A three-dimensional anterior segment examination optical assembly

Abstract

The application is suitable for the field of optical inspection technology, and provides a three-dimensional anterior segment inspection optical assembly, which comprises a corneal imaging optical system and an OCT optical system. The corneal imaging optical system is used for providing a first incident light beam to a cornea and receiving a first reflected light beam reflected by the cornea. The OCT optical system is used for providing a measurement light beam and a reference light beam to an anterior segment, receiving a second reflected light beam obtained after the measurement light beam is reflected, and causing the second reflected light beam and the reference light beam to interfere and form an interference light beam. A first light splitting component is used for separating the first reflected light beam and the second reflected light beam. A first objective lens module is arranged on a side of the first light splitting component facing the anterior segment, and is used for focusing the measurement light beam to the anterior segment, so that three-dimensional imaging of the anterior segment from a surface layer to a deep layer structure can be realized.

Description

Technical Field

[0001] This application relates to the field of optical inspection technology, and in particular to a three-dimensional anterior segment inspection optical assembly. Background Technology

[0002] With the continuous advancement of technological living standards, the amount of daily eye use in today's society is increasing, leading to greater public concern about eye health. The number of ophthalmology outpatient visits and surgeries is showing a year-on-year upward trend. Simultaneously, with the rapid development of ophthalmology, the requirements for the accuracy of diagnosis and treatment of eye diseases are becoming increasingly stringent. Optical coherence tomography (OCT) and corneal topography, as mainstream examination technologies in the field of ophthalmology, each play an irreplaceable and crucial role in the diagnosis and treatment of eye diseases due to their unique technical principles and functional characteristics.

[0003] Corneal topography plays a crucial role in clinical practice for the early diagnosis of corneal astigmatism, refractive errors, and keratoconus; for contact lens-induced corneal tortuosity; for preoperative examination and postoperative efficacy evaluation of corneal refractive surgery; and for calculating the required curvature and power of contact lenses for patients with refractive errors, guiding the fitting of data lenses. Optical coherence tomography (OCT) is a non-contact ophthalmic examination method used to assess the morphology and structure of different layers of the eye. Through OCT technology, doctors can obtain morphological and structural information of the anterior, middle, and posterior layers of the cornea, thereby assessing the overall morphology and health of the cornea.

[0004] The eye has a delicate and complex structure, with the anterior segment being a crucial region encompassing core tissues such as the cornea, iris, and lens. Even minor lesions within this segment can lead to various ophthalmic diseases. Therefore, comprehensive and accurate three-dimensional examination of the anterior segment is essential for the diagnosis and treatment of ophthalmic diseases. However, traditional mainstream examination techniques have limitations when dealing with this complex region. Corneal topography focuses on analyzing the surface morphology of the cornea and cannot delve into the internal tissues. While OCT technology can provide tomographic images of intraocular tissues, it is insufficient in grasping the overall morphology of the corneal surface and its macroscopic spatial relationships with other structures. Neither of these techniques can fully present the spatial relationships and overall morphology of the various structures in the anterior segment, failing to meet the clinical need for comprehensive, high-precision examination of the anterior segment and providing sufficient data support for accurate diagnosis, personalized treatment planning, and effective monitoring of ophthalmic diseases.

[0005] Therefore, there is an urgent need for an innovative inspection system that can provide comprehensive information about the anterior segment, enabling a complete and accurate three-dimensional inspection of the anterior segment structure. Utility Model Content

[0006] The purpose of this application is to provide a three-dimensional anterior segment examination optical assembly, which aims to provide a solution that is compatible with anterior segment surface morphology and tissue depth information.

[0007] This application embodiment is implemented as follows: a three-dimensional anterior segment examination optical assembly includes:

[0008] A corneal imaging optical system for providing a first incident beam L1 to the cornea and receiving a first reflected beam L1' reflected by the cornea;

[0009] An OCT optical system is used to provide a measurement beam L2 and a reference beam L3 to the anterior segment of the eye, receive a second reflected beam L2' obtained after the measurement beam L2 is reflected, and cause the second reflected beam L2' and the reference beam L3 to interfere and form an interference beam, satisfying the interference condition: |ΔL|≤L c Where ΔL is the optical path difference between L2' and L3, L c The length of coherence;

[0010] A first beam splitter is used to separate the first reflected beam L1' and the second reflected beam L2'; and

[0011] The first objective lens module is located on the side of the first beam splitter facing the anterior segment, and is used to focus the measurement beam L2 onto the anterior segment.

[0012] In some embodiments, the corneal imaging optical system and the OCT optical system are configured as confocal, and the confocal accuracy δ≤±0.01mm, wherein the confocal accuracy is defined as the maximum deviation in three-dimensional space of the intersection point of the optical axis of the corneal imaging optical system and the optical axis of the OCT optical system. Δx, Δy, and Δz are the deviations of the intersection points in the x, y, and z axes, respectively.

[0013] In some embodiments, the transmission band of the first beam splitter is 300nm-780nm and 921nm-1000nm, and the reflection band is 785nm-920nm and 1010nm-2000nm; the number of the first beam splitter is at least one, and the first beam splitter is one or more of the following stacked combinations: high-precision multilayer dielectric film beam splitter, metal-dielectric composite film beam splitter, cubic beam splitter prism, periodic grating beam splitter element, and prism-type dispersive beam splitter.

[0014] In some embodiments, the OCT optical system includes a second light source, an optical coupler assembly, a measurement arm, a reference arm, a coupling interference assembly, and a second imaging module; the second light source is used to provide a second incident beam; the optical coupler is used to split the second incident beam into the measurement beam L2 and the reference beam L3; the measurement arm is used to guide the measurement beam L2 to the cornea and receive the second reflected beam L2'; the reference arm is used to receive and reflect the reference beam L3; the coupling interference assembly is used to receive the second reflected beam L2' and the reference beam L3, and to cause the second reflected beam L2' and the reference beam L3 to interfere within them; the second imaging module is used for imaging the interference beam.

[0015] In some embodiments, the light beam provided by the second light source is selected from at least one of broadband light beams and swept laser beams, and its center wavelength is selected from at least one wavelength in the range of 400nm-1600nm.

[0016] In some embodiments, the second incident beam has a preset spectral width, which typically satisfies 0 nm ≤ Δλ ≤ 300 nm. The spectral width is defined as the wavelength range corresponding to half the peak spectral intensity, i.e., Δλ = λ. high -λ low , λ high λ represents the wavelength at which the peak value at the longer wavelength end is half. low This is the wavelength corresponding to half the peak value at the short wavelength end.

[0017] In some embodiments, the second imaging module includes a second collimator, a second beam splitter, a second objective lens module, and a second camera arranged sequentially along the optical path of the interference beam; the second collimator is used to collimate the interference beam, the second beam splitter is used to diffract the interference beam, and the second objective lens is used to focus the diffracted light onto the second camera.

[0018] In some embodiments, the second collimator can collimate NA ≥ 0.1, and the collimated beam divergence angle ≤ 0.1mrad.

[0019] In some embodiments, the second camera is a line scan camera with a single row or multiple rows of imaging pixels, each row having at least 2048 imaging pixels, and the imaging pixel size being at least 3.5μm × 3.5μm.

[0020] In some embodiments, the second beam splitter includes a diffraction grating with a density of 1200 l / mm to 2400 l / mm; the incident surface of the second beam splitter has a certain tilt angle with the optical axis of the light emitted from the second collimator, the tilt angle being in the range of 0° to 180°, with a range error ≤ ±0.5°.

[0021] In some embodiments, the second imaging module further includes a third objective lens module disposed between the second beam splitter and the second camera. The third objective lens module is used to focus diffracted light of different wavelengths onto the second camera and to arrange the light of different wavelengths linearly on the second camera according to wavelength. The light spot formed by focusing the diffracted light beam satisfies a diameter ≤ 7 μm and the diameter of the light spot is approximately twice the size of a pixel unit.

[0022] In some embodiments, the third objective lens module includes a third cemented doublet lens, a third concave lens, a fourth cemented doublet lens, and a fifth cemented doublet lens arranged sequentially along the optical path. The focal length f1 of the third cemented doublet lens satisfies 22mm≤f1≤42mm, the focal length f2 of the third concave lens satisfies -10mm≤f2≤-30mm, the focal length of the fourth cemented doublet lens is infinite, and the focal length f3 of the fifth cemented doublet lens satisfies 140mm≤f3≤175mm. The second objective lens module is a telecentric objective lens module. The optical axis of the third objective lens module has a certain angle with the incident surface of the second beam splitter, the angle ranging from 0° to 180°, with a range error ≤±0.5°.

[0023] In some embodiments, the second light source is a highly spatially coherent light source with a beam divergence angle ≤ 0.008 mrad.

[0024] In some embodiments, the measuring arm includes a first collimator and a scanning galvanometer arranged sequentially along the optical path of the measuring beam L2. The first collimator is used to collimate the measuring beam L2 and the second reflected beam L2', and its collimation NA is ≥0.14, and the divergence angle of the collimated beam is ≤0.1mrad. The scanning galvanometer is used to control the movement of the measuring beam L2 in the scanning plane to provide the measuring beam L2 to different radial sections of the anterior segment of the eye.

[0025] In some embodiments, the scanning galvanometer is used to control the movement of the measurement beam L2 within the scanning plane, with a maximum scanning optical angle range of ±30° and a scanning linearity error ∈ ≤0.1%. Where |θ 实际 -θ 理论 | max θ represents the maximum deviation between the actual angle and the theoretical angle across the entire scanning range. 满量程 The maximum deflection angle range of the scanning galvanometer is ±20°.

[0026] In some embodiments, the reference arm includes a third collimator and a reflective assembly. The third collimator is used to collimate the reference beam L3, with a collimation NA ≥ 0.2 and a collimated beam divergence angle ≤ 0.1 mrad. The reflective assembly is used to reflect the reference beam L3 back to the third collimator. The flatness of the reflective assembly is ≤ λ / 4, where λ = 632.8 nm and the reflectivity is ≥ 98%.

[0027] In some embodiments, the reference arm includes a converging lens group with a focal length f5 satisfying 10mm≤f5≤30mm, and the converging lens group is disposed between the third collimator and the reflecting assembly.

[0028] In some embodiments, the distance and / or angle of the reflective component relative to the third collimator is adjustable, with the distance adjustment accuracy of the reflective component relative to the third collimator being ≤ ±5 μm and the angle adjustment accuracy being ≤ ±0.01°.

[0029] In some embodiments, the corneal imaging optical system includes a projection device and a first imaging module; the projection device is used to provide the first incident beam L1, and the first objective lens module is used to receive the first reflected beam L1' and focus the first reflected beam L1' onto the first imaging module.

[0030] In some embodiments, the wavelength range of the first incident beam L1 is selected from at least one of 300nm-780nm and 921nm-2000nm.

[0031] In some embodiments, the first imaging module further includes a fourth objective lens module, which is disposed on the light-incident side of the first imaging module. The fourth objective lens module is a telecentric objective lens module with a telecentricity ≤0.1°. The fourth objective lens module includes a first cemented doublet lens, a plano-convex lens, a first concave lens, a second concave lens, and a second cemented doublet lens arranged sequentially along the optical path. The focal length f1 of the first cemented doublet lens satisfies -5mm≤f1≤-25mm, the focal length f2 of the plano-convex lens satisfies 0mm≤f2≤12mm, the focal length f3 of the first concave lens satisfies 5mm≤f3≤18mm, the focal length f4 of the second concave lens satisfies 30mm≤f4≤55mm, and the focal length f5 of the second cemented doublet lens satisfies -40mm≤f5≤-64mm. The transverse chromatic aberration of the entire field of view is ≤±0.7μm.

[0032] In some embodiments, the first objective lens module is a telecentric objective lens module, the telecentricity of the first objective lens module is ≤0.1°, the focal length f and the aperture D of the first objective lens module satisfy 3mm≤f / D≤10mm, the focal length temperature drift coefficient of the first objective lens module is ≤0.01mm / ℃, and the numerical aperture NA of the first objective lens module satisfies 0.1≤NA≤0.5.

[0033] The three-dimensional anterior segment examination optical assembly provided in this application has the following advantages:

[0034] The three-dimensional anterior segment examination optical assembly provided in this application embodiment enables three-dimensional examination of the anterior segment from the surface to the deep structure, providing detailed and reliable data support for the diagnosis of ophthalmic diseases, the precise formulation of treatment plans, and the long-term monitoring of the condition, thus contributing to the improvement of ophthalmic medical standards. Attached Figure Description

[0035] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0036] Figure 1 This is a three-dimensional structural diagram of the anterior segment examination system provided in the embodiments of this application;

[0037] Figure 2 This is a side view of the three-dimensional anterior segment inspection optical assembly provided in the embodiments of this application;

[0038] Figure 3 This is a schematic diagram of the optical path structure of the three-dimensional anterior segment inspection optical assembly provided in the embodiments of this application;

[0039] Figure 4 This is an exploded view of a portion of the three-dimensional anterior segment examination optical assembly provided in the embodiments of this application;

[0040] Figure 5 This is a schematic diagram of another part of the three-dimensional anterior segment examination optical assembly provided in the embodiments of this application;

[0041] Figure 6 This is a schematic diagram of the optical path of the corneal imaging optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0042] Figure 7 This is a schematic diagram of the structure of the first imaging module of the corneal imaging optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0043] Figure 8 This is a schematic diagram of the structure of a reference arm of the OCT optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0044] Figure 9 This is another schematic diagram of the reference arm of the OCT optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0045] Figure 10 This is a schematic diagram of the structure of the second imaging module of the OCT optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0046] Figure 11 This is a schematic diagram of the optical path of the second imaging module of the OCT optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment. Figure 1 ;

[0047] Figure 12 This is a schematic diagram of the optical path of the second imaging module of the OCT optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment. Figure 2 ;

[0048] Figure 13 This is a cross-sectional structural schematic diagram of the transmission device of the corneal imaging optical system in the three-dimensional anterior segment examination optical assembly provided in this application embodiment;

[0049] Figure 14 This is another cross-sectional structural schematic diagram of the transmission device of the corneal imaging optical system in the three-dimensional anterior segment examination system provided in the embodiments of this application;

[0050] Figure 15 This is a front view of the first light source component of the corneal imaging optical system in the three-dimensional anterior segment examination system provided in this application embodiment.

[0051] The markings in the diagram mean:

[0052] 100-Three-dimensional anterior segment inspection optical assembly;

[0053] 10-Corneal Imaging Optical System;

[0054] 11-Projection device, 111-First light source assembly, 1111-First light source, 1112-Light guide, 112-Plasido disk, 1120-Center hole, 1121-Transparent area, 1122-Non-transparent area, 1123-Disk body;

[0055] 12-First imaging module, 121-Fourth objective lens module, 1211-First cemented doublet lens, 1212-Planto-convex lens, 1213-First concave lens, 1214-Second concave lens, 1215-Second cemented doublet lens, 122-First camera;

[0056] 20-OCT optical system;

[0057] 21-Second light source;

[0058] 22-Optical coupler assembly;

[0059] 23-Measuring arm, 231-First collimator, 232-Scanning galvanometer, 233-Scanning galvanometer drive assembly, 234-Measuring housing;

[0060] 24-Reference arm, 241-Third collimator, 242-Reflection assembly, 243-Converging lens group, 244-Reference housing, 245-Aperture;

[0061] 25-Coupled Interference Component;

[0062] 26-Second imaging module, 261-Second beam splitter, 262-Second camera, 263-Second collimator, 264-Third objective lens module, 2641-Third cemented doublet lens, 2642-Third concave lens, 2643-Fourth cemented doublet lens, 2644-Fifth cemented doublet lens, 265-Second objective lens module;

[0063] 30 - Data Analysis and Processing Module;

[0064] 40 - Control Module;

[0065] 50 - First beam splitter;

[0066] 60 - First objective lens module;

[0067] 70-Base, 71-Moving component, 72-Operating component;

[0068] 80 - Power module, 90 - Eyeball. Detailed Implementation

[0069] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0070] It should be noted that when a component is referred to as "fixed to" or "set on" another component, it can be directly or indirectly fixed to or set on that other component. When a component is referred to as "connected to" another component, it can be directly or indirectly connected to that other component. The terms "upper," "lower," "left," "right," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the purpose of description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this patent. The terms "first" and "second" are used only for the purpose of description and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features. "A plurality" means two or more, unless otherwise explicitly specified.

[0071] In the description of this application, unless otherwise stated, " / " indicates that the objects before and after are in an "or" relationship. For example, A / B can mean A or B. "And / or" in this application is merely a description of the relationship between the related objects, indicating that there can be three relationships. For example, A and / or B can mean: A exists alone, A and B exist simultaneously, and B exists alone. A and B can be single or multiple. Furthermore, in the description of this application, "at least one of the following" or similar expressions refer to any combination of these items, including any combination of single or multiple items. For example, at least one of a, b, and c can represent: a, b, c, a+b, a+c, b+c, a+b+c, where a, b, and c can be single or multiple. As another example, at least one of a, b, or c can represent: a, b, c, a+b, a+c, b+c, a+b+c, where a, b, and c can be single or multiple.

[0072] To illustrate the technical solutions described in this application, the following detailed description is provided in conjunction with specific drawings and embodiments.

[0073] Corneal topography technology has undergone continuous development and innovation. Early contact corneal topography instruments required the measuring head to directly contact the corneal surface to acquire data. While this provided some corneal parameters, it could cause discomfort to patients, posed a risk of corneal damage, and had limited measurement range and accuracy. To overcome the drawbacks of contact instruments, non-contact corneal topography instruments emerged, with those based on the Placido disc principle being the most widely used. This instrument projects a series of concentric rings onto the corneal surface and calculates corneal curvature, height, and other parameters based on the degree of distortion in the reflected image. It overcomes the shortcomings of contact instruments, achieving non-invasive and rapid measurements, and can more comprehensively reflect the morphological characteristics of the anterior corneal surface. It plays a crucial role in the early diagnosis of keratoconus, keenly capturing subtle changes in corneal morphology and providing a basis for early intervention.

[0074] Corneal topography devices based on the Placido disk principle typically reconstruct the entire freeform surface of the diseased cornea using a ring-shaped virtual image structured light method. This allows for the direct acquisition of 3D information, sagittal, and aberration information of the overall corneal curvature. A key element for ring-shaped virtual image structured light imaging is the need for a uniformly distributed ring light source. The virtual image of this source is then reflected by the eye's surface and captured by the sensor. Algorithms are then used to reconstruct the freeform surface of the cornea based on the spacing of the rings or the amount of ring deformation. In a normal eye, because the eye's surface has a standard radius of curvature, reflected light entering the sensor forms a uniformly distributed ring image with alternating bright and dark areas. However, when there is deformation on the eye's surface, the ring image will be distorted. The amount of deformation in the ring image can then be used to reconstruct the corneal lesion.

[0075] OCT technology can be broadly classified into two categories based on its implementation method: Time Domain OCT (TD-OCT) and Frequency Domain OCT (FD-OCT). Frequency Domain OCT can be further divided into Spectral Domain OCT (SD-OCT) and Swept Source OCT (SS-OCT) based on its own light source and inspection scheme.

[0076] TD-OCT, the earliest OCT technology, uses a mirror in a mechanical scanning reference arm to change the optical path of the reference light, thereby achieving scanning imaging at different depths of the sample. In early ophthalmological applications, TD-OCT provided doctors with preliminary tomographic images of intraocular tissues, allowing them to observe the approximate structure of tissues such as the retina. However, TD-OCT's relatively slow scanning speed and limited imaging resolution restricted its wider and more in-depth clinical application. To overcome the limitations of TD-OCT, frequency-domain OCT (FD-OCT) technology, which enables high-speed real-time imaging, emerged. Compared to SD-OCT, FD-OCT technology eliminates the limitation of a moving robotic arm. It analyzes the light intensity information after the interference of different wavelengths of laser light in the target area and performs a Fourier transform to obtain the corresponding frequency information (where the amplitude of different frequencies corresponds to the light intensity at different depths of the target location), thus enabling depth examination of the target area. In FD-OCT, SD-OCT uses a broadband low-coherence light source, uses a spectrometer to receive the spectral information of the interference light, and then performs a Fourier transform to obtain the target depth information. This technology significantly improves imaging resolution, enabling clearer visualization of retinal structures such as the retinal nerve fiber layer and the outer plexus layer. In clinical applications, SD-OCT allows doctors to diagnose retinal diseases more accurately, with substantial improvements in the accuracy and efficiency of diagnosing conditions like retinal detachment and macular holes. SS-OCT operates on a similar principle to SD-OCT, but utilizes a swept-frequency laser source that emits narrowband coherent light. This results in faster scanning of the target area and effectively reduces artifacts caused by minute movements during the scan. For patients who cannot maintain a fixed posture for extended periods, such as infants or those with certain neurological disorders, SS-OCT provides more stable and accurate images.

[0077] Please see Figures 1 to 3 As shown, this application embodiment first provides a three-dimensional anterior segment examination optical assembly 100, which includes a corneal imaging optical system 10 and an OCT optical system 20. The corneal imaging optical system 10 is used to acquire surface morphological data of the cornea in the eyeball 90, and the OCT optical system 20 is used to acquire tomographic image data of the anterior segment tissue.

[0078] The corneal imaging optical system 10 provides a first incident beam L1 to the cornea of ​​the eyeball 90 and receives a first reflected beam L1' reflected by the cornea. The OCT optical system 20 provides a second incident beam to the anterior segment of the eye, the second incident beam including a measurement beam L2 and a reference beam L3, receives the second reflected beam L2' obtained after the measurement beam L2 is reflected, and causes the second reflected beam L2' and the reference beam L3 to interfere and form an interference beam, satisfying the interference condition: |ΔL|≤L cWhere ΔL is the optical path difference between L2' and L3, L c The length of coherence.

[0079] Please see Figures 1 to 3 As shown in the embodiments of this application, the three-dimensional anterior segment examination optical assembly 100 further includes a first beam splitter 50 and a first objective lens module 60. The first beam splitter 50 is used to separate the first reflected beam L1' and the second reflected beam L2'. The first objective lens module 60 is disposed on the side of the first beam splitter 50 facing the anterior segment and is used to focus the measurement beam L2 onto the anterior segment.

[0080] The three-dimensional anterior segment examination optical assembly 100 provided in this application embodiment, combined with the functions of the corneal imaging optical system 10 and the OCT optical system 20, can obtain three-dimensional information of the anterior segment that simultaneously includes surface morphological data of the cornea and tomographic image data of the anterior segment tissue. This enables three-dimensional examination of the anterior segment from the surface to the deep structure, providing detailed and reliable data support for the diagnosis of ophthalmic diseases, the precise formulation of treatment plans, and the long-term monitoring of the condition, thus contributing to the improvement of ophthalmic medical standards.

[0081] Please see Figures 1 to 3 As shown in some embodiments of this application, the three-dimensional anterior segment examination optical assembly 100 further includes a data analysis and processing module 30. The data analysis and processing module 30 is communicatively connected to the corneal imaging optical system 10 and the OCT optical system 20, respectively, and is used to acquire corneal surface morphology data and anterior segment tissue tomographic image data, and process the corneal surface morphology data and anterior segment tissue tomographic image data to obtain three-dimensional information of the anterior segment.

[0082] In some optional embodiments, the data analysis and processing module 30 performs three-dimensional reconstruction of the corneal surface morphology data and the tomographic image data of the anterior segment tissue. Optionally, the data analysis and processing module 30 reconstructs the corneal surface morphology data and the tomographic image data of the anterior segment tissue in the same coordinate system, so that the information of each point of the cornea corresponds to the information of each point on the surface of the anterior segment, thereby obtaining three-dimensional information of the corresponding anterior segment surface and deep tissues.

[0083] In some embodiments of this application, such as Figure 3 , Figure 4 and Figure 6 As shown, the corneal imaging optical system 10 is used to project a first incident beam L1 onto the cornea and to receive a first reflected beam L1' reflected by the cornea. By analyzing the deformation of the first reflected beam L1' relative to the first incident beam L1, the corneal imaging optical system 10 can calculate the surface morphology data of the cornea, including parameters such as curvature and height at various points on the corneal surface.

[0084] In some embodiments of this application, such as Figure 3 , Figure 4 and Figure 11 As shown, the OCT optical system 20 projects a measurement beam L2 and a reference beam L3 onto the anterior segment. The measurement beam is configured to penetrate the anterior segment tissue to a certain depth and performs three-dimensional scanning of the anterior segment tissue at different angles. The returned second reflected beam L2' carries anterior segment depth information. By analyzing the second reflected beam L2', the OCT optical system 20 can calculate the depth information of the anterior segment at different angles.

[0085] In some embodiments, the corneal imaging optical system 10 and the OCT optical system 20 are configured to be confocal, with a confocal accuracy δ ≤ ±0.5 mm, so that the three-dimensional anterior segment examination optical assembly 100 can achieve optimal performance. The confocal accuracy is defined as the maximum deviation in three-dimensional space of the intersection point of the optical axes of the corneal imaging optical system 10 and the OCT optical system 20. Δx, Δy, and Δz are the deviations of the intersection points of the two optical axes in the x, y, and z axes, respectively.

[0086] The z-axis is parallel to the optical axis. The x-axis and y-axis are perpendicular to each other and both perpendicular to the z-axis.

[0087] The corneal imaging optical system 10 and the OCT optical system 20 are confocal, which enables the surface morphology data of the cornea and the tomographic image data of the anterior segment tissue to be imaged with the same focal point. In this way, the surface morphology data of the cornea and the tomographic image data of the anterior segment tissue in the obtained three-dimensional information of the anterior segment have the same coordinate point, and the surface morphology data of the cornea and the tomographic image data of the anterior segment tissue can be combined into one.

[0088] The first incident beam L1 and the first reflected beam L1' have the same wavelength. The measuring beam L2 and the second reflected beam L2' have the same wavelength. The first incident beam L1 and the measuring beam L2 have different wavelengths. Thus, light rays of different wavelengths can be separated or combined by the first beam splitter 50.

[0089] In some embodiments of this application, the first incident beam L1 and the first reflected beam L1' are visible light. The measuring beam L2 and the second reflected beam L2' are infrared light.

[0090] In some embodiments of this application, the wavelength range of the first incident beam L1 and the first reflected beam L1' is 400 nm to 780 nm. The wavelength range of the measurement beam L2 and the second reflected beam L2' is greater than or equal to 780 nm, such as 780 nm to 2500 nm.

[0091] In some alternative embodiments, the wavelength range of the first incident beam L1 and the first reflected beam L1' is 630nm to 780nm.

[0092] The wavelength range of the measuring beam L2 and the second reflected beam L2' is 780 nm to 900 nm, and / or 1310 ± 100 nm. For example, the wavelength range of the measuring beam L2 and the second reflected beam L2' is 780 nm to 900 nm, or the wavelength range of the measuring beam L2 and the second reflected beam L2' is 1310 ± 100 nm, or both the measuring beam L2 and the second reflected beam L2' can simultaneously contain light in the range of 780 nm to 900 nm and light in the range of 1310 ± 100 nm.

[0093] In some specific embodiments, the wavelengths of the first incident beam L1 and the first reflected beam L1' can be 650nm, 680nm, 740nm, etc. In some specific embodiments, the wavelengths of the measurement beam L2 and the second reflected beam L2' can include one or more of the following: 780nm, 800nm, 820nm, 840nm, 860nm, 880nm, 900nm, 1210nm, 1260nm, 1310nm, 1360nm, and 1410nm.

[0094] In some embodiments of this application, the transmission band of the first beam splitter 50 is 300nm-780nm and 921nm-1000nm, and the reflection band is 785nm-920nm and 1010nm-2000nm.

[0095] The first incident beam L1 and the first reflected beam L1' can be projected onto the first beam splitter 50, and the measurement beam L2 and the second reflected beam L2' can be reflected by the first beam splitter 50.

[0096] In some embodiments, the number of first beam-splitting components 50 is at least one.

[0097] In some embodiments, the first beam splitting component 50 is a stacked combination of one or more of the following: a high-precision multilayer dielectric film beam splitter, a metal-dielectric composite film beam splitter, a cubic beam splitting prism, a periodic grating beam splitting element, and a prism-type dispersive beam splitter.

[0098] When the first beam splitter is used for 50 beams, the total light loss is η≤0.5%, where the light loss is defined as... In the formula, T 有效 R represents the actual transmittance of the first beam splitter 50 to the first reflected beam L1'. 有效 The actual reflectivity of the first beam splitter 50 for measuring beam L2 and the second reflected beam L2'. The power of the first reflected beam L1' incident on the first beam splitter 50. The total power of the measurement beam L2 incident on the first beam splitter 50 and the second reflected beam L2' is given.

[0099] In some embodiments of this application, such as Figure 3 , Figure 4 and Figure 6 As shown, the first beam-splitting assembly 50 includes a beam splitter. The surface of the beam splitter is tilted along the axial direction of the anterior segment to deflect the measurement beam L2 and the second reflected beam L2' relative to the axial direction of the anterior segment, so that the paths of the measurement beam L2 and the second reflected beam L2' are adapted to the positions of the anterior segment and the OCT optical system 20.

[0100] In some embodiments of this application, the angle between the surface of the beam splitter and the axis of the anterior segment is 45°. This causes the paths of the measurement beam L2 and the second reflected beam L2' to be deflected by 90°.

[0101] In some alternative embodiments, a bandpass antireflection-high reflectance coating (not shown) is provided on the surface of the beam splitter facing the anterior segment to increase the transmittance of the first reflected beam L1' and to improve the reflectance of the measurement beam L2 and the second reflected beam L2'. The antireflection band of the bandpass antireflection-high reflectance coating covers the wavelengths of the first incident beam L1 and the first reflected beam L1', while the reflection band of the bandpass antireflection-high reflectance coating covers the wavelengths of the measurement beam L2 and the second reflected beam L2'.

[0102] In some alternative embodiments, an antireflection coating (not shown) is provided on the surface of the beam splitter facing the anterior segment to increase the transmittance of the first reflected beam L1'. The antireflection band of the antireflection coating covers the bands of the first incident beam L1 and the first reflected beam L1'.

[0103] In some embodiments of this application, such as Figure 3 , Figure 4 and Figure 6 As shown, the first objective lens module 60 is a telecentric objective lens module. The first objective lens module 60 is disposed on the side of the first beam splitter 50 facing the anterior segment; the first objective lens module 60 is used to transmit a first reflected beam, a second incident beam, and a second reflected beam, and to perform wavefront modulation on the first reflected beam, the second incident beam, and the second reflected beam, including collimating the first reflected beam and the second reflected beam, and focusing the second incident beam onto the surface of the anterior segment.

[0104] By setting a telecentric objective lens module on the side of the first beam splitter 50 facing the anterior segment, the measurement beam can be incident on the anterior segment and focused on its surface, and the first and second reflected beams can exit from the anterior segment in a manner that is parallel to each other and both parallel to the axis of the anterior segment. This allows the corneal imaging optical system 10 and the OCT optical system 20 to achieve confocality, with the first and second reflected beams jointly focused at the corresponding central vertex of the cornea. Furthermore, this ensures that the vertices of the 3D curved surface image of the cornea output by the corneal imaging optical system 10 coincide exactly with the surface contour vertices of the 3D anterior segment image output by the OCT optical system 20. Thus, 3D information of the anterior segment is obtained, simultaneously containing surface morphological data of the cornea and tomographic image data of the anterior segment tissue.

[0105] In this embodiment, by setting a telecentric objective lens module on the side of the first beam-splitting component 50 facing the anterior segment, the light reflected from the cornea of ​​the eyeball 90 (including the first reflected beam and the second reflected beam) is parallel light. This parallel light includes multiple sets of light rays corresponding to different regions of the cornea, and the angle between the principal ray in each set and the optical axis of the corneal imaging optical system 10 is less than or equal to 0.5°.

[0106] In this embodiment, the reflection of light on the cornea is specular reflection.

[0107] By setting a telecentric objective module on the side of the first beam splitter 50 facing the anterior segment, the imaging deviation and error of the corneal imaging optical system 10 are not caused by the human eye's positioning error in the anterior-posterior direction when examining the anterior segment and cornea, thus obtaining a more accurate image. Therefore, this eliminates the influence of the anterior-posterior positioning error of the human eye on the corneal imaging result.

[0108] In some embodiments, the telecentricity of the first objective lens module 60 is ≤0.1°, the focal length f of the first objective lens module 60 and its aperture D satisfy 3mm≤f / D≤10mm, the focal length temperature drift coefficient of the first objective lens module 60 is ≤0.01mm / ℃, and the numerical aperture NA of the first objective lens module 60 satisfies 0.1≤NA≤0.5.

[0109] like Figure 6 As shown, in some embodiments of this application, the first objective lens module 60 is a cemented doublet lens. An anti-reflection coating is provided on the incident surface, the emitting surface, and the cemented surface of the cemented doublet lens. The anti-reflection band of the anti-reflection coating includes the bands of the first incident beam and the measurement beam.

[0110] The table below shows the parameters of the first objective lens module 60.

[0111]

[0112] In some embodiments of this application, such as Figure 3 and Figure 5 As shown, the three-dimensional anterior segment examination optical assembly 100 also includes a control module 40, which is connected to the corneal imaging optical system 10, the OCT optical system 20 and the data analysis and processing module 30 respectively. The control module 40 is used to control the corneal imaging optical system 10 and the OCT optical system 20, and to transmit the surface morphology of the cornea and the tomographic image data of the anterior segment tissue to the data analysis and processing module 30.

[0113] In some embodiments of this application, such as Figure 3 , Figure 4 and Figure 6 As shown, the corneal imaging optical system 10 includes a projection device 11 and a first imaging module 12; the projection device 11 is used to provide a first incident beam L1 to the cornea, and the first objective lens module 60 is used to receive a first reflected beam L1' and focus the first reflected beam L1' onto the first imaging module 12.

[0114] In some embodiments of this application, the first incident beam is a black-and-white concentric ring-shaped virtual image structured light. The first reflected beam is a black-and-white ring-shaped virtual image structured light obtained after the black-and-white concentric ring-shaped virtual image structured light is reflected. When there is deformation of the cornea, the image obtained in the first imaging module 12 will produce local distortion. For example, when the cornea flattens (curvature decreases, corresponding to farsightedness), the spacing between the black-and-white ring stripes in the image will increase; when the cornea becomes convex (curvature increases, corresponding to nearsightedness), the spacing between the black-and-white ring stripes in the image will decrease; when the curvature of the cornea on the X-axis and Y-axis is different (astigmatism), the spacing between the black-and-white ring stripes in the image will be uneven in the X and Y directions, and the image will show elliptical ring stripes. The X-axis and Y-axis are perpendicular to each other and perpendicular to the axis of the anterior segment.

[0115] In some embodiments of this application, the projection device 11 includes a placid disk 112 and a first light source assembly 111, such as Figure 14 and Figure 15 As shown, the first light source assembly 111 includes a plurality of first light sources 1111. Each first light source 1111 is used to emit a first-band beam. The first light sources 1111 are distributed on the light-incident side of the plassiding disk 112, that is, the side of the plassiding disk 112 opposite to the anterior segment. The light emitted from each first light source 1111 enters the plassiding disk 112 and exits from the side surface of the plassiding disk 112 toward the anterior segment.

[0116] like Figure 1 and Figure 14As shown, the Placido disk 112 has multiple light-transmitting areas 1121 and non-light-transmitting areas 1122 arranged in concentric rings. The first-band beam emitted by the first light source 1111 passes through the Placido disk 112 and is transmitted to the anterior segment of the eye. After passing through the light-transmitting areas 1121 and non-light-transmitting areas 1122, it forms a black and white concentric striped structured light.

[0117] In one embodiment, each of the first light sources 1111 is distributed radially and circumferentially along the plassid disk 112, thereby forming a relatively uniform surface light source on the side of the plassid disk 112 away from the anterior segment of the eye. The light is further diffused and homogenized within the plassid disk 112, thereby obtaining uniform black and white concentric striped structured light from the light-emitting surface of the plassid disk 112.

[0118] The formation of the light-transmitting area 1121 and the non-light-transmitting area 1122 of the Plassido disc 112 is not limited. For example, as Figure 15 As shown, the non-transparent area 1122 can be formed by providing a non-transparent coating on the light-emitting surface of the Placid disk 112. The non-transparent coating can be a black paint layer, etc.

[0119] In some embodiments, the plassid disk 112 may be doped with scattering particles to further increase the uniformity of light within the plassid disk 112. The scattering particles may include one or more of titanium dioxide particles, zirconium dioxide particles, barium sulfate particles, etc.

[0120] like Figure 14 and Figure 15 As shown, the first light source assembly 111 also includes a circuit board 114, with each first light source 1111 disposed on the side of the circuit board 114 facing the plascidos disk 112. Each first light source 1111 is spaced apart from the plascidos disk 112, forming a mixing cavity 115 between them. This allows the light from each first light source 1111 to be mixed and homogenized within the mixing cavity 115, thereby further homogenizing the light within and emanating from the plascidos disk 112.

[0121] In some embodiments of this application, such as Figure 13 As shown, the first light source assembly 111 of the projection device 11 includes not only a plurality of first light sources 1111, but also a light guide 1112, with each first light source 1111 disposed on the light-incident side of the light guide 1112. The light-emitting surface of the light guide 1112 is disposed on the light-incident side of the plassiding disk 112, and the light guide 1112 is used to guide the first incident light beam to the plassiding disk 112. By guiding the first wavelength light beam emitted by each first light source 1111 through the light guide 1112, a uniform surface light source is obtained on the light-emitting side of the plassiding disk 112, and the light is uniformly incident on the cornea.

[0122] In this embodiment, each first light source 1111 can be distributed radially and circumferentially along the plassiding disk 112 and the light guide 1112, or it can be correspondingly disposed at the radial edge of the plassiding disk 112 and the light guide 1112. For example... Figure 13 As shown, each first light source 1111 and circuit board 114 are disposed at the radial outer edge of light guide 1112. The light from each first light source 111 enters the light guide 1112 through the radial outer edge of light guide 1112 and is dispersed radially and circumferentially within the light guide 1112. A surface light source is obtained on the side of light guide 1112 facing the plassid disk 112. After being homogenized by plassid disk 112, a black and white concentric stripe structured light is obtained.

[0123] The type of the first light source 1111 is not limited. For example, it can be a light-emitting diode, an organic light-emitting diode, or a laser source, or a combination of multiple types of light-emitting diodes, organic light-emitting diodes, and laser sources. The laser source may include at least one of a vertical-cavity surface-emitting laser and an edge-emitting semiconductor laser.

[0124] like Figure 1 As shown, the Plassid disk 112 has a through-hole 1120. The through-hole 1120 is used for the first reflected beam L1', the measuring beam L2, and the second reflected beam L2' to pass through.

[0125] During the use of the three-dimensional anterior segment examination optical assembly 100, the plassid disc 112 is configured such that the central axis of its central hole 1120 is parallel to the axial direction of the anterior segment.

[0126] In some embodiments of this application, the light guide 1112 is in the form of a closed ring and is disposed on the light-incident surface side of the Placido disk 112. The closed-ring light guide 1112 can disperse the light from the first light source 1111 along the radial and circumferential directions, so that the light is diffused and dispersed to the entire area of ​​the Placido disk 112, thereby obtaining uniform black and white striped structured light on the light-emitting surface side of the Placido disk 112.

[0127] The wavelength range of the first incident beam L1 is selected from at least one of 300nm-780nm and 921nm-2000nm.

[0128] In some embodiments of this application, such as Figure 4 , Figure 6 and Figure 7As shown, the first imaging module 12 includes a first camera 122. The first camera 122 is an area scan camera. Optionally, the area scan camera has more than 5 million pixels. In some specific embodiments, the area scan camera may be a CMOS (Complementary Metal-Oxide-Semiconductor) camera or a CCD (Charge Coupled Device) camera.

[0129] like Figure 6 As shown, in some embodiments of this application, the second reflected beam is perpendicular to or close to the target surface of the vertical area array camera. In some optional embodiments, the second reflected beam contains multiple sets of light rays corresponding to different regions of the cornea, and the angle error between the principal ray in each set of light rays and the optical axis of the corneal imaging optical system 10 is less than or equal to 0.5.

[0130] In some embodiments of this application, such as Figure 4 , Figure 6 and Figure 7 As shown, the first imaging module 12 also includes a fourth objective lens module 121, which is located on the light-incident side of the first imaging module 12. The fourth objective lens module 121 is used to correct chromatic aberration, including the wavelength of the first incident beam.

[0131] The fourth objective lens module 121 is located on the light-incident side of the first imaging module 12, and the fourth objective lens module 121 is a telecentric objective lens module. Optionally, the telecentricity of the fourth objective lens module 121 is ≤0.1°. The purpose of this setting is that when there is an error in the focal point of the first imaging module 12, the imaging of the black and white ring virtual image structured light will not be distorted, and the surface topography of the cornea can be accurately obtained.

[0132] In some embodiments of this application, such as Figure 7 As shown, the fourth objective lens module 121 includes a first cemented doublet 1211, a plano-convex lens 1212, a first concave lens 1213, a second concave lens 1214, and a second cemented doublet 1215 arranged sequentially along the optical path. The focal length f1 of the first cemented doublet 1211 satisfies -5mm≤f1≤-25mm, the focal length f2 of the plano-convex lens 1212 satisfies 0mm≤f2≤12mm, the focal length f3 of the first concave lens 1213 satisfies 5mm≤f3≤18mm, the focal length f4 of the second concave lens 1214 satisfies 30mm≤f4≤55mm, and the focal length f5 of the second cemented doublet 1215 satisfies -40mm≤f5≤-64mm. This satisfies the requirement that the achromatic range covers the wavelength range of 380nm-780nm, and the transverse chromatic aberration within this range is ≤±0.7μm across the entire field of view.

[0133] Anti-reflective coatings are provided on the incident and exit surfaces of the first cemented doublet 1211, the plano-convex lens 1212, the first concave lens 1213, the second concave lens 1214, and the second cemented doublet 1215, as well as on the cemented surfaces of the first cemented doublet 1211 and the second cemented doublet 1215. The anti-reflective band of these coatings includes at least the bands of the first incident beam L1 and the first reflected beam L1'. For example... Figure 3 As shown, in some embodiments of this application, the OCT optical system 20 includes a second light source 21, which provides a second-band beam as a second incident beam. The OCT optical system 20 also includes an optical coupler assembly 22, a measurement arm 23, a reference arm 24, a coupling interference assembly 25, and a second imaging module 26. The optical coupler assembly 22 is used to split the second incident beam into a measurement beam L2 and a reference beam L3. The measurement arm 24 is used to guide the measurement beam L2 to the cornea and receive the second reflected beam L2'. The reference arm 24 is used to receive and reflect the reference beam L3. The coupling interference assembly 25 is used to receive the second reflected beam L2' and the reference beam L3 and cause the second reflected beam L2' and the reference beam L3 to interfere within it. The second imaging module 26 is used for interferometric beam imaging.

[0134] The beam provided by the second light source 21 is selected from at least one of broadband beams and swept laser beams. The center wavelength of the beam provided by the second light source 21 is selected from at least one wavelength in the range of 400nm to 1600nm.

[0135] The second reflected beam is reflected back from the anterior segment of the eye, and the second reflected beam carries multi-angle depth information of the anterior segment of the eye.

[0136] In some embodiments, the second incident beam is a broadband beam with a center wavelength of 840 nm, and / or the second incident beam is a broadband beam with a center wavelength of 1310 nm.

[0137] In some embodiments, the second incident beam has a preset spectral width, which typically satisfies: 0 nm ≤ Δλ ≤ 300 nm, where the spectral width is defined as the wavelength range corresponding to half the peak spectral intensity, i.e., Δλ = λ high -λ low , λ high λ represents the wavelength at which the peak value at the longer wavelength end is half. low This is the wavelength corresponding to half the peak value at the short wavelength end.

[0138] In some alternative embodiments, the spectral width of the second incident beam is 50 nm to 250 nm.

[0139] Further optionally, the spectral width of the second incident beam is 75nm to 200nm. In some specific embodiments, the spectral width of the second incident beam is 10nm, 30nm, 50nm, 70nm, 75nm, 100nm, 150nm, 200nm, 250nm, 300nm, etc.

[0140] In some embodiments of this application, the optical coupler assembly 22 may include a first fiber optic splitter. The first fiber optic splitter includes a 1×2 splitting fiber. After the second incident beam is incident on the first fiber optic splitter, it is split into two. One part of the light beam serves as the first incident beam and enters the measurement arm 23, while the other part of the light beam serves as the reference beam and enters the reference arm 24.

[0141] The splitting ratio of the fiber optic beam splitter can be set as needed, as long as the second reflected beam and the reference beam can interfere. In some embodiments, the splitting ratio of the fiber optic beam splitter is 1%-99% to 99%-1%. In some optional embodiments, the splitting ratio of the fiber optic beam splitter is 10%-90% to 90%-10%. In some optional embodiments, the splitting ratio of the fiber optic beam splitter is 20%-80% to 80%-20%. In some optional embodiments, the splitting ratio of the fiber optic beam splitter is 30%-70% to 70%-30%. In some optional embodiments, the splitting ratio of the fiber optic beam splitter is 40%-60% to 60%-40%. In some optional embodiments, the splitting ratio of the fiber optic beam splitter is 50%-50%.

[0142] In some embodiments of this application, the coupling interference component 25 includes a second fiber optic splitter, which includes a 1×2 splitting fiber. The second reflected beam and the reflected reference beam are combined and interfere within the 1×2 splitting fiber.

[0143] In some embodiments, a beam splitting interference component is constituted by at least a coupling interference component 25 and an optical coupler component 22. The beam splitting interference component includes a 2×2 beam splitting fiber, which splits the second incident beam into a measurement beam and a reference beam in the exit direction of the second incident beam, and combines the second reflected beam and the reference beam in the propagation direction of the second reflected beam.

[0144] In some embodiments of this application, such as Figure 3 As shown, the second light source 21 is used to emit a second incident light beam. That is, the first collimator 231 is used to ensure that the second incident light beam is incident on the cornea in a parallel manner. The second reflected light beam is parallel light, and the reference light beam is parallel light.

[0145] In some alternative embodiments, the second light source 21 is a broadband light source. In some embodiments, the second light source 21 includes a superluminescent diode. A superluminescent diode (SLD) is a photoelectric semiconductor device that generates broadband light using the superluminescent emission phenomenon of semiconductors.

[0146] In some alternative embodiments, the second light source 21 is a highly spatially coherent light source. For example, the second light source 21 provides highly coherent near-infrared light, providing sufficient penetration depth and resolution for anterior segment tissue imaging.

[0147] In some embodiments of this application, such as Figure 3 As shown, the measuring arm 23 includes a first collimator 231 and a scanning galvanometer 232 arranged sequentially along the optical path of the measuring beam. The first collimator 231 is used to collimate the measuring beam L2 and the second reflected beam L2', such that the measuring beam L2 is incident on the anterior segment of the eye in a parallel manner, and that the second reflected beam is incident on the second imaging module 26 in a parallel manner. The scanning galvanometer 232 is used to control the movement of the measuring beam within the scanning plane (XY plane) to provide the second beam to multiple different radial sections of the anterior segment of the eye.

[0148] In some embodiments, the first collimator 231 is used for collimable NA ≥ 0.14, and the divergence angle of the collimated beam is ≤ 0.1mrad.

[0149] In some alternative embodiments, the scanning galvanometer 232 is configured to move in mutually perpendicular X and Y directions. Specifically, the scanning galvanometer 232 moves along one radial direction of the anterior segment of the anterior segment, so that the measurement beam is sequentially provided to multiple points along that radial direction, thus obtaining multi-point depth information corresponding to one radial cross-section on the side of the second imaging module 26; controlling the scanning galvanometer 232 to rotate through a certain angle and controlling the scanning galvanometer 232 to move along another radial direction of the anterior segment of the anterior segment, so that the measurement beam is sequentially provided to multiple points along that radial direction, thus obtaining multi-point depth information corresponding to the other radial cross-section on the side of the second imaging module 26. This process continues, allowing the acquisition of depth information for multiple different radial cross-sections of the anterior segment of the anterior segment.

[0150] In some optional embodiments, the scanning galvanometer 232 is used to control the movement of the measurement beam L2 within the scanning plane, with a maximum scanning optical angle range of ±30° and a scanning linearity error ∈ ≤0.1%. Where, |θ 实际 -θ 理论 | max θ represents the maximum deviation between the actual angle and the theoretical angle across the entire scanning range. 满量程 The maximum deflection angle range of the scanning galvanometer 232 is ±20°.

[0151] In some embodiments of this application, such as Figure 3 As shown, the measuring arm 23 also includes a measuring housing 234, which is a hollow structure with openings at both ends. The scanning galvanometer 232 and the first collimator 231 are located inside the measuring housing 234.

[0152] In some embodiments of this application, such as Figure 3 As shown, the measuring arm 23 has a measuring optical path from its light-emitting end to the center vertex of the anterior segment, and the reference arm 24 has a reference optical path. The difference between the measuring optical path and the reference optical path is within the coherence length range; the coherence length satisfies the following formula:

[0153] L = n*λ^2 / Δλ;

[0154] Where L is the coherence length, n is the refractive index of air, λ is the center wavelength of the second incident beam, and Δλ is the full width at half maximum (FWHM) of the second incident beam.

[0155] The measuring optical path of measuring arm 23 refers to the optical distance from the center apex of the eyeball 90 to the first collimator 231. The reference optical path of reference arm 24 refers to the unidirectional optical path length of the reference beam within reference arm 24.

[0156] In some embodiments of this application, such as Figure 10 , Figure 11 and Figure 12 As shown, the second imaging module 26 includes a second beam splitter 261 and a second camera 262 arranged sequentially along the optical path of the interference beam. The second incident beam is a broadband beam. The second beam splitter 261 is used to diffract and split beams of different wavelengths, so that beams of different wavelengths are imaged at different positions of the second imaging module 26, thereby obtaining information on the depths of the anterior segment.

[0157] The second beam-splitting component 261 may include one or more of a reflection grating, a projection grating, a diffraction grating, and a beam-splitting prism.

[0158] In some embodiments, the second beam splitter 261 may include a diffraction grating for diffracting incident light to separate light of different wavelengths.

[0159] In some embodiments, the density of the second beam-splitting component 261 is 1200 l / mm to 2400 l / mm. In some optional embodiments, the density of the second beam-splitting component 261 is 1500 l / mm to 2100 l / mm. In some specific embodiments, the density of the second beam-splitting component 261 is 1200 l / mm, 1500 l / mm, 1800 l / mm, 2100 l / mm, or 2400 l / mm.

[0160] In some embodiments of this application, such as Figure 11 and Figure 12 As shown, the second beam-splitting component 261 is a polarizing holographic grating. The diffracted beam obtained by the interference beam incident on the second beam-splitting component 261 is deflected relative to the interference beam. Furthermore, this arrangement aims to deflect the diffracted beam relative to the incident beam, which facilitates the placement of the second imaging module 26 within the entire OCT optical system 20, specifically its placement relative to the measurement arm 23 and the coupling interference component 25, resulting in a compact and small-sized OCT optical system 20.

[0161] In some embodiments of this application, such as Figure 10 As shown, the second imaging module 26 further includes a second collimator 263 disposed upstream of the second beam splitter 261 along the optical path of the interference beam; the second collimator 263 is used to collimate the interference beam, so that the interference beam is incident on the second beam splitter 261 in the form of a collimated beam. Optionally, the second collimator 263 is used to collimate the interference beam, and its collimation NA is ≥0.1, and the divergence angle of the collimated beam is ≤0.1mrad. The incident surface of the second beam splitter 261 and the optical axis of the light emitted from the second collimator 263 have a certain tilt angle, the tilt angle being in the range of 0° to 180°, with a range error ≤±0.5°.

[0162] In some embodiments of this application, the second camera 262 is a line scan camera, which has a single row or multiple rows of imaging pixels.

[0163] In some embodiments, the number of imaging pixels in each row of the line scan camera is at least 2048. This is intended to provide the second camera 262 with high resolution, enabling it to obtain high-resolution three-dimensional information of the anterior segment. In some alternative embodiments, the number of imaging pixels in each row of the line scan camera is at least 2048, and the pixel size is at least 3.5 μm × 3.5 μm.

[0164] In some embodiments of this application, such as Figure 10 As shown, the second imaging module 26 also includes a second objective lens module 265, which is disposed between the second beam splitter 261 and the second collimator 263. The second objective lens module 265 is a telecentric objective lens module. The purpose of this arrangement is to further collimate the diffracted beam, ensuring that the diffracted beam is incident on the second beam splitter 261 as parallel light, such as... Figure 11 As shown. In some embodiments, the second objective lens module 265 includes two spaced-apart lenses.

[0165] The table below shows the parameters of the second objective module 265.

[0166]

[0167]

[0168] In some embodiments of this application, such as Figure 10 As shown, the second imaging module 26 also includes a third objective lens module 264 disposed between the second beam splitter 261 and the second camera 262. The third objective lens module 264 is a telecentric objective lens module. The purpose of this arrangement is that the third objective lens module 264 is used to focus diffracted light of different wavelengths onto the second camera 262, so that the light of different wavelengths is linearly arranged according to wavelength on the second camera 262.

[0169] The light spot formed by focusing the diffracted beam satisfies a diameter ≤ 7 μm, and the diameter of the light spot is approximately twice the size of a pixel unit.

[0170] In this embodiment, the diffracted beam includes multiple sets of light rays corresponding to different regions of the anterior segment of the eye. Through the third objective lens module 264, the principal ray in each set of light rays in the diffracted beam is incident on the second camera 262 in a perpendicular or substantially perpendicular manner. Optionally, the angle between the principal ray in each set of light rays in the diffracted beam and the optical axis of the second imaging module 26 is less than or equal to 0.5°.

[0171] In some alternative embodiments, the optical axis of the third objective lens module 264 coincides with the diffracted beam at the center wavelength position of the second beam splitter 261. In some alternative embodiments, the center wavelength of the second beam splitter 261 is 840 nm.

[0172] In some embodiments of this application, such as Figure 10 As shown, the third objective lens module 264 includes a third cemented doublet lens 2641, a third concave lens 2642, a fourth cemented doublet lens 2643, and a fifth cemented doublet lens 2644 arranged sequentially along the optical path.

[0173] The focal length f1 of the third cemented doublet 2641 satisfies 22mm≤f1≤42mm, the focal length f2 of the third concave lens 2642 satisfies -10mm≤f2≤-30mm, the focal length of the fourth cemented doublet 2643 is infinite, and the focal length f3 of the fifth cemented doublet 2644 satisfies 140mm≤f3≤175mm.

[0174] The third objective module 264 is a telecentric objective module. The optical axis of the third objective module 264 and the incident surface of the second beam splitter 261 have a certain angle, ranging from 0° to 180°, with a range error of ≤ ±0.5°.

[0175] Optionally, an anti-reflection coating is provided on the light-incident and light-out surfaces of the third cemented doublet lens 2641, the third concave lens 2642, the fourth cemented doublet lens 2643, and the fifth cemented doublet lens 2644, as well as on the cementing surface of the third cemented doublet lens 2641, the fourth cemented doublet lens 2643, and the fifth cemented doublet lens 2644. The anti-reflection band of the anti-reflection coating corresponds to the band of the second incident beam.

[0176] The table below shows the parameters of the third objective module 264.

[0177]

[0178]

[0179] like Figure 10 As shown, in some embodiments, the angle between the light-incident surface of the second beam-splitting component 261 and the horizontal direction (optical axis of the third objective lens module 264) is α, and the value of α ranges from 139.1° ± 0.5°. Figure 10 As shown, in some embodiments, the angle between the optical axis of the third objective module 264 and the vertical direction is β, and the value of β ranges from 8.23°±0.5°.

[0180] In some embodiments of this application, such as Figure 3 , Figure 8 and Figure 9 As shown, the reference arm 24 includes a third collimator 241 and a reflector 242. The third collimator 241 is used to further collimate the reference beam L3 from the optical coupler assembly 22, and the reflector 242 is used to reflect the reference beam L3 back to the third collimator 241. The reference beam L3 is incident on the reflector 242 as parallel light and is reflected perpendicularly, and is still incident on the second imaging module 26 as parallel light.

[0181] Here, the reference optical path of reference arm 24 refers to the optical distance between the third collimator 241 and the reflective component 242.

[0182] The reflective component 242 may specifically include a reflector.

[0183] In some embodiments, the third collimator 241 can collimate a beam with an NA ≥ 0.2, and the divergence angle of the collimated beam is ≤ 0.1 mrad. The flatness of the reflective component 242 is ≤ λ / 4, where λ = 632.8 nm, and the reflectivity is ≥ 98%.

[0184] In some embodiments of this application, such as Figure 3 and Figure 9As shown, the reference arm 24 also includes a converging lens group 243, which is disposed between the third collimator 241 and the reflecting assembly 242. The converging lens group 243 is used to narrow the range of the reference beam and further converge and collimate the diverging reference beam.

[0185] In some embodiments of this application, the distance between the reflecting component 242 and the third collimator 241 is adjustable. This is intended to ensure that by adjusting the reflecting component 242 along the direction of the reference beam, a suitable reference optical path can be achieved within the reference arm 24, guaranteeing that the reference beam can interfere with the measurement beam. Furthermore, by adjusting the reflecting component 242 along the direction of the reference beam, the reflected reference beam can also have a suitable range.

[0186] In some embodiments of this application, the angle of the reflecting component 242 relative to the third collimator 241 is adjustable. The third collimator 241 is fixedly disposed within the reference arm 24; therefore, it can be said that the tilt angle of the reflecting component 242 relative to the optical axis of the reference arm 24 is adjustable. The purpose of this arrangement is to further collimate the reflected reference beam by adjusting the tilt angle of the reflecting component 242. For example, when there are manufacturing or installation deviations in the third collimator 241, the reference beam can be further collimated by adjusting the angle of the reflecting component 242.

[0187] In some embodiments, the distance adjustment accuracy of the reflective component 242 relative to the third collimator 241 is ≤ ±5 μm, and the angle adjustment accuracy is ≤ ±0.01°.

[0188] In some embodiments of this application, such as Figure 3 , Figure 8 and Figure 9 As shown, the reference arm 24 also includes an aperture 245, which is disposed between the third collimator 241 and the converging lens group 243. The aperture of the aperture 245 is adjustable to adjust the luminous flux of the reference beam entering the converging lens group 243, so that the reference beam, after being reflected, interferes with the second reflected beam with a suitable luminous flux, ensuring the accuracy and high resolution of the interference beam imaging. For example, when there are manufacturing errors in the optical coupler assembly 22, resulting in a difference between the beam splitting ratio and the predetermined beam splitting ratio, the aperture 245 can be adjusted to achieve interference between the reference beam and the second reflected beam with a suitable luminous flux.

[0189] like Figure 3 , Figure 8 and Figure 9As shown, in some embodiments of this application, the reference arm 24 further includes a reference housing 244, a third collimator 241 fixedly disposed at one end opening of the reference housing 244, and an aperture stop 245, a converging lens group 243, and a reflecting assembly 242 all disposed within the reference housing 244. Furthermore, in some embodiments of this application, such as... Figure 5 As shown, the reference arm 24 also includes a scanning galvanometer drive assembly 233, which is also disposed within the reference housing 244 and connected to the scanning galvanometer 232. The scanning galvanometer drive assembly 233 is used to drive the scanning galvanometer 232 to rotate in the XY plane to scan multiple radial sections of the anterior segment.

[0190] In some embodiments, the more rotation angles the scanning galvanometer 232 rotates in the XY plane, the more radial sections are scanned on the anterior segment, resulting in more accurate and comprehensive three-dimensional information of the anterior segment. For example, in some embodiments, the scanning galvanometer drive assembly 233 is used to drive the scanning galvanometer 232 to scan 25 radial sections in the XY plane, forming a scanning path covering the anterior chamber circumference of the entire anterior segment.

[0191] In some embodiments of this application, such as Figure 3 As shown, the OCT optical system 20 is located on the side of the projection device 11 away from the anterior segment, and also on the side of the first beam splitting assembly 50 away from the projection device 11.

[0192] Among them, such as Figure 1 As shown, in some embodiments of this application, the first imaging module 12 of the corneal imaging optical system 10 partially passes through the measuring housing of the measuring arm 23 in the front-to-back direction. This arrangement allows the first imaging module 12 to be positioned using the measuring housing of the measuring arm 23. The optical path of the first reflected beam is partially located within the measuring housing.

[0193] In some embodiments, the reflective housing of the projection device 11 and the measuring housing of the measuring arm 23 are directly or indirectly fixedly connected.

[0194] In some embodiments, the second light source 21, the optical coupler assembly 22, the reference arm 24, the coupling interference assembly 25, and the second imaging module 26 are all located below the measuring arm 23.

[0195] In the embodiments of this application, the control module 40 is connected to the corneal imaging optical system 10. Specifically, the control module 40 is connected to the projection device 11 and is used to control the first light source 1111 of the projection device 11 to work to form a first incident beam. It is also connected to the first imaging module 12 to obtain a topographic map of the cornea from the first imaging module 12.

[0196] The control module 40 is connected to the OCT optical system 20. Specifically, the control module 40 is connected to the second light source 21 to form a reference beam for the measurement beam. It is also connected to the reflection component 242 via an adjustment device (not shown) to control the position and / or angle of the reflection component 242. It is also connected to the scanning galvanometer drive component 233 to control the position of the scanning galvanometer 232. Furthermore, it is connected to the second imaging module 26 to acquire three-dimensional depth information of the anterior segment of the eye from the second imaging module 26.

[0197] The above describes the OCT optical system 20 in the embodiments of this application as a spectral domain OCT.

[0198] In other alternative embodiments, the OCT optical system 20 described above can also be a swept-frequency OCT.

[0199] In this OCT optical system 20, the second light source 21 is a swept-frequency light source, and the second imaging module 26 is replaced by a balanced-probe OCT optical system 20. The swept-frequency light source outputs light of different wavelengths according to the time change, and then is evenly split into two beams by the optical coupler assembly 22, which enter the reference arm 24 and the sample arm respectively. The portion of the light entering the measurement arm 23 serves as the reference light, and after passing through the scanning galvanometer 232, it enters the patient's anterior segment tissue and is reflected as a second reflected beam carrying depth information of the target region of the anterior segment. The portion entering the reference arm 24 serves as the reference beam and is returned. The second reflected beam and the returned reference beam interfere within the coupling interference assembly 25. The resulting interference fringes are input into the balanced-probe OCT optical system 20, which converts the interference light signal into an analog electrical signal, and finally transmits it to the data analysis and processing module 30 for analysis. The data analysis and processing module 30 preprocesses the transmitted image information and uses physiological structure algorithms to reconstruct the three-dimensional information of the anterior segment.

[0200] The sweep frequency OCT can perform tomographic depth scanning of the anterior segment region at different angles according to a preset scanning mode, and realize the synchronous operation of the corneal imaging optical system 10 and the sweep frequency OCT.

[0201] like Figure 1 and Figure 2 As shown, the three-dimensional anterior segment examination optical assembly 100 also includes an optomechanical structure, which serves as the bottom support for the entire three-dimensional anterior segment examination optical assembly 100 and supports the corneal imaging optical system 10 and the OCT optical system 20 to a certain height to adapt to the height position of the human eye.

[0202] In some embodiments, the optomechanical structure includes a frame and an adjustment assembly 70. The frame has a positioning reference surface with a flatness error of no more than ±0.1 mm. The adjustment assembly 70 is disposed on the positioning reference surface and is used to adjust the position of the corneal imaging optical system 10 and the OCT optical system 20 on the positioning reference surface.

[0203] like Figure 1 and Figure 2 As shown, in some embodiments of this application, the adjustment component 70 of the three-dimensional anterior segment examination optical assembly 100 includes a moving component 71 and an operating component 72. The corneal imaging optical system 10 and the OCT optical system 20 are disposed on the moving component 71, which is mounted on the optomechanical structure. The moving component 71 is configured to move relative to the positioning reference plane in at least one direction in the horizontal plane, thereby enabling the corneal imaging optical system 10 and the OCT optical system 20 to move in at least one direction in the horizontal plane. For example, the moving component 71 is configured to move the corneal imaging optical system 10 and the OCT optical system 20 in the front-back direction or in the left-right direction. In this way, the three-dimensional anterior segment examination optical assembly 100 can be adapted to the height and horizontal position of the human eye.

[0204] The operating component 72 is connected to the moving component 71. The inspector moves the moving component 71 via the operating component 72. The specific form of the moving component 71 is not limited; for example, it can be one or more slide rails. The form of the operating component 72 is not limited; for example, it can be a knob, a swing handle, or other operating element.

[0205] In some embodiments of this application, the components are configured to move relative to the optomechanical structure in two mutually perpendicular directions in the horizontal plane. Specifically, the moving component 71 is configured to drive the corneal imaging optical system 10 and the OCT optical system 20 to move in the front-back direction and in the left-right direction.

[0206] In some embodiments, such as Figure 5 As shown, the control module 40 is located on the rear side of the OCT optical system 20.

[0207] In some embodiments of this application, the data analysis and processing module 30 can be connected to the control module 40 via wired or wireless communication. Therefore, in some embodiments, the data analysis and processing module 30 can be located away from or separate from the optomechanical structure. For example, the data analysis and processing module 30 can be integrated into a computer.

[0208] like Figure 3 and Figure 5As shown, the three-dimensional anterior segment examination optical assembly 100 also includes a power supply module 80, which is electrically connected to the corneal imaging optical system 10, the OCT optical system 20, and the control module 40, and is used to provide the power required for operation to the corneal imaging optical system 10, the OCT optical system 20, and the control module 40.

[0209] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. A three-dimensional anterior segment examination optical assembly, characterized in that, include: A corneal imaging optical system for providing a first incident beam L1 to the cornea and receiving a first reflected beam L1' reflected by the cornea; An OCT optical system is used to provide a measurement beam L2 and a reference beam L3 to the anterior segment of the eye, receive a second reflected beam L2' obtained after the measurement beam L2 is reflected, and cause the second reflected beam L2' and the reference beam L3 to interfere and form an interference beam, satisfying the interference condition: Where ΔL is the optical path difference between L2' and L3, L c The length of coherence; A first beam splitter is used to separate the first reflected beam L1' and the second reflected beam L2'. as well as The first objective lens module is located on the side of the first beam splitter facing the eyeball and is used to focus the measurement beam L2 onto the anterior segment of the eye.

2. The three-dimensional anterior segment examination optical assembly as described in claim 1, characterized in that, The corneal imaging optical system and the OCT optical system are configured as confocal systems, and the system achieves optimal performance when the confocal accuracy δ ≤ ±0.5 mm. The confocal accuracy is defined as the maximum deviation in three-dimensional space of the intersection point of the optical axes of the corneal imaging optical system and the OCT optical system. Δx, Δy, and Δz are the deviations of the intersection points in the x, y, and z axes, respectively.

3. The three-dimensional anterior segment examination optical assembly as described in claim 1, characterized in that, The first beam splitter has a transmission band of 300nm-780nm and 921nm-1000nm, and a reflection band of 785nm-920nm and 1010nm-2000nm. The number of the first beam splitter is at least one, and the first beam splitter is one or more of the following stacked combinations: high-precision multilayer dielectric film beam splitter, metal-dielectric composite film beam splitter, cubic beam splitter prism, periodic grating beam splitter element, and prism-type dispersive beam splitter.

4. The three-dimensional anterior segment examination optical assembly as described in claim 1, characterized in that, The OCT optical system includes a second light source, an optical coupler assembly, a measurement arm, a reference arm, a coupling interference assembly, and a second imaging module. The second light source provides a second incident beam. The optical coupler assembly splits the second incident beam into a measurement beam L2 and a reference beam L3. The measurement arm guides the measurement beam L2 to the cornea and receives the second reflected beam L2'. The reference arm receives and reflects the reference beam L3. The coupling interference assembly receives the second reflected beam L2' and the reference beam L3 and causes them to interfere within each other. The second imaging module is used for imaging the interference beam.

5. The three-dimensional anterior segment examination optical assembly as described in claim 4, characterized in that, The second light source is a high spatial coherence light source, selected from at least one of broadband laser beams and swept laser beams, with its center wavelength selected from at least one wavelength in the range of 400nm-1600nm; the second incident beam has a preset spectral width, satisfying 0nm≤Δλ≤300nm, where the spectral width is defined as the wavelength range corresponding to half the peak spectral intensity, i.e., Δλ=λ high -λ low , λ high λ represents the wavelength at which the peak value at the longer wavelength end is half. low This is the wavelength corresponding to half the peak value at the short wavelength end.

6. The three-dimensional anterior segment examination optical assembly as described in claim 4, characterized in that, The second imaging module includes a second collimator, a second beam splitter, a second objective lens module, and a second camera arranged sequentially along the optical path of the interference beam; the second collimator is used to collimate the interference beam, the second beam splitter is used to diffract the interference beam, and the second objective lens is used to focus the diffracted beam onto the second camera.

7. The three-dimensional anterior segment examination optical assembly as described in claim 6, characterized in that, The second collimator can collimate a beam with an NA ≥ 0.1, and the beam divergence angle after collimation is ≤ 0.1 mrad.

8. The three-dimensional anterior segment examination optical assembly as described in claim 6, characterized in that, The second camera is a line scan camera with a single or multiple rows of imaging pixels, each row having at least 2048 imaging pixels and the imaging pixel size being at least 3.5μm×3.5μm.

9. The three-dimensional anterior segment examination optical assembly as described in claim 6, characterized in that, The second beam-splitting component includes a diffraction grating with a density of 1200 l / mm to 2400 l / mm; the incident surface of the second beam-splitting component has a certain tilt angle with the optical axis of the light emitted from the second collimator, the tilt angle ranging from 0° to 180°, with a range error. 0.5 .

10. The three-dimensional anterior segment examination optical assembly as described in claim 6, characterized in that, The second imaging module further includes a third objective lens module disposed between the second beam splitter and the second camera. The third objective lens module is used to focus diffracted beams of different wavelengths onto the second camera and to arrange the light of different wavelengths linearly on the second camera according to wavelength. The light spot formed by focusing the diffracted beam satisfies a diameter ≤ 7 μm and the diameter of the light spot is approximately twice the size of a pixel unit.

11. The three-dimensional anterior segment examination optical assembly as described in claim 10, characterized in that, The third objective lens module includes a third cemented doublet lens, a third concave lens, a fourth cemented doublet lens, and a fifth cemented doublet lens arranged sequentially along the optical path. The focal length f1 of the third cemented doublet lens satisfies 22mm ≤ f1 ≤ 42mm, the focal length f2 of the third concave lens satisfies -10mm ≤ f2 ≤ -30mm, the focal length of the fourth cemented doublet lens is infinite, and the focal length f3 of the fifth cemented doublet lens satisfies 140mm ≤ f3 ≤ 175mm. The second objective lens module is a telecentric objective lens module. The optical axis of the third objective lens module has a certain angle with the incident surface of the second beam splitter, the angle ranging from 0° to 180°, with a range error. 0.5 .

12. The three-dimensional anterior segment examination optical assembly as described in claim 4, characterized in that, The measuring arm includes a first collimator and a scanning galvanometer arranged sequentially along the optical path of the measuring beam L2. The first collimator is used to collimate the measuring beam L2 and the second reflected beam L2', and its collimation NA is ≥0.14, and the beam divergence angle after collimation is ≤0.1mrad. The scanning galvanometer is used to control the movement of the measuring beam L2 in the scanning plane to provide the measuring beam L2 to different radial sections of the anterior segment of the eye.

13. The three-dimensional anterior segment examination optical assembly as described in claim 12, characterized in that, The scanning galvanometer is used to control the movement of the measurement beam L2 within the scanning plane. The maximum range of the scanning optical angle is ±30°, and the scanning linearity error is... ,in This represents the maximum deviation between the actual angle and the theoretical angle across the entire scanning range. The maximum deflection angle range of the scanning galvanometer is ±20°.

14. The three-dimensional anterior segment examination optical assembly as described in claim 4, characterized in that, The reference arm includes a third collimator and a reflective assembly. The third collimator is used to collimate the reference beam L3, and its collimation NA is ≥0.

2. After collimation, the beam divergence angle is ≤0.1mrad. The reflective assembly is used to reflect the reference beam L3 back to the third collimator. The flatness of the reflective assembly is ≤λ / 4, λ=632.8nm, and reflectivity is ≥98%.

15. The three-dimensional anterior segment examination optical assembly as described in claim 14, characterized in that, The reference arm includes a converging lens group, the focal length f5 of which satisfies 10mm≤f5≤30mm, and the converging lens group is disposed between the third collimator and the reflection assembly.

16. The three-dimensional anterior segment examination optical assembly as described in claim 15, characterized in that, The distance and / or angle of the reflective component relative to the third collimator are adjustable, with the distance adjustment accuracy of the reflective component relative to the third collimator ≤ ±5μm and the angle adjustment accuracy ≤ ±0.01°.

17. The three-dimensional anterior segment examination optical assembly as described in claim 1, characterized in that, The corneal imaging optical system includes a projection device and a first imaging module; the projection device is used to provide the first incident beam L1, and the first objective lens module is used to receive the first reflected beam L1' and focus the first reflected beam L1' onto the first imaging module.

18. The three-dimensional anterior segment examination optical assembly as described in claim 17, characterized in that, The wavelength range of the first incident beam L1 is selected from at least one of 300nm-780nm and 921nm-2000nm.

19. The three-dimensional anterior segment examination optical assembly as described in claim 17, characterized in that, The first imaging module further includes a fourth objective lens module, which is located on the light-incident side of the first imaging module. The fourth objective lens module is a telecentric objective lens module with a telecentricity ≤0.1°. The fourth objective lens module includes a first cemented doublet lens, a plano-convex lens, a first concave lens, a second concave lens, and a second cemented doublet lens arranged sequentially along the optical path. The focal length f1 of the first cemented doublet lens satisfies -5mm≤f1≤-25mm, the focal length f2 of the plano-convex lens satisfies 0mm≤f2≤12mm, the focal length f3 of the first concave lens satisfies 5mm≤f3≤18mm, the focal length f4 of the second concave lens satisfies 30mm≤f4≤55mm, and the focal length f5 of the second cemented doublet lens satisfies -40mm≤f5≤-64mm. The transverse chromatic aberration across the entire field of view is ≤±0.7μm.

20. The three-dimensional anterior segment examination optical assembly as described in any one of claims 1 to 19, characterized in that, The first objective lens module is a telecentric objective lens module, the telecentricity of the first objective lens module is ≤0.1°, the focal length f and the aperture D of the first objective lens module satisfy 3mm≤f / D≤10mm, the focal length temperature drift coefficient of the first objective lens module is ≤0.01mm / ℃, and the numerical aperture NA of the first objective lens module satisfies 0.1≤NA≤0.5.

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