A non-coaxial multi-optical path integrated optical system

Abstract

The present invention relates to the field of eyeglass treatment equipment, and in particular to a non-coaxial multi-light path integrated optical system. It comprises: a camera observation light path unit, an indicator light light path unit, a scanning galvanometer, a scanning lens and a first long-wavelength pass dichroic mirror. The scanning lens is used to focus the laser, indicator light and coherent tomography light emitted by the scanning galvanometer onto a target area. The first long-wavelength pass dichroic mirror is used to project the reflected light of the visible light on the surface of the eyeball in the first light path into the second light path. In the present invention, the incident end of the second light path can be set on the side of the scanning lens close to the eyeball through the first long-wavelength pass dichroic mirror. Therefore, even if the indicator light forms a large reflection on the incident side of the scanning lens, since the incident end of the second light path is not located on the side where the reflected visible light is located, no reflected indicator light will enter the camera, thereby avoiding the problem of reddish light and poor imaging quality in the captured image.

Description

Technical Field

[0001] The present invention relates to the field of eyeglass treatment equipment, and in particular to a non-coaxial multi-light path integrated optical system. Background Art

[0002] Glaucoma is a disease associated with optic nerve damage and is usually associated with increased intraocular pressure. If left untreated, it can lead to vision loss or even blindness. In glaucoma patients, especially those with primary open-angle glaucoma (POAG), the function of the trabecular meshwork is usually impaired, resulting in obstruction of aqueous humor outflow, which in turn causes increased intraocular pressure. Increased intraocular pressure can compress the optic nerve and lead to irreversible vision loss. In related technologies, optical coherence tomography (OCT), camera imaging, indicator light irradiation and other technologies are used to observe the condition of the eye, and lasers and scanning galvanometers are used to perform minimally invasive operations on the trabecular meshwork to improve aqueous humor outflow, thereby reducing intraocular pressure for treatment.

[0003] Usually, in order to simplify the structure and miniaturize the equipment, the OCT system, laser system, camera imaging system and indicator light system are set up in the same optical path, so that the OCT light, laser and indicator light will eventually enter the eye along the coaxial optical path with the same optical axis. The camera obtains imaging information of the surface of the eye by collecting the visible light returning in the coaxial optical path. However, since the wavelength of the indicator light is much smaller than the wavelength of the OCT light and the wavelength of the laser, in order to allow the OCT light and laser to pass smoothly, a higher wavelength transmission range is set on the devices in the coaxial optical path. However, since the indicator light is visible light and its wavelength is short, it will form a large reflection on the devices in the coaxial optical path. Ultimately, these reflected light rays enter the imaging optical path of the camera system together, resulting in the image of the surface of the eyeball being captured with a reddish cast and poor imaging quality. Summary of the Invention

[0004] In view of this, the present invention provides a non-coaxial multi-light-path integrated optical system, which at least partially solves the problems existing in the prior art.

[0005] According to one aspect of the present invention, there is provided a non-coaxial multi-light-path integrated optical system, comprising:

[0006] Laser optical path unit, optical coherence tomography optical path unit, camera observation optical path unit, indicator light optical path unit, scanning galvanometer, scanning lens and first long-wave pass dichroic mirror.

[0007] The laser optical path unit, the optical coherence tomography optical path unit and the indicator light optical path unit are respectively used to project corresponding light rays onto the scanning galvanometer.

[0008] The scanning lens is located on the light-emitting side of the scanning galvanometer. It integrates the laser light, indicator light, and coherence tomography light emitted by the scanning galvanometer into the first optical path and focuses it on the target area. The scanning lens has a wavelength transmission range of [800nm, 1100nm].

[0009] The camera observation optical path unit includes a zoom camera, a ring light source and a focusing lens.

[0010] A first long-wavelength dichroic mirror is disposed in the first optical path and is located on the light-exiting side of the scanning lens. The first long-wavelength dichroic mirror is used to project the reflected visible light from the surface of the eyeball in the first optical path into the second optical path. A condenser lens is located in the second optical path, and the optical axis of the condenser lens is the same as the optical axis of the second optical path. The condenser lens is used to converge the incident light in the second optical path. A zoom camera is disposed on the light-exiting side of the condenser lens. The optical axis of the first optical path is different from the optical axis of the second optical path.

[0011] The annular light source is coaxially arranged with the first optical path, and is located on a side of the first long-wavelength dichroic mirror close to the eyeball.

[0012] The technical solution of the present invention has at least the following beneficial effects:

[0013] In the present invention, a first long-wavelength dichroic mirror is used to reflect light reflected from the eye's surface within the optical path (i.e., the first optical path) containing the laser, indicator light, and coherence tomography light, into the camera's observation optical path (i.e., the second optical path), enabling the camera to capture and image the image. By separating the first and second optical paths, the incident end of the second optical path can be positioned on the side of the scanning lens closest to the eye. Thus, even if the indicator light is significantly reflected from the incident side of the scanning lens, since the incident end of the second optical path is not located on the side where the reflected visible light is located, no reflected indicator light enters the camera's imaging optical path. This prevents red cast and poor image quality in the captured image of the eye's surface.

[0014] Furthermore, the present invention uses a lens as a device to focus the light rays in the coaxial optical path on the relevant area of ​​the eye. Due to its larger diameter, the lens provides a larger light entry aperture. This, in turn, reduces the galvanometer deflection angle restrictions during scanning, thereby increasing the scanning range. This also provides a larger incident light diameter for the laser, thereby reducing the resulting treatment spot size and improving treatment precision.

[0015] Furthermore, the light received by the camera observation optical path unit in the present invention is light from the second optical path. Since the second optical path is independent of the first optical path, sufficient space is available for installation of the camera observation optical path unit. Therefore, in this embodiment, the camera observation optical path unit includes a zoom camera and a condenser lens. The condenser lens focuses the incident light, thereby improving the resolution of the resulting zoom camera image. Furthermore, by adjusting the focal length of the zoom camera, the image magnification can be varied, switching from a wide to a narrow field of view, allowing for clearer observation of the eye and facilitating the doctor's trabecular meshwork positioning. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for use in the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0017] Figure 1 Schematic diagram of the structure of a non-coaxial multi-light path integrated optical system in one embodiment of the present application; wherein the dotted line is a schematic diagram of light path propagation, and the dot-dash line is a schematic diagram of communication control;

[0018] Figure 2 This is a schematic diagram of the shapes and colors of the light spots of two indicator light beams at different plane positions in the Z direction in another embodiment of the present application.

[0019] Reference numerals

[0020] 10. Zoom camera; 11. Condensing lens; 12. Reflector; 13. Ring light source; 20. First long-wavelength pass dichroic mirror; 21. Scanning lens; 22. Scanning galvanometer; 23. Second long-wavelength pass dichroic mirror; 24. Third long-wavelength pass dichroic mirror; 30. Optical coherence tomography scanner; 40. Indicator light source; 41. Spectroscopic mask; 42. Beam expander; 50. Laser light source; 51. Adjustable beam expander; 60. Negative pressure ring; 61. Vacuum pump. DETAILED DESCRIPTION

[0021] The embodiments of the present invention are described in detail below with reference to the accompanying drawings.

[0022] It should be noted that the following embodiments and features therein may be combined with each other unless they conflict. Furthermore, all other embodiments derived by persons of ordinary skill in the art based on the embodiments in this disclosure without inventive effort are also within the scope of protection of this disclosure.

[0023] It should be noted that various aspects of the embodiments within the scope of the appended claims are described below. It should be apparent that the aspects described herein can be embodied in a wide variety of forms, and any specific structure and / or function described herein is merely illustrative. Based on this disclosure, it should be understood by those skilled in the art that an aspect described herein can be implemented independently of any other aspect, and two or more of these aspects can be combined in various ways. For example, any number of aspects described herein can be used to implement an apparatus and / or practice a method. In addition, other structures and / or functionalities other than one or more of the aspects described herein can be used to implement this apparatus and / or practice this method.

[0024] As an embodiment of the present invention, Figure 1 As shown, a non-coaxial multi-optical path integrated optical system is provided, including: a laser optical path unit, an optical coherence tomography optical path unit, a camera observation optical path unit, an indicator light optical path unit, a scanning galvanometer 22, a scanning lens 21 and a first long-wave pass dichroic mirror 20.

[0025] The laser optical path unit, the optical coherence tomography optical path unit, and the indicator light optical path unit are respectively used to project corresponding light rays onto the scanning galvanometer 22 .

[0026] In this embodiment, the laser optical path unit is used to provide a femtosecond laser for minimally invasive thermal ablation of tissue in the eye. The optical coherence tomography optical path unit is used to obtain high-resolution cross-sectional images of the internal structure of the eye, and the camera observation optical path unit is used to obtain images of the eye surface. The images obtained by the optical coherence tomography optical path unit and the camera observation optical path unit are used to guide the user in operating the femtosecond laser on the corresponding tissue.

[0027] In this embodiment, the laser optical path unit includes a laser light source 50 and a beam expander 42 .

[0028] The beam expander 42 is disposed on the light-emitting side of the laser light source 50 , and the expanded laser beam passes through the third optical path and enters the scanning galvanometer 22 .

[0029] The laser light source 50 is a laser light source 50 that can emit femtosecond laser with a wavelength of 1030 nm, and the adjustable beam expander 51 is used to increase the diameter of the laser.

[0030] The optical coherence tomography optical path unit includes an optical coherence tomography scanner 30 .

[0031] The third long-wavelength pass dichroic mirror 24 is used to reflect the coherence tomography light from the optical coherence tomography scanner 30 and transmit it through the second long-wavelength pass dichroic mirror 23 before transmitting it to the scanning galvanometer 22. The wavelength range of the coherence tomography light is [800nm, 900nm].

[0032] The indicator light path unit includes an indicator light source 40 , a spectroscopic mask 41 and a beam expander 42 .

[0033] Along the direction of light emission from the indicator light source 40, a spectroscopic mask 41 and a beam expander 42 are sequentially arranged. The wavelength of the indicator light is 660 nm. The beam expander 42 can be a 3x beam expander 42.

[0034] The spectroscopic mask 41 is used to filter the output light from the indicator light source 40 into two parallel beams. The beam expander 42 is used to expand the diameter of each beam. The second long-wavelength dichroic mirror 23 is used to reflect the two expanded beams to the scanning galvanometer 22.

[0035] like Figure 2 As shown, in this embodiment, the spectroscopic mask 41 is primarily used to split the indicator light into two parallel beams. These are then reflected by the scanning galvanometer mirror 22 and enter the first optical path. Under the focusing process of the scanning lens 21, the two parallel beams ultimately converge at the same focal point. Consequently, along the optical axis of the first optical path (i.e., the Z direction), the two beams gradually emerge from their separation, completely overlapping at the focal point on the focal plane of the scanning lens 21 before gradually separating again. Therefore, based on this characteristic, the degree of overlap between the two indicator light spots on any surface in the Z direction can be used to determine whether the current position is at the focal point of the scanning lens 21. This provides Z-direction positioning information for device operation.

[0036] The scanning lens 21 is located on the light-emitting side of the scanning galvanometer 22. It integrates the laser light, indicator light, and coherence tomography light emitted by the scanning galvanometer 22 into the first optical path and focuses them onto the target area. The wavelength transmission range of the scanning lens 21 is [800nm, 1100nm].

[0037] In the treatment of glaucoma, the target area targeted by the laser, indicator light, and coherence tomography light is the trabecular meshwork. During treatment, driven by the scanning galvanometer 22, the laser, indicator light, and coherence tomography light are sequentially scanned and focused on different parts of the trabecular meshwork. The thermal energy of the femtosecond laser then thermally ablates the corresponding parts of the trabecular meshwork.

[0038] At the same time, the relevant technology uses an objective lens as a device to focus each light beam on the relevant area of ​​the eyeball in the coaxial optical path. However, since the maximum incident aperture of the existing objective lens is 11.2 mm, the deflection angle of the galvanometer is limited during scanning, and the diameter of the incident light is limited, resulting in a limited scanning range.

[0039] The formula for calculating the laser spot diameter ω after it passes through the focusing lens is ω≈λf / πr. Here, λ is the laser wavelength, f is the focal length of the focusing lens, and r is the radius of the incident laser beam. In existing technologies, the small incident laser beam diameter also results in a larger treatment spot and lower treatment accuracy.

[0040] In this embodiment, a lens is used as a device to focus the light beams in the coaxial optical path on the relevant area of ​​the eye. Due to its larger diameter, the lens provides a larger light entry aperture. This, in turn, reduces the galvanometer mirror deflection angle restrictions during scanning, thereby increasing the scanning range. It also provides a larger incident light diameter for the laser, resulting in a smaller treatment spot and improved treatment precision.

[0041] The camera observation optical path unit includes a zoom camera 10 and a condenser lens 11 .

[0042] The first long-wavelength pass dichroic mirror 20 is arranged in the first optical path, and the first long-wavelength pass dichroic mirror 20 is located on the light-exiting side of the scanning lens 21. The first long-wavelength pass dichroic mirror 20 is used to project the reflected light of the visible light on the surface of the eyeball in the first optical path into the second optical path. The focusing lens 11 is located in the second optical path, and the optical axis of the focusing lens 11 is the same as the optical axis of the second optical path. The focusing lens 11 is used to converge the incident light in the second optical path. The zoom camera 10 is arranged on the light-exiting side of the focusing lens 11. The optical axis of the first optical path is different from the optical axis of the second optical path. In this embodiment, the focusing lens 11 can be a convex lens or an objective lens. The zoom range of the zoom camera 10 can be [12mm, 100mm], and the focal length of the focusing lens 11 can be 200mm.

[0043] In this embodiment, the second optical path is perpendicular to the first optical path and is specifically connected via a first long-wavelength-pass dichroic mirror 20. In other words, the second optical path is derived from a portion of the light from the first optical path. Since light diverges at a certain angle during propagation, more light must enter the zoom camera 10 lens to achieve a higher resolution of the image of the eye surface captured by the camera. Therefore, in this embodiment, a condenser lens 11 is provided before the zoom camera 10 to focus more light into the zoom camera 10.

[0044] Furthermore, in this embodiment, the zoom camera 10 and the condenser lens 11 form an entire imaging system. In this imaging system, the focal length of the condenser lens 11 complements and enhances the focal length of the zoom camera 10, thereby increasing the equivalent zoom range of the entire imaging system. For example, if the zoom range of the zoom camera 10 is [12 mm, 100 mm] and the focal length of the condenser lens 11 is 200 mm, the equivalent zoom range of the imaging system formed by the zoom camera 10 is [212 mm, 300 mm].

[0045] The relationship between a camera's focal length, field of view, and imaging magnification indicates that a shorter focal length allows the camera to capture a wider range of scenes, meaning a larger field of view (FOV) and a wider imaging range, with objects appearing smaller. Conversely, a longer focal length results in a smaller FOV, meaning the camera captures a narrower range of scenes, but objects appear larger. Therefore, the combination of the zoom camera 10 and condenser lens 11 can provide a wider zoom range, allowing the operator to more easily and conveniently switch the field of view when observing the optical path unit and the surface of the eye through the camera, thereby obtaining a global or local image.

[0046] The camera observation optical path unit also includes: a reflecting mirror.

[0047] The reflector is disposed between the zoom camera 10 and the focusing lens 11 to change the direction of the incident light of the zoom camera 10 .

[0048] By adding a reflector, the direction of the light path can be changed, and the installation position of the zoom camera 10 can be flexibly adjusted, further making the entire device more compact.

[0049] Furthermore, it also includes: a ring light source 13.

[0050] The annular light source 13 is coaxially arranged with the first optical path and is located on the side of the first long-wavelength dichroic mirror 20 close to the eyeball. The condenser lens 11 is an achromatic lens.

[0051] The ring light source 13 in this embodiment emits white light to illuminate the eye, enabling clearer imaging in the zoom camera 10. Because white light is composed of light of different colors (wavelengths), they have different refractive indices when passing through the focusing lens 11, causing them to be unable to converge to the same focal point. This can cause image fringing or reduced clarity. Therefore, in this embodiment, the focusing lens 11 is configured as an achromatic lens to address this issue and improve image clarity. Specifically, a corresponding coating or film can be added to the surface of the focusing lens 11 to achieve achromatic aberration.

[0052] In addition, this embodiment further includes a negative pressure ring 60 and a vacuum pump 61 .

[0053] The negative pressure ring 60 is disposed at one end of the first optical path close to the eyeball, and the negative pressure ring 60 is connected to a vacuum pump 61 .

[0054] During actual use, the negative pressure ring 60 and vacuum pump 61 work together to hold the eyeball in place, facilitating subsequent examination and treatment. A gonioscope can also be used. A gonioscope is a medical device specifically designed for ophthalmic examinations, primarily used to observe the structure of the anterior chamber angle of the eye in detail. The anterior chamber angle, located at the intersection of the iris and cornea, plays a key role in the drainage of intraocular fluid (aqueous humor). The state of the anterior chamber angle is crucial for the diagnosis and management of eye diseases such as glaucoma.

[0055] As another possible embodiment of the present invention, the cutoff wavelengths of the first long-wave pass dichroic mirror 20 and the second long-wave pass dichroic mirror 23 are both 650 nm, and the cutoff wavelength of the third long-wave pass dichroic mirror 24 is 940 nm.

[0056] In the present invention, the first long-wavelength pass dichroic mirror 20, the second long-wavelength pass dichroic mirror 23 and the third long-wavelength pass dichroic mirror 24 can achieve the cutoff wavelength of the corresponding band by providing anti-reflection films of corresponding wavelengths on their surfaces.

[0057] In this embodiment, a long-pass dichroic mirror is a special optical filter that selectively reflects short-wavelength light and transmits long-wavelength light. Specifically, a long-pass dichroic mirror exhibits a wavelength range from nearly total reflection to nearly total transmission. Within this range, incident light partially transmits through the mirror and partially reflects. As the wavelength of the incident light increases, the proportion of transmitted light gradually increases, while the proportion of reflected light gradually decreases. The cutoff wavelength in this embodiment is the wavelength at which the long-pass dichroic mirror achieves a semi-transmissive, semi-reflective effect.

[0058] Taking a wavepass dichroic mirror with a cutoff wavelength of 650nm as an example, a wavepass dichroic mirror can achieve a semi-transmissive and semi-reflective effect for light with a wavelength of 650nm. While it can both transmit and reflect light with wavelengths between 650nm and 630nm, the transmittance decreases rapidly as the wavelength decreases. Light with a wavelength below 630nm is essentially not transmitted, achieving a state of total reflection.

[0059] Correspondingly, although light with a wavelength of 650nm to 680nm is both transmitted and reflected, the transmittance of the light increases rapidly with the increase of wavelength. For light with a wavelength above 680nm, it is basically not transmitted and reaches a state of total reflection.

[0060] like Figure 1As shown, according to the light propagation paths of each optical path unit in this embodiment, the third long-wavelength pass dichroic mirror 24 is mainly used to reflect the coherent tomography light with a wavelength range of [800nm, 900nm] into the third optical path, and the second long-wavelength pass dichroic mirror 23 is mainly used to reflect the indicator light with a wavelength of 660nm into the third optical path. At the same time, the third long-wavelength pass dichroic mirror 24 and the second long-wavelength pass dichroic mirror 23 cannot block the femtosecond laser with a wavelength of 1030nm, so the cutoff wavelengths of the second long-wavelength pass dichroic mirror 23 and the third long-wavelength pass dichroic mirror 24 are set as above.

[0061] In addition, since most of the visible light in the first optical path needs to be separated into the second optical path through the first long-wavelength pass dichroic mirror 20 for use in camera imaging, and the approximate range of visible light is 380nm to 780nm, the cutoff wavelength of the first long-wavelength pass dichroic mirror 20 needs to be near the maximum wavelength of visible light.

[0062] At the same time, the indicator light needs to be able to pass through the first long-wave dichroic mirror 20 and be reflected on the first long-wave dichroic mirror 20. Therefore, the cutoff wavelength of the first long-wave dichroic mirror 20 is also required to be close to the wavelength of the indicator light. Since the indicator light will undergo multiple processes similar to semi-transmission and semi-reflection on the propagation path of this system, the energy that finally reaches the human eye and the camera will be greatly weakened. Therefore, in this embodiment, red light with stronger energy in visible light is selected as the indicator light, and its specific wavelength is 660nm. Therefore, it is appropriate to set the cutoff wavelength of the first long-wave dichroic mirror 20 and the second long-wave dichroic mirror 23 to 650nm. On the one hand, it can avoid the damage to the eyeball caused by high-energy indicator light, and on the other hand, it can ensure good visibility when the camera is imaging.

[0063] The above are merely specific embodiments of the present invention, but the scope of protection of the present invention is not limited thereto. Any changes or substitutions that can be easily conceived by a person skilled in the art within the technical scope disclosed in the present invention should be included in the scope of protection of the present invention. Therefore, the scope of protection of the present invention should be based on the scope of protection of the claims.

Claims

1. A non-coaxial multi-light path integrated optical system, characterized in that: include: Laser optical path unit, optical coherence tomography optical path unit, camera observation optical path unit, indicator light optical path unit, scanning galvanometer, scanning lens and first long-wavelength pass dichroic mirror; The laser optical path unit, the optical coherence tomography optical path unit and the indicator light optical path unit are respectively used to project corresponding light onto the scanning galvanometer; The scanning lens is arranged on the light-emitting side of the scanning galvanometer. The scanning lens is used to integrate the laser, indicator light, and coherence tomography light emitted by the scanning galvanometer into the first optical path and focus them on the target area. The wavelength transmission range of the scanning lens is a closed interval of 800nm ​​to 1100nm. The first optical path is the optical path between the scanning lens and the target area. The target area is the tissue area of ​​the trabecular meshwork in the eyeball. The camera observation optical path unit includes a zoom camera, a ring light source and a focusing lens; The first long-wavelength-pass dichroic mirror is disposed in the first optical path, the first long-wavelength-pass dichroic mirror is located on the light-exiting side of the scanning lens, and is used to project the reflected light of the visible light from the surface of the eyeball in the first optical path into the second optical path; the condenser lens is located in the second optical path, the optical axis of the condenser lens is the same as the optical axis of the second optical path, and the condenser lens is used to converge the incident light in the second optical path; the zoom camera is disposed on the light-exiting side of the condenser lens; the optical axis of the first optical path is different from the optical axis of the second optical path; The second optical path is the observation optical path of the camera; The annular light source is arranged coaxially with the first optical path, and the annular light source is located on a side of the first long-wave pass dichroic mirror close to the eyeball.

2. The non-coaxial multi-light path integrated optical system according to claim 1, characterized in that: The camera observation optical path unit further includes: a reflector; The reflector is arranged between the zoom camera and the focusing lens, and is used to change the direction of the incident light of the zoom camera.

3. The non-coaxial multi-light path integrated optical system according to claim 1, characterized in that: The condensing lens is an achromatic lens.

4. The non-coaxial multi-light path integrated optical system according to claim 1, characterized in that: Also includes: a second long-wave-pass dichroic mirror and a third long-wave-pass dichroic mirror; The second long-wavelength pass dichroic mirror and the third long-wavelength pass dichroic mirror are both located in the third optical path; The third optical path is used to transmit the laser, the indicator light and the coherence tomography light to the scanning galvanometer.

5. The non-coaxial multi-light path integrated optical system according to claim 4, characterized in that: The indicator light path unit includes an indicator light source, a spectroscopic mask and a beam expander; Along the light emission direction of the indicator light source, the spectroscopic mask and the beam expander are arranged in sequence; The spectroscopic mask is used to filter the outgoing light of the indicator light source into two parallel beams; the beam expander is used to expand the diameter of each beam of light; the second long-wave pass dichroic mirror is used to reflect the two expanded beams of light to the scanning galvanometer.

6. The non-coaxial multi-light path integrated optical system according to claim 5, characterized in that: The optical coherence tomography optical path unit includes: an optical coherence tomography scanner; The third long-wavelength pass dichroic mirror is used to reflect the coherence tomography light of the optical coherence tomography scanner and transmit it through the second long-wavelength pass dichroic mirror to the scanning galvanometer.

7. The non-coaxial multi-light path integrated optical system according to claim 6, characterized in that: The laser optical path unit includes: a laser light source and a beam expander; The beam expander is arranged on the light-emitting side of the laser light source, and the expanded laser passes through the third optical path and enters the scanning galvanometer.

8. The non-coaxial multi-light path integrated optical system according to claim 7, characterized in that: The cutoff wavelengths of the first long-wave pass dichroic mirror and the second long-wave pass dichroic mirror are both 650 nm, and the cutoff wavelength of the third long-wave pass dichroic mirror is 940 nm; the wavelength of the laser is 1030 nm; the wavelength of the indicator light is 660 nm; and the wavelength range of the coherent tomography light is a closed interval from 800 nm to 900 nm.

9. The non-coaxial multi-light path integrated optical system according to claim 1, characterized in that: The condensing lens is a convex lens or an objective lens.

10. The non-coaxial multi-light path integrated optical system according to claim 1, characterized in that: It also includes a negative pressure ring and a vacuum pump; The negative pressure ring is arranged at one end of the first optical path close to the eyeball, and the negative pressure ring is connected to a vacuum pump.

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