Explanation of the reference numerals in the drawings:
[0037] 100. Corneal endothelial cell meter optical path system; 1. First optical branch; 11. First camera; 12. First filter; 13. First reflector; 14. First imaging objective lens; 15. First slit diaphragm; 16. First beam splitter; 17. First wedge prism; 18. Second imaging objective lens; 2. First auxiliary branch; 21. First illumination light source; 22. First condenser lens; 23. Second slit diaphragm; 24. Second beam splitter; 25. Second wedge prism; 26. Illumination objective lens; 3. Second optical branch; 31. Second camera; 4. Second auxiliary branch; 41. Second illumination light source; 42. Second condenser lens; 43. First small hole diaphragm; 5. Third optical branch; 51. Third camera; 52. Second filter; 53. Circular hole diaphragm; 54. Third imaging objective lens; 55. Third beam splitter; 56. Fourth beam splitter; 6. Supplementary light branch; 61. First supplementary light branch; 611. Third illumination light source; 612. First collimating lens; 62. Second supplementary light branch; 621. Fourth illumination light source; 622. Second collimating lens; 63. Third supplementary light branch; 631. Fifth illumination light source; 632. Third collimating lens; 7. First infrared supplementary light; 8. Second infrared supplementary light; 9. Fourth optical branch; 91. Light source lamp board; 92. Adjustable lens; 93. Second small hole diaphragm; 94. Second reflector; 95. Fixation lens.
[0038] The realization, functional characteristics and advantages of the object of the present invention will be further described with reference to the embodiments and the accompanying drawings. Detailed implementation manners
[0039] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts shall fall within the protection scope of the present invention.
[0040] It should be noted that if there are directional indications (such as up, down, left, right, front, back,...) involved in the embodiments of the present invention, the directional indications are only used to explain the relative position relationship and movement conditions between components in a specific posture. If the specific posture changes, the directional indications will also change accordingly.
[0041] In addition, if the descriptions such as "first", "second", etc. are involved in the embodiments of the present invention, the descriptions of "first", "second", etc. are only for descriptive purposes and should not be construed as indicating or implying their relative importance or implicitly specifying the quantity of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include at least one such feature. In addition, if "and / or" or "and / or" appears throughout the text, its meaning includes three parallel scenarios. Taking "A and / or B" as an example, it includes scenario A, scenario B, or the scenario where both A and B are satisfied simultaneously. In addition, the technical solutions between various embodiments can be combined with each other, but it must be based on the ability of those of ordinary skill in the art to implement. When the combination of technical solutions results in contradictions or cannot be implemented, it should be considered that such a combination of technical solutions does not exist.
[0042] In the field of ophthalmic medical devices, the core function that a corneal endothelial cell meter needs to complete is to clearly image corneal endothelial cells, and secondly, to measure corneal thickness.
[0043] The human cornea is a complex tissue with multiple layers of structure. Its inner surface is a non-renewable single-cell layer, namely the corneal endothelial cell layer. Indicators such as the number, density, size, and morphology of endothelial cells are closely related to the visual ability of the human eye. Since corneal endothelial cells are a single-cell layer, the cells are small and have very high transparency, and they are distributed in an approximately spherical state. It is very difficult to clearly image and measure the thickness of them, and special illumination and imaging optical paths are required to achieve this. The imaging optical path scheme is the difficulty in the development of corneal endothelial cell meters.
[0044] To solve the above problems, the present invention proposes a corneal endothelial cell meter optical path system and a corneal endothelial cell meter, aiming to provide a corneal endothelial cell meter optical path system and a corneal endothelial cell meter for imaging corneal endothelial cells of the human eye and measuring the thickness of the cornea. Figure 1 It is a schematic structural diagram of an embodiment provided by the corneal endothelial cell meter optical path system of the present invention.
[0045] Please refer to Figure 1 , in an embodiment of the present invention, the corneal endothelial cell meter optical path system 100 includes a first optical branch 1, a first auxiliary branch 2, a second optical branch 3, and a second auxiliary branch 4; the first optical branch 1 is used for imaging corneal endothelial cells; the first auxiliary branch 2 is symmetrically arranged with the first optical branch 1 and is used to provide a light source when the first optical branch 1 images corneal endothelial cells; the second optical branch 3 is used for measuring corneal thickness and human eye Z-axis positioning; the second auxiliary branch 4 provides a signal light source to assist the second optical branch 3 in measuring corneal thickness and human eye Z-axis positioning.
[0046] The technical solution of the present invention uses the first optical branch 1 to image corneal endothelial cells, and the first auxiliary branch 2 symmetrically arranged with the first optical branch 1 provides a light source for imaging corneal endothelial cells; then the second optical branch 3 measures the corneal thickness, and the second auxiliary branch 4 is used for positioning the optical path of the human eye Z-axis while assisting the second optical branch 3 to measure the corneal thickness. With such a setting, the optical path system 100 of the corneal endothelial cell meter can both image the cornea of the eye and measure its thickness, and the two do not interfere with each other and can be carried out simultaneously.
[0047] Further, please refer to Figure 1 , the first optical branch 1 sequentially includes a first camera 11, a first filter 12, a first mirror 13, a first imaging objective 14, a first slit diaphragm 15, a first beam splitter 16, a first wedge prism 17, and a second imaging objective 18; the first auxiliary branch 2 sequentially includes a first illumination light source 21, a first condenser 22, a second slit diaphragm 23, a second beam splitter 24, a second wedge prism 25, and an illumination objective 26; wherein, the first illumination light source 21 and the first camera 11 are arranged synchronously. It can be understood that in order to image the corneal endothelial cells by the first optical branch 1, the first optical branch 1 sequentially includes the first camera 11 to acquire an image, the first filter 12 filters out stray light in the environment, and then sequentially passes through the first mirror 13, the first imaging objective 14, the first slit diaphragm 15, the first beam splitter 16, the first wedge prism 17, and the second imaging objective 18; the first auxiliary branch 2 provides illumination for the first optical branch 1 to image the corneal endothelial cells, and sequentially includes the first illumination light source 21, the first condenser 22 improves the illumination brightness by means of condensing, and then passes through the second slit diaphragm 23, the second beam splitter 24, the second wedge prism 25, and the illumination objective 26; in particular, the first light source and the first camera 11 are arranged synchronously. Thus, when the first camera 11 works, the first illumination light source 21 immediately works, and when the first camera 11 stops working, the first illumination light source 21 also stops working. With such a setting, the power consumption of the device can be further saved.
[0048] Further, the second slit diaphragm 23 is conjugate to the corneal endothelial cell layer (illumination target position). It can be understood that in order to obtain good imaging of corneal endothelial cells and prominent features, thus, the second slit diaphragm 23 is conjugate to the illumination target position of the corneal endothelial cell layer, and then the first auxiliary branch 2 adopts a Köhler illumination optical path. With such a setting, the illumination uniformity of the imaging image of the corneal endothelial cells is good, and the structural features of the corneal endothelial cells are prominent and convenient for observation.
[0049] It is understandable that, specifically, the first optical branch 1 adopts a two-stage magnifying imaging optical path to achieve high-resolution clear imaging of corneal endothelial cells. The human eye endothelial cell layer (object plane) is inclined with respect to the optical axis, and the first camera 11 (image plane) is also inclined with respect to the optical axis. The object plane and the image plane are in an inclined conjugate state, which is beneficial to clear imaging and has a larger depth of field. The first slit diaphragm 15 is located at the intermediate image position of the two-stage imaging optical path, that is, the first slit diaphragm 15 is conjugate to the endothelial cell layer (object plane) and also conjugate to the first camera 11. Therefore, the first slit diaphragm 15 is the field stop of the first optical branch 1. It limits the imaging range and also blocks the reflected light from the anterior surface of the human cornea from entering the first imaging objective 14; the first wedge mirror 17 and the second wedge mirror 25 are used to deflect the optical path, thereby further reducing the volume of the corneal endothelial cell meter optical path system 100; the first beam splitter 16 and the second beam splitter 24 are used to reflect the 498 nm corneal endothelial cell imaging beam and transmit the 850 nm corneal thickness measurement beam; the first filter 12 is a 498 nm narrow-band filter, which transmits the 498 nm wavelength and cuts off other wavelength bands to filter out stray light.
[0050] In addition, please refer to Figure 1 , the second optical branch 3 includes a second camera 31, and is sequentially connected and shares the first beam splitter 16, the first wedge mirror 17 and the second imaging objective 18; the second auxiliary branch 4 sequentially includes a second illumination light source 41, a second condenser 42 and a first small hole diaphragm 43, and is sequentially connected and shares the second beam splitter 24, the second wedge mirror 25 and the illumination objective 26; wherein, the second optical branch 3 and the second auxiliary branch 4 cooperate to measure the corneal thickness, and the second light source and the second camera are synchronously arranged. It is understandable that while measuring the corneal thickness, the Z-axis positioning of the human eye can also be performed. Specifically, the second optical branch 3 includes the second camera 31, and is sequentially connected and shares the first beam splitter 16, the first wedge mirror 17 and the second imaging objective 18. This setting further reduces the volume of the corneal endothelial cell meter optical path system 100; the second auxiliary branch 4 sequentially includes the second illumination light source 41, the second condenser 42 and the first small hole diaphragm 43, and is sequentially connected and shares the second beam splitter 24, the second wedge mirror 25 and the illumination objective 26. This setting further reduces the volume of the corneal endothelial cell meter optical path system 100; wherein, the second optical branch 3 and the second auxiliary branch 4 cooperate to measure the corneal thickness and achieve the Z-axis positioning of the human eye.
[0051] The second optical branch 3 and the second auxiliary branch 4 work together, and they have two functions: one is to accurately locate the distance between the inner cortex of the human cornea and the optical system (referred to as Z-axis positioning); the other is to measure the thickness of the human cornea. The projection light spot formed by the second auxiliary branch 4 is projected onto the cornea, and reflected light will be formed on both the outer surface and the inner surface (endothelial cell layer) of the cornea and enter the second optical branch 3. After passing through the second imaging objective lens 18, it converges onto the photosensitive surface of the second camera 31, forming two separate light spot images. Since the reflectivity of the outer surface of the cornea is high, the light spot formed on the outer surface of the cornea is large and bright, while the reflectivity of the inner cortex of the cornea is low, and the formed light spot is small and dim. The separation distance between these two light spots reflects the thickness of the cornea, and the corneal thickness is obtained through calibration and solved by a professional algorithm software. The position of the imaging light spot of the reflected light from the inner cortex of the cornea on the second camera 31 reflects the position of the inner cortex of the human cornea relative to the optical system, and the Z-axis position of the inner cortex of the cornea relative to the optical system is also obtained through solution by a professional algorithm software.
[0052] In addition, please refer to Figure 1 , the corneal endothelial cell meter optical path system 100 further includes a third optical branch 5 for imaging the anterior surface of the human eye; the third optical branch 5 includes a third camera 51, a second filter 52, a circular aperture stop 53, a third imaging objective lens 54, a third beam splitter 55, and a fourth beam splitter 56. It can be understood that in order to image the anterior surface of the human eye, the corneal endothelial cell meter optical path system 100 further includes the third optical branch 5. Specifically, the third optical branch 5 includes the third camera 51, the second filter 52, the circular aperture stop 53, the third imaging objective lens 54, the third beam splitter 55, and the fourth beam splitter 56, so as to obtain clear images of the human eye pupil and the human eye contour, with the purpose of automatically searching for the position of the human eye (pupil) and achieving alignment of the vertex of the human cornea relative to the optical system in the X and Y directions (X is the horizontal direction, Y is the vertical direction, that is, the direction perpendicular to the paper surface).
[0053] Furthermore, please refer to Figure 1, the corneal endothelial cell meter optical path system 100 further includes a supplementary light branch 6, and the supplementary light branch 6 includes a first supplementary light branch 61, a second supplementary light branch 62, and a third supplementary light branch 63; the first supplementary light branch 61 successively includes a third illumination light source 611 and a first collimating lens 612, and is connected to the fourth beam splitter 56; the second supplementary light branch 62 successively includes a fourth illumination light source 621 and a second collimating lens 622; the third supplementary light branch 63 successively includes a fifth illumination light source 631 and a third collimating lens 632; wherein, the second supplementary light branch 62 and the third supplementary light branch 63 are symmetrically arranged. It can be understood that the first supplementary light branch 61, the second supplementary light branch 62, and the third supplementary light branch 63 included in the supplementary light branch 6 provide signal light sources for corneal positioning for the third optical branch 5..
[0054] Further, please refer to Figure 1 , the corneal endothelial cell meter optical path system 100 further includes a first infrared supplementary light lamp 7 and a second infrared supplementary light lamp 8, and the first infrared supplementary light lamp 7 and the second infrared supplementary light lamp 8 are symmetrically distributed along the optical axis of the third optical branch 5. It can be understood that for supplementary light illumination of the anterior surface of the human eye, the corneal endothelial cell meter optical path system 100 further includes the first infrared supplementary light lamp 7 and the second infrared supplementary light lamp 8. Specifically, the first infrared supplementary light lamp 7 and the second infrared supplementary light lamp 8 are symmetrically distributed along the optical axis of the third optical branch 5. With such a setting, the light distribution for supplementary light illumination of the anterior surface of the human eye is uniform, which is beneficial to the clear imaging of the eye surface contour features and is beneficial to the search and positioning of the human eye pupil position. It can be understood that both the first infrared supplementary light lamp 7 and the second infrared supplementary light lamp 8 are 940nm light.
[0055] It can be understood that the third optical branch 5, the first supplementary light branch 61, the second supplementary light branch 62, the third supplementary light branch 63, the first infrared supplementary light lamp 7, and the second infrared supplementary light lamp 8 work in cooperation.
[0056] Among them, the third optical branch 5 is an imaging optical path, which images the anterior surface of the human eye to obtain clear images of the human eye pupil and the human eye contour. The purpose is to automatically search for the position of the human eye (pupil) and realize the alignment of the corneal apex of the human eye with respect to the optical path system in the X and Y directions (X is the horizontal direction, Y is the vertical direction, that is, the direction perpendicular to the paper surface).
[0057] The light beams projected by the first supplementary light branch 61, the second supplementary light branch 62, and the third supplementary light branch 63 onto the human cornea are reflected by the outer surface of the human cornea and enter the third optical branch 5. They are imaged onto the third camera 51 (the third camera 51 can also be a area array camera) by the third imaging objective lens 54. The three separated spot images (the xy coordinate positions of the spots on the third camera 51) obtained by the third camera 51 reflect the XY-direction position of the human corneal apex relative to the optical path system. After calibration and determination by professional algorithm software, the XY-direction position information of the human corneal apex relative to the optical path system is obtained, thereby being used for the precise positioning of the human corneal apex in the XY direction relative to the optical system.
[0058] The third optical branch 5 preferably adopts an object-space telecentric imaging optical path, that is, the circular aperture stop 53 is arranged on the rear focal plane of the third imaging objective lens 54, which is beneficial to improving the positioning accuracy of the human corneal apex.
[0059] The third optical branch 5 realizes the precise positioning of the corneal apex in the XY direction. Combining with the Z-direction precise positioning realized by the second optical branch 3, the precise positioning of the entire optical path system relative to the human corneal endothelial cell layer can be achieved, ensuring that the positions of the corneal endothelial cells captured by the first optical branch 1 each time are accurate, the imaging is clear, and the repeatability is high. The whole process is controlled by professional software, realizing fully automated human eye alignment and corneal endothelial cell imaging, with high reliability, clear images, and good repeatability.
[0060] Additionally, the second filter 52 is a narrow-band filter of 940 nm, which can effectively filter out the interference of ambient stray light and ensure the stability and reliability of the system operation. The third beam splitter 55 reflects light of 570 nm and transmits light of 940 nm. The fourth beam splitter 56 is a semi-reflective and semi-transmissive beam splitter of 940 nm.
[0061] In addition, please refer to Figure 1 , the corneal endothelial cell meter optical path system 100 further includes a fourth optical branch 9 for human eye fixation; the fourth optical branch 9 sequentially includes a light source lamp board 91, an adjustable lens 92, a second small aperture stop 93, a second mirror 94, and a fixation lens 95, and are sequentially connected and share the third beam splitter 55 and the fourth beam splitter 56. It can be understood that the fourth optical branch 9 is a human eye fixation optical path, and its function is to provide a visual target and stabilize the human eye visual axis during the process of human eye alignment and capturing corneal endothelial cell images; specifically, the fourth optical branch 9 sequentially includes the light source lamp board 91, the adjustable lens 92, the second small aperture stop 93, the second mirror 94, and the fixation lens 95, and are sequentially connected and share the third beam splitter 55 and the fourth beam splitter 56. With such a setting, it has the effect of reducing the volume of the optical system.
[0062] In addition, by controlling the lighting and extinguishing of the LED lights at different positions on the light source lamp board 91, the state of the human eye visual axis is adjusted, so as to change the position of the corneal endothelium layer aligned with the first optical branch 1, and cell images of different positions of the corneal endothelium are obtained. The light source lamp board 91 may be a single LED light or multiple LED lights, and the arrangement of the multiple LED lights can be adjusted according to needs. The second small aperture diaphragm 93 is preferably arranged on the focal plane of the adjustable lens 92 (in the telecentric optical path mode). The advantage of such an arrangement is that the LED lights observed by the human eye are all in the front view orientation, and the fixation effect is better.
[0063] The present invention provides a corneal endothelial cell meter, which includes the corneal endothelial cell meter optical path system 100. The specific structure of the corneal endothelial cell meter optical path system 100 refers to the above embodiments. Since the corneal endothelial cell meter adopts all the technical solutions of the above embodiments, it at least has all the beneficial effects brought by the technical solutions of the above embodiments, which will not be elaborated one by one here.
[0064] The above are only exemplary embodiments of the present invention, and do not limit the patent scope of the present invention accordingly. Any equivalent structural transformation made by using the content of the specification and drawings of the present invention under the technical concept of the present invention, or direct / indirect application in other related technical fields, is included in the patent protection scope of the present invention.
Claims
1. An optical path system of a corneal endothelial cell meter, characterized in that, Comprising: A first optical branch for corneal endothelial cell imaging; A first auxiliary branch, symmetrically arranged with the first optical branch, for providing a light source when the first optical branch images corneal endothelial cells; A second optical branch for measuring corneal thickness and human eye Z-axis positioning; And, A second auxiliary branch for providing a signal light source to assist the second optical branch in measuring corneal thickness and human eye Z-axis positioning.
2. The corneal endothelial cell meter optical path system according to claim 1, wherein The first optical branch sequentially includes a first camera, a first filter, a first mirror, a first imaging objective lens, a first slit diaphragm, a first beam splitter, a first wedge prism, and a second imaging objective lens; The first auxiliary branch sequentially includes a first illumination light source, a first condenser lens, a second slit diaphragm, a second beam splitter, a second wedge prism, and an illumination objective lens; Wherein, the first light source and the first camera are synchronously arranged.
3. The corneal endothelial cell meter optical path system according to claim 2, wherein, The second slit diaphragm is conjugate to the position of the corneal endothelial cell layer.
4. The corneal endothelial cell meter optical path system according to claim 2, wherein, The second optical branch includes a second camera and is sequentially connected and shares the first beam splitter, the first wedge prism, and the second imaging objective lens; The second auxiliary branch sequentially includes a second illumination light source, a second condenser lens, and a first small aperture diaphragm, and is sequentially connected and shares the second beam splitter, the second wedge prism, and the illumination objective lens; Wherein, the second optical branch and the second auxiliary branch cooperate to measure corneal thickness, and the second light source and the second camera are synchronously arranged.
5. The corneal endothelial cell meter optical path system according to claim 1, wherein, The corneal endothelial cell meter optical path system further includes a third optical branch for imaging the anterior surface of the human eye; The third optical branch includes a third camera, a second filter, a circular aperture diaphragm, a third imaging objective lens, a third beam splitter, and a fourth beam splitter.
6. The corneal endothelial cell meter optical path system according to claim 5, wherein, The corneal endothelial cell meter optical path system further includes a supplementary light branch, and the supplementary light branch includes: A first supplementary light branch, sequentially including a third illumination light source and a first collimating lens, connected to the fourth beam splitter; A second supplementary light branch, sequentially including a fourth illumination light source and a second collimating lens; and, A third supplementary light branch, sequentially including a fifth illumination light source and a third collimating lens; Wherein, the second supplementary light branch and the third supplementary light branch are symmetrically arranged.
7. The corneal endothelial cell meter optical path system according to claim 5, characterized in that, The corneal endothelial cell meter optical path system further includes a first infrared supplementary light lamp and a second infrared supplementary light lamp, and the first infrared supplementary light lamp and the second infrared supplementary light lamp are symmetrically distributed along the optical axis of the third optical branch.
8. The corneal endothelial cell meter optical path system according to claim 5, wherein, The corneal endothelial cell meter optical path system further includes a fourth optical branch for human eye fixation; The fourth optical branch sequentially includes a light source lamp board, an adjustable lens, a second small aperture diaphragm, a second mirror, and a fixation lens, and is sequentially connected and shares the third beam splitter and the fourth beam splitter.
9. A corneal endothelial cell meter, characterized in that, The corneal endothelial cell meter includes the corneal endothelial cell meter optical path system according to any one of claims 1-8.