CN216365007U

CN216365007U - Line field confocal OCT device

Info

Publication number: CN216365007U
Application number: CN202122247018.XU
Authority: CN
Inventors: 孔冠岳; 谢会开; 赵晖; 何方明
Original assignee: Foshan Light Micro Technology Co ltd
Current assignee: Foshan Light Micro Technology Co ltd
Priority date: 2021-09-16
Filing date: 2021-09-16
Publication date: 2022-04-26
Anticipated expiration: 2031-09-16

Abstract

The application provides a confocal OCT device of line field relates to medical diagnosis technical field, and its technical scheme main points are: comprises a light source module for providing a line beam; the beam splitting module is used for receiving the line beam and splitting the line beam into reference light and sample light; the reference module is used for receiving the reference light and reflecting the reference light to the beam splitting module, and the reference module is connected with a first displacement mechanism used for driving the reference module to displace; the sample module is used for receiving sample light, the sample light enters the sample tissue through the sample module and is reflected back to the beam splitting module along the light path, and the sample module is connected with a second displacement mechanism used for driving the sample module to displace; and the imaging module is used for receiving the reference light reflected by the reference module and the interference light formed on the beam splitting module by the sample light reflected by the sample tissue, and generating an image according to the interference light. The application provides a confocal OCT device of line field has the resolution ratio height, and the advantage that the detection degree of depth is big.

Description

Line field confocal OCT device

Technical Field

The application relates to the technical field of medical diagnosis, in particular to a line-field confocal OCT device.

Background

For early diagnosis of cancer, diagnostic modalities using non-invasive imaging techniques have been developed to provide earlier, more accurate detection of malignant lesions.

Clinically available techniques that enable in vivo skin imaging at the highest spatial resolution are, for example, Reflection Confocal Microscopy (RCM), Optical Coherence Tomography (OCT), and fluorescence microscopy. RCM is an optical technique that provides a frontal cross-sectional view of tissue with a spatial resolution comparable to histology, on the order of 1 μm. RCM has been shown to improve diagnostic accuracy. However, the main limitation of RCM is that the penetration in tissue is relatively weak, only about 200 microns, and structures located in tissue cannot be imaged. Another major problem is the interpretation of RCM slices, since they are tissue slices in the frontal direction, i.e. perpendicular to the conventional vertical direction. OCT is an interferometric optical imaging modality. OCT produces images of cross-sections of the skin with a resolution of a few microns, significantly lower than RCM. However, the skin penetration depth of OCT is higher than RCM, about 1 mm. The possibility of evaluating OCT images in a view in the vertical direction makes them easier to compare with conventional tissue sections. OCT has been applied to diagnosis of various cancer syndromes. However, diagnosis using OCT is less accurate than using RCM, mainly because of insufficient imaging resolution of OCT.

In view of the above problems, the inventors propose a line-field confocal OCT scheme combining the advantages of RCM and OCT in terms of spatial resolution, penetration and image direction.

SUMMERY OF THE UTILITY MODEL

The application aims to provide a line-field confocal OCT device which has the advantages of high resolution and large detection depth.

In a first aspect, the present application provides a line-field confocal OCT apparatus, which comprises:

including the light source module that is used for providing the line beam, still include:

the beam splitting module is used for receiving the line beam and splitting the line beam into reference light and sample light;

the reference module is used for receiving the reference light and reflecting the reference light to the beam splitting module, and the reference module is connected with a first displacement mechanism used for driving the reference module to displace;

the sample module is used for receiving the sample light, the sample light enters the sample tissue through the sample module and is reflected back to the beam splitting module along the light path, and the sample module is connected with a second displacement mechanism used for driving the sample module to displace;

and the imaging module is used for receiving the reference light reflected by the reference module and interference light formed on the beam splitting module by the sample light reflected by the sample tissue, and generating an image according to the interference light.

Utilize the light source module to provide the line beam, the line beam is divided into reference light and sample light through beam splitting module, reference light is reflected back beam splitting module along former light path behind the reference module, sample light is reflected back beam splitting module along former light path behind sample module arrival sample tissue, reflected reference light and reflected sample light mix on beam splitting module and form interference light, interference light shines on imaging module and generates the image, at this in-process, remove reference module through first displacement mechanism, remove sample module and then realize the detection of different degree of depth through second displacement mechanism, and sample light is after sample module, the focus falls on sample tissue, interference light that forms through reflection mixing focuses on imaging module, the advantage that has combined RCM and OCT, have the resolution height, the big beneficial effect of detection depth.

Further, in the present application, the reference module includes a first cemented doublet for receiving the reference light emitted from the beam splitting module, a first microscope objective for receiving the reference light passing through the first cemented doublet, and a reflector for receiving and reflecting the reference light passing through the first microscope objective to return the reference light to the beam splitting module along an incident light path.

Chromatic aberration is eliminated through the first cemented doublet, and imaging quality is improved.

Further, in this application, first biconvex lens is formed by first biconvex lens and first meniscus veneer, first biconvex lens sets up and is being close to beam splitting module one side, first biconvex lens is close to the radius of curvature of beam splitting module one side is 31.69mm, and the radius of curvature of opposite side is-28.45 mm, and thickness is 8mm, first meniscus is close to the radius of curvature of beam splitting module one side is-28.45 mm, and the radius of curvature of opposite side is-161.05 mm, and thickness is 4 mm.

Further, in the present application, the sample module includes a second doublet for receiving the sample light emitted from the beam splitting module, a second microscope objective for receiving the sample light passing through the second doublet, and a window sheet for receiving the sample light passing through the second microscope objective, the sample light passing through the window sheet into the sample tissue.

Chromatic aberration is eliminated through the second double cemented lens, and imaging quality is improved.

Further, in this application, the second biconvex lens is formed by the second biconvex lens and the second meniscus veneer, the second biconvex lens sets up and is being close to beam splitting module one side, the second biconvex lens is close to the radius of curvature of beam splitting module one side is 31.69mm, and the radius of curvature of opposite side is-28.45 mm, and thickness is 8mm, the second meniscus is close to the radius of curvature of beam splitting module one side is-28.45 mm, and the radius of curvature of opposite side is-161.05 mm, and thickness is 4 mm.

Further, in this application, the imaging module includes a third double cemented lens and a line camera, where the third double cemented lens is used to receive the interference light and focus the interference light on the line camera, and the line camera converts the interference light into an electrical signal to generate an image.

Further, in this application, the third double-cemented lens is formed by third biconvex lens and the veneer of third meniscus lens, third biconvex lens sets up and is being close to beam splitting module one side, third biconvex lens is close to the curvature radius of beam splitting module one side is 36.27mm, and the curvature radius of opposite side is-33.8 mm, and thickness is 8mm, third meniscus lens is close to the curvature radius of beam splitting module one side is-33.8 mm, and the curvature radius of opposite side is-248.86 mm, and thickness is 4 mm.

Further, in the present application, the beam splitting module is a non-polarizing beam splitting cube.

Further, in this application, light source module includes laser instrument, the two cemented lens of fourth and the two cemented lens of fifth, laser instrument output light extremely the two cemented lens of fourth, the two cemented lens of fourth will light turns into the gaussian beam, the two cemented lens of fifth is used for receiving the gaussian beam and focuses on it into the line beam.

Further, in this application, the fourth double cemented lens is formed by the fourth convex-concave lens and the fourth double convex lens, the fourth convex-concave lens sets up and is being close to laser instrument one side, the fourth convex-concave lens is close to the curvature radius of laser instrument one side is 57.3mm, and the curvature radius of opposite side is 9.545mm, and thickness is 2mm, the fourth double convex lens is close to the curvature radius of laser instrument one side is 9.545mm, and the curvature radius of opposite side is-9.545 mm, and thickness is 6.5mm, the fifth double cemented lens is formed by the gluing of fifth double convex lens and fifth convex-concave lens, the fifth double convex lens sets up and is being close to fourth double cemented lens one side, the fifth double convex lens is close to the curvature radius of fourth double cemented lens one side is 30.922mm, and the curvature radius of opposite side is-40.11 mm, and thickness is 6.12mm, the curvature radius of one side, close to the fourth double-cemented lens, of the fifth meniscus lens is-40.11 mm, the curvature radius of the other side of the fifth meniscus lens is-254.462 mm, the thickness of the fifth meniscus lens is 4.18mm, and the distance between the fourth double-cemented lens and the fifth double-cemented lens is 80 mm.

In the process, the reference module is moved by the first displacement mechanism, the sample module is moved by the second displacement mechanism to realize detection of different depths, and the sample light passes through the sample module, the focal point falls on the sample tissue, the interference light formed by reflection and mixing is focused on the imaging module, thereby combining the advantages of RCM and OCT, the method has the advantages of high resolution and large detection depth.

Additional features and advantages of the application will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by the practice of the application. The objectives and other advantages of the application may be realized and attained by the structure particularly pointed out in the written description and claims hereof as well as the appended drawings.

Drawings

Fig. 1 is a schematic structural diagram of a line-field confocal OCT apparatus provided in the present application.

Fig. 2 is a schematic structural diagram of a line-field confocal OCT apparatus provided in the present application.

Fig. 3 is a schematic structural diagram of a line-field confocal OCT apparatus provided in the present application.

Fig. 4 is a resolution-field size diagram of a line-field confocal OCT apparatus using the present application.

In the figure: 100. a light source module; 200. a beam splitting module; 300. a reference module; 400. a sample module; 500. an imaging module; 600. a second displacement mechanism; 700. a first displacement mechanism; 110. a laser; 120. a fourth doublet lens; 130. a fifth cemented doublet; 210. a non-polarizing beam splitting cube; 310. a first cemented doublet lens; 320. a first microscope objective; 330. a reflective sheet; 410. a second cemented doublet lens; 420. a second microscope objective; 430. a window sheet; 510. a third cemented doublet; 520. a line scan camera.

Detailed Description

The technical solutions in the present application will be described clearly and completely with reference to the drawings in the present application, and it should be understood that the described embodiments are only a part of the embodiments of the present application, and not all of the embodiments. The components of the present application, as generally described and illustrated in the figures herein, may be arranged and designed in a wide variety of different configurations. Thus, the following detailed description of the embodiments of the present application, presented in the accompanying drawings, is not intended to limit the scope of the claimed application, but is merely representative of selected embodiments of the application. All other embodiments, which can be derived by a person skilled in the art from the embodiments of the present application without making any creative effort, shall fall within the protection scope of the present application.

It should be noted that: like reference numbers and letters refer to like items in the following figures, and thus, once an item is defined in one figure, it need not be further defined and explained in subsequent figures. Meanwhile, in the description of the present application, the terms "first", "second", and the like are used only for distinguishing the description, and are not to be construed as indicating or implying relative importance.

Referring to fig. 1 to 4, a line-field confocal OCT apparatus includes:

a light source module 100 for providing a line beam;

a beam splitting module 200 for receiving the line beam and splitting the line beam into reference light and sample light;

the reference module 300 is used for receiving the reference light and reflecting the reference light to the beam splitting module 200, and the reference module 300 is connected with a first displacement mechanism 700 for driving the reference module 300 to displace;

the sample module 400 is used for receiving sample light, the sample light enters the sample tissue through the sample module 400 and is reflected back to the beam splitting module 200 along the light path, and the sample module 400 is connected with a second displacement mechanism 600 for driving the sample module 400 to displace;

and an imaging module 500 for receiving the reference light reflected by the reference module 300 and the interference light formed on the beam splitting module 200 by the sample light reflected by the sample tissue, and generating an image according to the interference light.

Through the above technical solution, a light source module 100 is used to provide a line beam, the line beam is divided into reference light and sample light through a beam splitting module 200, the reference light is reflected back to the beam splitting module 200 along an original light path after passing through the reference module 300, the sample light is reflected back to the beam splitting module 200 along the original light path after passing through a sample module 400 to reach a sample tissue, the reflected reference light and the reflected sample light are mixed on the beam splitting module 200 to form interference light, the interference light is irradiated on an imaging module 500 to generate an image, in this process, the reference module 300 is moved through a first displacement mechanism 700, the sample module 400 is moved through a second displacement mechanism 600 to realize detection of different depths of the sample tissue, and after passing through the sample module 400, a focus falls on the sample tissue, the interference light formed by reflection and mixing is focused on the imaging module 500, so advantages of RCM and OCT are combined, the method has the advantages of high resolution and large detection depth.

Further, as shown in fig. 2 and 3, in some embodiments, the reference module 300 includes a first cemented doublet 310, a first microscope objective 320, and a reflector 330, the first cemented doublet 310 is configured to receive the reference light emitted from the beam splitting module 200, the first microscope objective 320 is configured to receive the reference light passing through the first cemented doublet 310, and the reflector 330 is configured to receive and reflect the reference light passing through the first microscope objective 320, so that the reference light returns to the beam splitting module 200 along the incident light path.

Through the above technical scheme, the first cemented doublet 310 focuses the reference light on the first microscope objective 320, the reference light passes through the first microscope objective 320 and then irradiates the reflector 330, and then is reflected back to the beam splitting module 200 along the light path, in this process, the first cemented doublet 310 is used for eliminating chromatic aberration, and meanwhile, the reference light is focused on the first microscope objective 320, so that loss is reduced, and imaging quality is further improved.

In some embodiments, the first microscope objective 320 may be a microscope objective commonly used in the market, and preferably, the first microscope objective 320 in this application is a 20 × 0.85na microscope objective of Nikon CFI Super Fluor series.

In some embodiments, the first biconvex lens 310 is formed by gluing a first biconvex lens and a first meniscus lens, the first biconvex lens is disposed on a side close to the beam splitting module 200, a curvature radius of the first biconvex lens close to the beam splitting module 200 is 31.69mm, a curvature radius of the first biconvex lens on the other side is-28.45 mm, and a thickness of the first biconvex lens is 8mm, a curvature radius of the first meniscus lens close to the beam splitting module 200 is-28.45 mm, a curvature radius of the first meniscus lens on the other side is-161.05 mm, and a thickness of the first biconvex lens is 4 mm. The first biconvex lens is made of n-lak22, and the first meniscus lens is made of n-sf 6. Moreover, the distance between the first meniscus lens and the first microscope objective lens 320 is 80mm, the distance between the first microscope objective lens 320 and the reflector 330 is 1mm, and the distance between the first biconvex lens and the beam splitting module 200 is 42.605 mm.

Wherein the focal length of the first cemented doublet 310 is 50 mm.

In some embodiments, the reflector 330 is a neutral density reflector, which is a coated glass plate, and transmits a portion of light and reflects another portion of light according to the principle of thin film interference, so that the illumination intensity of the reference light reflected to the beam splitting module 200 can be adjusted as required.

Further, in some embodiments, the sample module 400 includes a second doublet lens 410, a second microscope objective 420 and a window sheet 430, the second doublet lens 410 is used for receiving the sample light emitted from the beam splitting module 200, the second microscope objective 420 is used for receiving the sample light passing through the second doublet lens 410, the window sheet 430 is used for receiving the sample light passing through the second microscope objective 420, and the sample light passes through the window sheet 430 to enter the sample tissue.

Through the above technical scheme, the second cemented doublet 410 focuses the sample light on the second microscope objective 420, the second microscope objective 420 focuses the sample light again, at this time, the sample light is highly focused and then passes through the window sheet 430 to irradiate on the sample tissue, and then is reflected back to the beam splitting module 200 along the light path, in this process, the second cemented doublet 410 is used for focusing the sample light on the second microscope objective 420, so that the loss is reduced, and meanwhile, the effect of reducing chromatic aberration is achieved, and the imaging quality is further improved.

In some embodiments, the second microscope objective 420 may be a microscope objective commonly used in the market, and preferably, the second microscope objective 420 in this application is a 20 × 0.85na microscope objective of Nikon CFI Super Fluor series.

In some embodiments, the second biconvex lens 410 is formed by gluing a second biconvex lens and a second meniscus lens, the second biconvex lens is disposed on a side close to the beam splitting module 200, a curvature radius of the second biconvex lens close to the beam splitting module 200 is 31.69mm, a curvature radius of the second biconvex lens on the other side is-28.45 mm, and a thickness of the second biconvex lens is 8mm, a curvature radius of the second meniscus lens close to the beam splitting module 200 is-28.45 mm, a curvature radius of the second meniscus lens on the other side is-161.05 mm, and a thickness of the second biconvex lens is 4 mm. The material of the second biconvex lens is n-lak22, and the material of the second biconvex lens is n-sf 6. Moreover, the distance between the second meniscus lens and the second microscope objective lens 420 is 80mm, the distance between the second microscope objective lens 420 and the window 430 is 1mm, and the distance between the second biconvex lens and the beam splitting module 200 is 42.605 mm.

Wherein the focal length of the second cemented doublet 410 is 50 mm.

The window piece 430 is used to provide protection from the external environment when the sample light is transmitted in the sample module 400. In other embodiments, the window sheet 430 may be eliminated.

Further, in some of the embodiments, the imaging module 500 includes a third double cemented lens 510 and a line camera 520, the third double cemented lens 510 is used for receiving interference light and focusing the interference light on the line camera 520, and the line camera 520 converts the interference light into an electrical signal to generate an image.

Through the above technical solution, the third double cemented lens 510 focuses the interference light on the line camera 520, and performs focusing and color aberration elimination through the third double cemented lens 510, and in the line-field confocal optical path, only the light emitted by the line on the focal plane can reach the line camera 520 for imaging; light rays emitted by lines outside the focal plane are out of focus at the image plane, and most of the light rays cannot reach the photosensitive elements of the line camera 520. Therefore, the observed target on the focal plane is bright, while the non-observed point is black as the background, so that the contrast is increased, and the image is clearer, and the third double cemented lens 510 allows the focus to fall on the photosensitive element of the line camera 520, so that the line camera 520 forms a high-quality image.

Further, in some embodiments, the third double-cemented lens 510 is formed by cementing a third double-convex lens and a third concave-convex lens, the third double-convex lens is disposed at a side close to the beam splitting module 200, a curvature radius of the third double-convex lens at a side close to the beam splitting module 200 is 36.27mm, a curvature radius of the other side is-33.8 mm, and a thickness of the third double-convex lens is 8mm, a curvature radius of the third concave-convex lens at a side close to the beam splitting module 200 is-33.8 mm, a curvature radius of the other side is-248.86 mm, and a thickness of the third concave-convex lens is 4 mm. The material of the third biconvex lens is n-lak22, and the material of the third concave-convex lens is n-sf 6. And, the pitch between the third meniscus lens and the line camera 520 is 52.955mm, and the pitch between the third biconvex lens and the beam splitting module 200 is 52.955 mm.

Wherein, in some embodiments, the focal length of the third cemented doublet 510 is 60 mm.

As a preferred embodiment, the line camera 520 may be a 2048 pixel cmos camera EV71YO1CUB2210-BB1 available from e2v, or an area camera may be used instead of the line camera 520.

Further, in some of these embodiments, the beam splitting module 200 is a non-polarizing beam splitting cube 210.

By the technical scheme, the non-polarization beam splitting cube 210 can split light into two directions at the same ratio regardless of the wavelength and the polarization state of the light, so that reference light and sample light are formed and are used for forming interference light in the subsequent process and imaging is performed through the interference light.

Further, in some embodiments, the light source module 100 includes a laser 110, a fourth double cemented lens 120, and a fifth double cemented lens 130, where the laser 110 is configured to output light to the fourth double cemented lens 120, the fourth double cemented lens 120 is configured to convert the light into a gaussian beam, and the fifth double cemented lens 130 is configured to receive the gaussian beam and focus the gaussian beam into a line beam. Among other things, in some embodiments, a xenon lamp may be used as the light source instead of the laser 110.

Through the above technical solution, the laser 110 generates light, wherein the laser 110 may be a super-continuum laser, and ultra-short pulse laser is coupled into a high nonlinear fiber, usually a photonic crystal fiber PCF, and the pulse spectrum of the output light is broadened due to the nonlinear effect, the four-wave mixing and the optical soliton effect of the fiber, and the spectrum width is from 0.4um to 2.4um, so as to achieve ultra-wide spectrum output, and emit the light onto the fourth double-cemented lens 120, the fourth double-cemented lens 120 converts the light into a gaussian beam of approximately parallel light, the gaussian beam irradiates on the fifth double-cemented lens 130, and the fifth double-cemented lens 130 focuses the gaussian beam into a line beam and outputs the line beam.

In some embodiments, the fourth double cemented lens 120 is formed by cementing a fourth convex-concave lens and a fourth double convex lens, the fourth convex-concave lens is disposed at a side close to the laser 110, the radius of curvature of the fourth convex-concave lens at the side close to the laser 110 is 57.3mm, the radius of curvature of the other side is 9.545mm, the thickness is 2mm, the radius of curvature of the fourth double convex lens at the side close to the laser 110 is 9.545mm, the radius of curvature of the other side is-9.545 mm, the thickness is 6.5mm, the fifth double cemented lens 130 is formed by cementing a fifth double convex lens and a fifth concave-convex lens, the fifth double convex lens is disposed at a side close to the fourth double cemented lens 120, the radius of curvature of the fifth double convex lens at a side close to the fourth double cemented lens 120 is 30.922mm, the radius of curvature of the other side is-40.11 mm, the thickness is 6.12mm, the radius of curvature of the fifth concave-convex lens at a side close to the fourth double cemented lens 120 is-40.11 mm, the radius of curvature of the other side is-254.462 mm, the thickness is 4.18mm, the distance between the fourth double cemented lens 120 and the fifth double cemented lens 130 is 80mm, and the distance between the fifth double cemented lens 130 and the beam splitting module 200 is 62.605 mm.

In some embodiments, the focal length of the fourth cemented doublet 120 is 15mm, and the focal length of the fifth cemented doublet 130 is 75 mm.

Specifically, as a preferred scheme, in the present application, the optical system parameters of the light emitted from the laser 110 to the window 430 are as follows:

the parameters of the light system after the light is emitted from the laser 110 to the reflector 330 are shown in the following table:

the optical system parameters of the interference light from the beam splitting module 220 to the line camera 520 are shown in the following table:

in addition, in some embodiments, the first displacement mechanism 700 and the second displacement mechanism 600 are PZT displacement tables, and in order to ensure the imaging clarity, the second displacement mechanism 600 drives the second microscope objective 420 and the window sheet 430 to move, so as to perform full-depth scanning on the sample tissue. The PZT translation stage is a piezoelectric translation stage driven by taking piezoelectric ceramics as a basic element, and the driving mode is a mechanism amplification type. Under the same driving voltage, the displacement of the mechanism amplification platform is several times to dozens of times of that of the direct-drive platform, and the mechanism amplification platform has nanometer resolution and millisecond response time.

The first displacement mechanism 700 drives the first microscope objective 320 and the reflector 330 to move, and the moving position is determined according to the moving position of the second microscope objective 420 and the window 430 driven by the second displacement mechanism 600.

In some embodiments, the first microscope objective 320 is spaced apart from the first cemented doublet 310 by 80mm to 80.7mm because the first displacement mechanism 700 drives the first microscope objective 320 to move.

Similarly, the second microscope objective 420 and the second doublet lens 410 are spaced apart by 80mm to 80.7 mm.

In addition, in the scheme of the application, a 5-frame phase shift method is adopted to improve the signal-to-noise ratio of the image. The algorithm needs to be calculated by 5 related frames E1, E2, E3, E4 and E5, and according to (E4-E2) ^ 2- (E1-E3) (E3-E5), the phase difference between every two adjacent frames is pi/2. In some embodiments, the central wavelength of the light source is 800nm, the refractive index of the sample tissue is set to 1.5, and the distance that the first displacement mechanism 700 needs to move is 800/(4 × 1.5) =133.3nm per frame. This displacement produces an optical phase shift of pi/2. The first displacement mechanism 700 is thus oscillated throughout the depth scanning performed by the second displacement mechanism 600. Where, in the above formula, one wavelength is 2Pi, so the distance corresponding to Pi/2 needs to be divided by 4.

Compared with the traditional OCT, the technical scheme of the application uses the light source of ultra wide band to provide the light for detection, focuses on light through the fifth double-cemented lens 130, and only one-dimensional imaging is carried out, thereby improving the signal-to-noise ratio, and not needing expensive spectrum devices such as practical grating, spectrometer, sweep frequency laser, etc., effectively reducing the cost while guaranteeing the detection quality.

The specific imaging effect is shown in fig. 4, and through the scheme of the application, the resolution can reach 1.4um, and the field of view is 0.98 mm.

The above description is only an example of the present application and is not intended to limit the scope of the present application, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, improvement and the like made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A line-field confocal OCT apparatus comprising a light source module (100) for providing a line beam, characterized by further comprising:

a beam splitting module (200) for receiving the line beam and splitting the line beam into reference light and sample light;

the reference module (300) is used for receiving the reference light and reflecting the reference light to the beam splitting module (200), and a first displacement mechanism (700) used for driving the reference module (300) to displace is connected to the reference module (300);

the sample module (400) is used for receiving the sample light, the sample light enters the sample tissue through the sample module (400) and is reflected back to the beam splitting module (200) along the light path, and the sample module (400) is connected with a second displacement mechanism (600) used for driving the sample module (400) to displace;

an imaging module (500) for receiving the reference light reflected back by the reference module (300) and interference light formed on the beam splitting module (200) by the sample light reflected back by the sample tissue, from which interference light an image is generated.

2. The confocal OCT apparatus of claim 1, wherein the reference module (300) comprises a first doublet lens (310), a first microscope objective (320), and a reflector (330), the first doublet lens (310) is configured to receive the reference light emitted from the beam splitting module (200), the first microscope objective (320) is configured to receive the reference light passing through the first doublet lens (310), and the reflector (330) is configured to receive and reflect the reference light passing through the first microscope objective (320) and return the reference light to the beam splitting module (200) along an incident light path.

3. The confocal OCT apparatus of claim 2, wherein the first biconvex lens (310) is formed by gluing a first biconvex lens and a first meniscus lens, the first biconvex lens is disposed on a side close to the beam splitting module (200), the first biconvex lens has a radius of curvature of 31.69mm on the side close to the beam splitting module (200), a radius of curvature of-28.45 mm on the other side, and a thickness of 8mm, the first meniscus lens has a radius of curvature of-28.45 mm on the side close to the beam splitting module (200), a radius of curvature of-161.05 mm on the other side, and a thickness of 4 mm.

4. The confocal OCT apparatus of claim 1, wherein the sample module (400) comprises a second doublet (410), a second microscope objective (420), and a window sheet (430), wherein the second doublet (410) is configured to receive the sample light emitted from the beam splitting module (200), the second microscope objective (420) is configured to receive the sample light passing through the second doublet (410), and the window sheet (430) is configured to receive the sample light passing through the second microscope objective (420), and the sample light passes through the window sheet (430) and enters the sample tissue.

5. The confocal OCT device of claim 4, wherein the second biconvex lens (410) is cemented by a second biconvex lens and a second meniscus lens, the second biconvex lens is disposed at a side close to the beam splitting module (200), the second biconvex lens has a radius of curvature of 31.69mm at a side close to the beam splitting module (200), a radius of curvature of-28.45 mm at another side, and a thickness of 8mm, the second meniscus lens has a radius of curvature of-28.45 mm at a side close to the beam splitting module (200), a radius of curvature of-161.05 mm at another side, and a thickness of 4 mm.

6. The confocal OCT apparatus of claim 1, wherein the imaging module (500) comprises a third double cemented lens (510) and a line camera (520), the third double cemented lens (510) is configured to receive the interference light and focus the interference light on the line camera (520), and the line camera (520) converts the interference light into an electrical signal to generate an image.

7. The confocal OCT apparatus of claim 6, wherein the third biconvex lens (510) is formed by a third biconvex lens and a third meniscus lens, the third biconvex lens is disposed on a side close to the beam splitting module (200), the third biconvex lens has a radius of curvature of 36.27mm on a side close to the beam splitting module (200), a radius of curvature of-33.8 mm on another side, and a thickness of 8mm, the third meniscus lens has a radius of curvature of-33.8 mm on a side close to the beam splitting module (200), and a radius of curvature of-248.86 mm on another side, and a thickness of 4 mm.

8. The confocal OCT apparatus of claim 1, wherein said beam splitting module (200) is a non-polarizing beam splitting cube (210).

9. The confocal OCT apparatus of claim 1, wherein the light source module (100) comprises a laser (110), a fourth doublet (120), and a fifth doublet (130), wherein the laser (110) is configured to output light to the fourth doublet (120), the fourth doublet (120) is configured to convert the light into a gaussian beam, and the fifth doublet (130) is configured to receive and focus the gaussian beam into the line beam.

10. The confocal line-field OCT device of claim 9, wherein the fourth biconvex lens (120) is formed by gluing a fourth convex-concave lens and a fourth biconvex lens, the fourth convex-concave lens is disposed on a side close to the laser (110), the fourth convex-concave lens has a radius of curvature of 57.3mm on a side close to the laser (110), a radius of curvature of 9.545mm on the other side, and a thickness of 2mm, the fourth biconvex lens has a radius of curvature of 9.545mm on a side close to the laser (110), and a radius of curvature of-9.545 mm on the other side, and a thickness of 6.5mm, the fifth biconvex lens (130) is formed by gluing a fifth biconvex lens and a fifth meniscus lens, the fifth biconvex lens is disposed on a side close to the fourth biconvex lens (120), and the radius of curvature of the fifth biconvex lens is 30.922mm on a side close to the fourth biconvex lens (120), the curvature radius of the other side is-40.11 mm, the thickness is 6.12mm, the curvature radius of one side, close to the fourth double-cemented lens (120), of the fifth concave-convex lens is-40.11 mm, the curvature radius of the other side is-254.462 mm, the thickness is 4.18mm, and the distance between the fourth double-cemented lens (120) and the fifth double-cemented lens (130) is 80 mm.