Non-coaxial multi-optical-path integrated optical system

Abstract

The invention relates to the field of glasses treatment equipment, in particular to a non-coaxial multi-optical-path integrated optical system. Comprising a camera observation light path unit, an indicating light path unit, a scanning galvanometer, a scanning lens and a first long-wave-pass dichroscope. The scanning lens is used for focusing the laser, the indicating light and the coherence tomography light emitted by the scanning galvanometer to a target area. The first long-wave-pass dichroscope is used for projecting reflected light of visible light on the surface of the eyeball in the first light path into the second light path. According to the invention, through the first long-wave-pass dichroscope, the incident end of the second light path can be arranged on one side, close to the eyeball, of the scanning lens. Therefore, even if the indicating light forms relatively large reflection on the incident side of the scanning lens, the incident end of the second light path is not located on the side where the reflected visible light is located, so that no reflected indicating light enters the camera, and the problems of red light flooding and poor imaging quality of a collected image can be avoided.

Description

Technical Field

[0001] The present invention relates to the field of ophthalmic treatment devices, and particularly to a non - coaxial multi - optical - path integrated optical system. Background Art

[0002] Glaucoma is a disease related to optic nerve damage, usually associated with elevated intraocular pressure. If left untreated, it can lead to vision loss and even blindness. In glaucoma patients, especially primary open - angle glaucoma (POAG), the function of the trabecular meshwork is usually impaired, resulting in blocked outflow of aqueous humor and thus increased intraocular pressure. The increased intraocular pressure compresses the optic nerve, leading to irreversible vision loss. In related technologies, techniques such as Optical Coherence Tomography (OCT), camera imaging, and indicator light irradiation are used to observe the eye condition, and lasers and scanning galvanometers are used to perform minimally invasive operations on the trabecular meshwork to improve the outflow of aqueous humor, thereby reducing intraocular pressure for treatment.

[0003] Generally, for the simplicity and miniaturization of the device structure, the OCT system, laser system, camera imaging system, and indicator light system are set with a common optical path. As a result, the light of OCT, laser, and indicator light will ultimately enter the eye along the coaxial optical path of the same optical axis. The camera acquires the imaging information of the eye surface by collecting the visible light returned in this coaxial optical path. However, since the wavelength of the indicator light is much smaller than the wavelengths of the OCT light and the laser, in order to allow the OCT light and the laser to pass through smoothly, a relatively high wavelength transmission range is set on the devices in the coaxial optical path. However, since the indicator light is visible light and has a short wavelength, a large reflection will be formed on the devices in the coaxial optical path. Eventually, these reflected lights enter the imaging optical path of the camera system together, resulting in problems such as red - light flooding and poor imaging quality of the acquired image of the eyeball surface. Summary of the Invention

[0004] In view of this, the present invention provides a non - coaxial multi - optical - 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, 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, a scanning lens, and a first long - wave - pass dichroic mirror.

[0006] The laser optical path unit, the optical coherence tomography optical path unit, and the indicator light optical path unit are respectively used to project the corresponding light onto the scanning galvanometer.

[0007] The scanning lens is disposed on the light-emitting side of the scanning galvanometer. The scanning lens is used to integrate the laser light, the indicating light, and the optical 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 [800 nm, 1100 nm].

[0008] The camera observation optical path unit includes a zoom camera, an annular light source, and a condenser lens.

[0009] The first long-pass dichroic mirror is disposed in the first optical path. The first long-pass dichroic mirror is located on the light-emitting side of the scanning lens. The first long-pass dichroic mirror 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 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. The condenser lens is used to converge the incident light in the second optical path. The zoom camera is disposed on the light-emitting 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 annular light source is disposed coaxially with the first optical path, and the annular light source is located on the side of the first long-pass dichroic mirror close to the eyeball.

[0010] The technical solution of the present invention has at least the following beneficial effects: In the present invention, through the first long-pass dichroic mirror, the reflected light on the surface of the eyeball in the optical path where the laser light, the indicating light, and the optical coherence tomography light are located (i.e., the first optical path) is reflected into the observation optical path of the camera (i.e., the second optical path), so that the camera can perform acquisition and imaging. After the first optical path and the second optical path are separately arranged, the incident end of the second optical path can be arranged on the side of the scanning lens close to the eyeball. Thus, even if a large reflection is formed on the incident side of the indicating light on 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, the reflected indicating light will not enter the imaging optical path of the camera system, and thus the problem of red light blooming and poor imaging quality in the image of the surface of the eyeball collected can be avoided.

[0011] At the same time, in the present invention, a lens is used as a device for focusing each light ray on the relevant area of the eyeball in the coaxial optical path. Since the diameter of the lens is larger, a larger light incident aperture can be provided. Correspondingly, when scanning, the deflection angle of the galvanometer is less restricted, and the scanning range can be increased. At the same time, a larger incident light diameter is provided for the laser, and thus the finally obtained treatment spot becomes smaller, and the treatment accuracy can be improved.

[0012] In addition, the light received by the camera observation optical path unit in the present invention is the light in the second optical path. Since the second optical path is independently arranged from the first optical path, there is sufficient space for the 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. By focusing the incident light through the condenser lens, the resolution of the final imaging of the zoom camera can be improved. In addition, by adjusting the focal length of the zoom camera, the magnification of the imaging can also be changed to switch from a large field of view to a small field of view, so as to observe the condition of the eyeball more clearly and facilitate the doctor's operation of positioning the trabecular meshwork. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings required for use in the embodiments will be briefly introduced below. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0014] Figure 1 It is a schematic structural diagram of a non-coaxial multi-optical path integrated optical system in an embodiment of the present application; wherein, the dotted line is the schematic of the optical path propagation, and the dash-dotted line is the schematic of the communication control. Figure 2 It is a schematic of the shape and color of the light spots when two indication light beams are at different plane positions in the Z direction in another embodiment of the present application.

[0015] REFERENCE NUMERALS 10. Zoom camera; 11. Condenser lens; 12. Reflecting mirror; 13. Annular light source; 20. First long-pass dichroic mirror; 21. Scanning lens; 22. Scanning galvanometer; 23. Second long-pass dichroic mirror; 24. Third long-pass dichroic mirror; 30. Optical coherence tomography scanner; 40. Indication light source; 41. Spectral mask; 42. Beam expander; 50. Laser light source; 51. Adjustable beam expander; 60. Negative pressure ring; 61. Vacuum pump. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0016] The embodiments of the present invention will be described in detail below with reference to the drawings.

[0017] It should be noted that, without conflict, the following embodiments and the features in the embodiments can be combined with each other. And, based on the embodiments in the present disclosure, all other embodiments obtained by those of ordinary skill in the art without creative efforts belong to the scope of protection of the present disclosure.

[0018] Note that the following description pertains to various aspects of embodiments within the scope of the appended claims. 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, those skilled in the art should understand that one 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 the aspects described herein can be used to implement an apparatus and / or practice a method. Additionally, this apparatus and / or method can be implemented using other structures and / or functionality in addition to one or more of the aspects described herein.

[0019] As an embodiment of the present invention, as Figure 1 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 indication light optical path unit, a scanning galvanometer 22, a scanning lens 21, and a first long - wave pass dichroic mirror 20.

[0020] The laser optical path unit, the optical coherence tomography optical path unit, and the indication light optical path unit are respectively used to project corresponding light rays onto the scanning galvanometer 22.

[0021] In this embodiment, the laser optical path unit is used to provide femtosecond laser to perform minimally invasive thermal ablation treatment on tissues in the eyeball. 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 surface of the eyeball. The images obtained by the optical coherence tomography optical path unit and the camera observation optical path unit are used to guide the user to operate the femtosecond laser to perform operations on the corresponding tissues.

[0022] In this embodiment, the laser optical path unit includes: a laser light source 50 and a beam expander 42.

[0023] The beam expander 42 is disposed on the light - emitting side of the laser light source 50, and the expanded laser passes through the third optical path and enters the scanning galvanometer 22.

[0024] 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.

[0025] The optical coherence tomography optical path unit includes: an optical coherence tomography scanner 30.

[0026] The third long - wave pass dichroic mirror 24 is used to reflect the coherence tomography light of the optical coherence tomography scanner 30, and after passing through the second long - wave pass dichroic mirror 23, it is transmitted to the scanning galvanometer 22. The wavelength range of the coherence tomography light is [800 nm, 900 nm].

[0027] The indicating light optical path unit includes an indicating light source 40, a beam splitting mask 41 and a beam expander 42.

[0028] Along the light emitting direction of the indicating light source 40, the beam splitting mask 41 and the beam expander 42 are arranged in sequence. The wavelength of the indicating light is 660 nm. The beam expander 42 can be a 3x beam expander 42.

[0029] The beam splitting mask 41 is used to filter the emitted light of the indicating light source 40 into two mutually parallel light beams. The beam expander 42 is used to expand the diameter of each light beam. The second long-wave pass dichroic mirror 23 is used to reflect the two expanded light beams to the scanning galvanometer 22.

[0030] As Figure 2 shown, in this embodiment, the beam splitting mask 41 is mainly used to split the indicating light into two parallel light columns, and then enter the first optical path after being reflected by the scanning galvanometer 22. And under the focusing process of the scanning lens 21, the two parallel light beams will finally converge at the same focus. Thus, in the optical axis direction (i.e., the Z direction) of the first optical path, the two light beams will gradually change from the separated state, and slowly completely overlap at the focus on the focal plane of the scanning lens 21, and then gradually separate. Therefore, based on this characteristic, it is possible to determine whether the current position is located at the focus of the scanning lens 21 by observing the overlapping degree of the two indicating light spots on any surface in the Z direction. Thus, it is possible to provide positioning information in the Z direction for the operation of the device.

[0031] The scanning lens 21 is arranged on the light emitting side of the scanning galvanometer 22. The scanning lens 21 is used to integrate the laser light, the indicating light and the optical coherence tomography light emitted by the scanning galvanometer 22 into the first optical path and focus them on the target area. The wavelength transmission range of the scanning lens 21 is [800 nm, 1100 nm].

[0032] In the usage scenario of treating glaucoma, the target area where the laser light, the indicating light and the optical coherence tomography light are focused is the tissue area of the trabecular meshwork. During the treatment process, under the drive of the scanning galvanometer 22, the laser light, the indicating light and the optical coherence tomography light are sequentially scanned and focused on different parts of the trabecular meshwork, and then the corresponding part of the trabecular meshwork is thermally ablated by the heat energy of the femtosecond laser.

[0033] At the same time, in the related art, an objective lens is used as a device that focuses 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, when scanning, the deflection angle of the galvanometer is limited, and the diameter of the incident light is limited, resulting in a limited scanning range.

[0034] According to the calculation formula for the spot diameter ω of the laser after passing through the focusing lens, ω≈λf / πr. Where λ is the wavelength of the laser, f is the focal length of the focusing lens, and r is the radius of the incident laser beam. In the prior art, due to the relatively small diameter of the incident light of the laser, the resulting treatment spot is relatively large and the treatment accuracy is low.

[0035] In this embodiment, a lens is used as a device that focuses each light ray on the relevant area of the eyeball in the coaxial optical path. Since the diameter of the lens is larger, a larger light incident aperture can be provided. Correspondingly, when scanning, the deflection angle of the galvanometer is less restricted, and the scanning range can be increased. At the same time, a larger incident light diameter can be provided for the laser, so that the resulting treatment spot becomes smaller and the treatment accuracy can be improved.

[0036] The camera observation optical path unit includes a zoom camera 10 and a condenser lens 11.

[0037] The first long-pass dichroic mirror 20 is disposed in the first optical path. The first long-pass dichroic mirror 20 is located on the light output side of the scanning lens 21. The first long-pass dichroic mirror 20 is used to project the reflected light of the visible light on the eyeball surface in the first optical path into the second optical path. The condenser lens 11 is located in the second optical path. The optical axis of the condenser lens 11 is the same as the optical axis of the second optical path. The condenser lens 11 is used to converge the incident light in the second optical path. The zoom camera 10 is disposed on the light output side of the condenser 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 condenser 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 condenser lens 11 can be 200mm.

[0038] In this embodiment, the second optical path is perpendicular to the first optical path, and is specifically connected through the first long-pass dichroic mirror 20. That is, the second optical path is separated from part of the light rays in the first optical path. Since there is a certain divergence angle in the propagation process of the light rays, in order to improve the resolution of the image of the eyeball surface collected by the camera, more light rays need to be incident on the lens of the zoom camera 10. Therefore, in this embodiment, a condenser lens 11 is disposed before the zoom camera 10 to converge more light rays into the zoom camera 10.

[0039] In addition, 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 and the focal length of the zoom camera 10 complement and enhance each other, thereby improving the equivalent zoom range of the entire imaging system. Taking the zoom range of the zoom camera 10 as [12mm, 100mm] and the focal length of the condenser lens 11 as 200mm as an example, the equivalent zoom range of the imaging system formed by the two is [212mm, 300mm].

[0040] According to the relationship between the camera focal length, the field of view size, and the imaging magnification, it can be known that the shorter the focal length, the wider the scene range that the camera can capture, that is, the larger the field of view angle (FOV), and the more extensive the imaging range, where the objects are relatively smaller; on the contrary, the longer the focal length, the smaller the field of view angle, which means that the scene range captured by the camera is narrower, but the objects in the imaging look larger. Therefore, the combination between the above zoom camera 10 and the condenser lens 11 can provide a larger zoom range, and further facilitate the operator to switch the field of view size more freely and conveniently when observing the optical path unit through the camera to view the surface condition of the eyeball, so as to obtain a global image or a local image.

[0041] The camera observing the optical path unit further includes: a reflector.

[0042] The reflector is arranged between the zoom camera 10 and the condenser lens 11, and is used to change the direction of the incident light of the zoom camera 10.

[0043] By adding a reflector, the optical path direction can be changed, the installation orientation of the zoom camera 10 can be flexibly adjusted, and further the whole device can become more compact.

[0044] Furthermore, it further includes: an annular light source 13.

[0045] The annular light source 13 is arranged coaxially with the first optical path, and the annular light source 13 is located on the side of the first long-pass dichroic mirror 20 close to the eyeball. The condenser lens 11 is an achromatic lens.

[0046] The annular light source 13 in this embodiment emits white light, which is used to provide illumination for the eyeball to form a clearer image in the zoom camera 10. Since white light is composed of light of different colors (wavelengths), it has different refractive indices when passing through the condenser lens 11, resulting in that they cannot be focused on the same focal point. This will cause problems such as colored edges or decreased clarity in the image. Therefore, in this embodiment, the condenser lens 11 is set as an achromatic lens to solve the above problems and improve the imaging clarity. Specifically, corresponding coatings or films can be added on the surface of the condenser lens 11 to achieve the achromatic effect.

[0047] In addition, this embodiment further includes a negative pressure ring 60 and a vacuum pump 61.

[0048] The negative pressure ring 60 is arranged at one end of the first optical path close to the eyeball, and the negative pressure ring 60 is connected to the vacuum pump 61.

[0049] In the actual use process, the negative pressure ring 60 cooperates with the vacuum pump 61 to suck the eyeball, so as to facilitate subsequent inspection and treatment operations. In addition, a gonioscope can also be set. A gonioscope is a medical device specifically used for ophthalmic examinations, mainly used to observe the anterior chamber angle structure of the eye in detail. The anterior chamber angle is an area located at the intersection of the iris and the cornea, and it plays a key role in the drainage process of intraocular fluid (aqueous humor). The condition of the anterior chamber angle is very important for the diagnosis and management of eye diseases such as glaucoma.

[0050] As another possible embodiment of the present invention, the cut-off wavelengths of the first long-pass dichroic mirror 20 and the second long-pass dichroic mirror 23 are both 650 nm, and the cut-off wavelength of the third long-pass dichroic mirror 24 is 940 nm.

[0051] In the present invention, the first long-pass dichroic mirror 20, the second long-pass dichroic mirror 23, and the third long-pass dichroic mirror 24 can all achieve the cut-off wavelengths of the corresponding wavelength bands by setting an anti-reflection film with the corresponding wavelength on the surface.

[0052] In this embodiment, the long-pass dichroic mirror is a special optical filter, which is used to selectively reflect short-wavelength light and transmit long-wavelength light. Specifically, there will be a wavelength change range from almost total reflection to almost total transmission for the long-pass dichroic mirror. In this range, for the incident light, part of the light will pass through the mirror body, and part of the light will be reflected. And as the wavelength of the incident light increases, the proportion of the transmitted light gradually increases, and the proportion of the reflected light gradually decreases. The cut-off wavelength in this embodiment is the wavelength at which the long-pass dichroic mirror has a semi-transmissive and semi-reflective effect on the light of this wavelength.

[0053] Taking the dichroic mirror with a cut-off wavelength of 650 nm as an example, the dichroic mirror can achieve a semi-transmissive and semi-reflective effect on the light with a wavelength of 650 nm. For the light with wavelengths from 650 nm to 630 nm, although there is both transmission and reflection, the transmittance of the light will rapidly decrease as the wavelength decreases. For the light with a wavelength below 630 nm, it basically does not pass through and reaches the total reflection state.

[0054] Correspondingly, for the light with wavelengths from 650 nm to 680 nm, although there is both transmission and reflection, the transmittance of the light will rapidly increase as the wavelength increases. For the light with a wavelength above 680 nm, it basically does not pass through and reaches the total reflection state.

[0055] Such as Figure 1As shown, according to the light propagation paths of each optical path unit in this embodiment, the third long-wave 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-wave dichroic mirror 23 is mainly used to reflect the indication light with a wavelength of 660nm into the third optical path. At the same time, the third long-wave dichroic mirror 24 and the second long-wave dichroic mirror 23 cannot block the femtosecond laser with a wavelength of 1030nm, so the cut-off wavelengths of the second long-wave dichroic mirror 23 and the third long-wave dichroic mirror 24 are set as above.

[0056] In addition, since most of the visible light in the first optical path needs to be separated into the second optical path for camera imaging through the first long-wavelength pass dichroic mirror 20, and the approximate range of visible light is 380nm to 780nm, the cut-off wavelength of the first long-wavelength pass dichroic mirror 20 needs to be near the maximum wavelength of visible light.

[0057] 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 cut-off 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 go through multiple processes similar to semi-transmission and semi-reflection on the propagation path of the system, the energy that finally reaches the human eye and the camera is greatly weakened, so in this embodiment, the red light with stronger energy in the visible light is selected as the indicator light, and its specific wavelength is 660nm. Therefore, the cut-off wavelengths of the first long-wave dichroic mirror 20 and the second long-wave dichroic mirror 23 are both set to 650nm, which can avoid the damage of high-energy indicator light to the eyeball on the one hand, and ensure good visibility when the camera is imaging on the other hand.

[0058] The above are only specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto. Any changes or substitutions that can be easily thought of by a person skilled in the art within the technical scope disclosed by the present invention should be included in the protection scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the protection scope of the claims.

Claims

1. A non-coaxial multi-optical path integrated optical system, characterized in that, include: 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, a scanning lens and a first long-wave 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 rays onto the scanning galvanometer; The scanning lens is arranged on the light-emitting side of the scanning galvanometer, and is used to integrate the laser, indicator light and coherent tomography light emitted by the scanning galvanometer into the first optical path and focus them onto the target area; the wavelength transmission range of the scanning lens is a closed interval of 800nm ​​to 1100nm; The camera observation optical path unit includes a zoom camera, an annular light source and a focusing lens; The first long-wave-pass dichroic mirror is arranged in the first optical path, the first long-wave-pass dichroic mirror is located at the light exit side of the scanning lens, and the first long-wave-pass dichroic mirror 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 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 arranged on the light exit 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 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-optical path integrated optical system according to claim 1, characterized in that, The camera observation optical path unit also 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-optical-path integrated optical system according to claim 1, characterized in that, The condensing lens is an achromatic lens.

4. A non-coaxial multi-optical path integrated optical system according to claim 1, wherein 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-optical-path integrated optical system according to claim 4, characterized in that The indicator light optical 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 mutually parallel light beams; the beam expander is used to expand the diameter of each light beam; and the second long-wave pass dichroic mirror is used to reflect the two expanded light beams to the scanning galvanometer.

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

7. An off-axis multi-optical path integrated optical system according to claim 6, characterized in that, The laser optical path unit comprises: 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 is incident on the scanning galvanometer.

8. The non-coaxial multi-optical-path integrated optical system according to claim 7, characterized in that, The cut-off wavelengths of both the first long-wave pass dichroic mirror and the second long-wave pass dichroic mirror are 650 nm, and the cut-off 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; the wavelength range of the optical coherence tomography light is in the closed interval from 800 nm to 900 nm.

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

10. A non-coaxial multi-optical path integrated optical system according to claim 1, characterized in that, It further 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 the vacuum pump.

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