CN216365007U - Line field confocal OCT device - Google Patents

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

A line-field confocal OCT device

technical field

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

Background technique

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

Examples of clinically available techniques capable of imaging in vivo skin with the highest spatial resolution are 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, approximately 1 μm. RCM has been shown to improve diagnostic accuracy. However, the main limitation of RCM is its relatively weak penetration in tissue, only about 200 microns, and cannot image structures located in tissue. Another major issue is the interpretation of RCM slices, as they are in frontal orientation, i.e., tissue slices perpendicular to the traditional vertical orientation. OCT is an interferometric optical imaging modality. OCT produces skin cross-sectional images with a resolution of a few microns, significantly lower than RCM. However, the skin penetration depth of OCT is higher than that of RCM, about 1 mm. The possibility to evaluate OCT images in a vertically oriented view makes them easier to compare with traditional tissue sections. OCT has been applied to the diagnosis of various cancer syndromes. However, diagnosis using OCT is not as accurate as using RCM, mainly because of the insufficient imaging resolution of OCT.

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

Utility model content

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

In the first aspect, the present application provides a line-field confocal OCT device, and the technical solution is as follows:

Includes light source module for supplying line beams, also includes:

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

a reference module, configured to receive the reference light and reflect the reference light to the beam splitting module, the reference module is connected with a first displacement mechanism for driving the reference module to displace;

The sample module is used for receiving the sample light, and the sample light enters the sample tissue through the sample module and is reflected back to the beam splitting module along the optical path, and the sample module is connected with a first module for driving the sample module to displace. Two displacement mechanisms;

an imaging module, configured to receive the reference light reflected back by the reference module and the interference light formed on the beam splitting module by the sample light reflected back by the sample tissue, and generate an image according to the interference light .

The light source module is used to provide a line beam. The line beam is divided into reference light and sample light through the beam splitting module. The reference light passes through the reference module and is reflected back to the beam splitting module along the original optical path. The original optical path is reflected back to the beam splitting module, the reflected reference light and the reflected sample light are mixed on the beam splitting module to form interference light, and the interference light is irradiated on the imaging module to generate an image. The reference module is moved, and the sample module is moved by the second displacement mechanism to realize detection at different depths. After the sample light passes through the sample module, the focus falls on the sample tissue, and the interference light formed by reflection and mixing is focused on the imaging module. Combined with the RCM And the advantages of OCT, it has the beneficial effects of high resolution and large detection depth.

Further, in this application, the reference module includes a first doublet lens, a first microscope objective lens and a reflection sheet, and the first doublet lens is used to receive the reference light emitted from the beam splitting module , the first microscope objective lens is used for receiving the reference light passing through the first doublet lens, and the reflection sheet is used for receiving and reflecting the reference light passing through the first microscope objective lens, so that all The reference light is returned to the beam splitting module along the incident light path.

The chromatic aberration is eliminated by the first doublet lens, thereby improving the image quality.

Further, in the present application, the first double cemented lens is formed by cementing a first biconvex lens and a first concave-convex lens, the first biconvex lens is arranged on the side close to the beam splitting module, and the first The curvature radius of one side of the biconvex lens close to the beam splitter module is 31.69mm, the curvature radius of the other side is -28.45mm, and the thickness is 8mm. The curvature radius of the first meniscus lens close to the beam splitter module is -28.45mm, the radius of curvature on the other side is -161.05mm, and the thickness is 4mm.

Further, in this application, the sample module includes a second doublet lens, a second microscope objective lens and a window, and the second doublet lens is used to receive the sample light emitted from the beam splitting module , the second microscope objective lens is used for receiving the sample light passing through the second doublet lens, the window is used for receiving the sample light passing through the second microscope objective lens, the sample light into the sample tissue through the window.

Chromatic aberration is eliminated by a second doublet lens, thereby improving image quality.

Further, in the present application, the second double cemented lens is formed by cementing a second lenticular lens and a second concave-convex lens, the second lenticular lens is arranged on the side close to the beam splitting module, and the second lenticular lens is The curvature radius of one side of the biconvex lens close to the beam splitting module is 31.69mm, the curvature radius of the other side is -28.45mm, and the thickness is 8mm. The curvature radius of the second meniscus lens close to the beam splitting module is -28.45mm, the radius of curvature on the other side is -161.05mm, and the thickness is 4mm.

Further, in this application, the imaging module includes a third doublet lens and a line scan camera, the third doublet lens is used for receiving the interference light and focusing the interference light on the line scan camera Above, the line scan camera converts the interference light into an electrical signal to generate an image.

Further, in the present application, the third double-cemented lens is formed by cementing a third double-convex lens and a third concave-convex lens, the third double-convex lens is arranged on a side close to the beam splitting module, and the third double-convex lens is The curvature radius of one side of the lenticular lens close to the beam splitter module is 36.27mm, the curvature radius of the other side is -33.8mm, and the thickness is 8mm. The curvature radius of the third meniscus lens close to the beam splitter module is -33.8mm, the radius of curvature on the other side is -248.86mm, and the thickness is 4mm.

Further, in this application, the beam splitting module is a non-polarized beam splitting cube.

Further, in this application, the light source module includes a laser, a fourth doublet lens and a fifth doublet lens, the laser outputs light to the fourth doublet lens, and the fourth doublet lens The light is converted into a Gaussian beam, and the fifth doublet lens is used to receive and focus the Gaussian beam into the line beam.

Further, in the present application, the fourth double cemented lens is formed by cementing a fourth convex-concave lens and a fourth double-convex lens, the fourth convex-concave lens is arranged on the side close to the laser, and the fourth convex-concave lens is The curvature radius of one side close to the laser is 57.3mm, the curvature radius of the other side is 9.545mm, and the thickness is 2mm. The curvature radius of the fourth lenticular lens close to the laser side is 9.545mm, and the other side The radius of curvature is -9.545mm, the thickness is 6.5mm, the fifth doublet lens is cemented by a fifth doublet lens and a fifth concave-convex lens, and the fifth doublet lens is arranged close to the fourth doublet lens. The curvature radius of one side of the fifth biconvex lens close to the fourth doublet lens is 30.922mm, the curvature radius of the other side is -40.11mm, and the thickness is 6.12mm, and the fifth meniscus lens is close to the The radius of curvature of one side of the fourth doublet lens is -40.11mm, the radius of curvature of the other side is -254.462mm, the thickness is 4.18mm, and the distance between the fourth doublet lens and the fifth doublet lens is 80mm .

It can be seen from the above that a line field confocal OCT device provided by the present application uses a light source module to provide a line beam, the line beam is divided into reference light and sample light through the beam splitting module, and the reference light passes through the reference module and follows the original optical path. After being reflected back to the beam splitter module, the sample light passes through the sample module to the sample tissue and then is reflected back to the beam splitter module along the original optical path. The reflected reference light and the reflected sample light are mixed on the beam splitter module to form interference light, and the interference light is irradiated on the beam splitter module. An image is generated on the imaging module. In this process, the reference module is moved by the first displacement mechanism, and the sample module is moved by the second displacement mechanism to realize detection at different depths. After the sample light passes through the sample module, the focus falls on the sample tissue. , the interference light formed by reflection and mixing is focused on the imaging module, which combines the advantages of RCM and OCT, and has the beneficial effects of high resolution and large detection depth.

Other features and advantages of the present application will be set forth in the description that follows, and, in part, will be apparent from the description, or learned by practice of the present application. The objectives and other advantages of the application may be realized and attained by the structure particularly pointed out in the written description, claims, and drawings.

Description of drawings

FIG. 1 is a schematic structural diagram of a line-field confocal OCT device provided by the present application.

FIG. 2 is a schematic structural diagram of a line-field confocal OCT device provided by the present application.

FIG. 3 is a schematic structural diagram of a line-field confocal OCT device provided by the present application.

FIG. 4 is a resolution-field size diagram of a line-field confocal OCT device provided by the present application.

In the figure: 100, light source module; 200, beam splitting module; 300, reference module; 400, sample module; 500, imaging module; 600, second displacement mechanism; 700, first displacement mechanism; 110, laser; 120, No. Four doublet lenses; 130, fifth doublet; 210, non-polarized beam splitter cube; 310, first doublet; 320, first microscope objective; 330, reflective sheet; 410, second doublet; 420, the second microscope objective; 430, the window; 510, the third doublet lens; 520, the line scan camera.

Detailed ways

The technical solutions in the present application will be clearly and completely described below with reference to the accompanying drawings in the present application. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all the embodiments. The components of the present application generally described and illustrated in the drawings herein may be arranged and designed in a variety of different configurations. Thus, the following detailed description of the embodiments of the application provided in the accompanying drawings is not intended to limit the scope of the application as claimed, but is merely representative of selected embodiments of the application. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without creative work fall within the protection scope of the present application.

It should be noted that like numerals and letters refer to like items in the following figures, so once an item is defined in one figure, it does not require further definition and explanation in subsequent figures. Meanwhile, in the description of the present application, the terms "first", "second", etc. are only used to distinguish the description, and cannot be understood as indicating or implying relative importance.

Please refer to FIG. 1 to FIG. 4 , a line-field confocal OCT device, the technical solution of which specifically includes:

a light source module 100 for providing a line beam;

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

The imaging module 500 is configured to receive 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 back by the sample tissue, and generate an image according to the interference light.

Through the above technical solution, the light source module 100 is used to provide the line beam, the line beam passes through the beam splitting module 200 and is divided into reference light and sample light, the reference light passes through the reference module 300 and is reflected back to the beam splitting module 200 along the original optical path, and the sample light After reaching the sample tissue through the sample module 400, it is reflected back to the beam splitting module 200 along the original optical path. The reflected reference light and the reflected sample light are mixed on the beam splitting module 200 to form interference light, and the interference light is irradiated on the imaging module 500 to further In this process, the reference module 300 is moved by the first displacement mechanism 700, and the sample module 400 is moved by the second displacement mechanism 600 to realize the detection of different depths of the sample tissue, and after the sample light passes through the sample module 400, the focus falls. On the sample tissue, the interference light formed by reflection and mixing is focused on the imaging module 500, thus combining the advantages of RCM and OCT, and having the beneficial effects of high resolution and large detection depth.

Further, as shown in FIGS. 2 and 3 , in some embodiments, the reference module 300 includes a first doublet lens 310 , a first microscope objective lens 320 and a reflection sheet 330 , and the first doublet lens 310 is used for receiving For the reference light emitted from the beam splitting module 200, the first microscope objective lens 320 is used for receiving the reference light passing through the first doublet lens 310, and the reflective sheet 330 is used for receiving and reflecting the reference light passing through the first microscope objective lens 320, so that the The reference light returns to the beam splitting module 200 along the incident light path.

Through the above technical solution, the first doublet lens 310 focuses the reference light on the first microscope objective lens 320, the reference light passes through the first microscope objective lens 320 and then irradiates on the reflective sheet 330, and then is reflected back to the beam splitting module 200 along the optical path, In this process, the first doublet lens 310 is used to eliminate chromatic aberration, and at the same time, the reference light is focused on the first microscope objective lens 320, thereby reducing loss and improving image quality.

Wherein, in some specific embodiments, the first microscope objective lens 320 can be a commonly used microscope objective lens in the market. As a preferred solution, the first microscope objective lens 320 in this application is a 20x0.85na of the Nikon CFI Super Fluor series. microscope objective.

Wherein, in some specific implementations, the first double-convex lens 310 is formed by cementing a first double-convex lens and a first concave-convex lens, the first double-convex lens is disposed on the side close to the beam splitting module 200 , and the first double-convex lens is close to the beam splitter The curvature radius of one side of the module 200 is 31.69mm, the curvature radius of the other side is -28.45mm, and the thickness is 8mm. The radius is -161.05mm and the thickness is 4mm. The material of the first lenticular lens is n-lak22, and the material of the first meniscus lens is n-sf6. Moreover, the distance between the first meniscus lens and the first microscope objective lens 320 is 80 mm, the distance between the first microscopic objective lens 320 and the reflection sheet 330 is 1 mm, and the distance between the first lenticular lens and the beam splitting module 200 is 42.605 mm.

The focal length of the first doublet lens 310 is 50mm.

Among them, in some specific embodiments, the reflective sheet 330 is a neutral density reflective sheet, which is a coated glass sheet. According to the principle of thin film interference, part of the light is transmitted and another part of the light is reflected. to adjust the illumination intensity of the reference light reflected to the beam splitting module 200 .

Further, in some of the embodiments, the sample module 400 includes a second doublet lens 410 , a second microscope objective lens 420 and a window 430 , and 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 430 is used for receiving the sample light passing through the second microscope objective 420 , and the sample light passes through the window 430 into the sample tissue.

Through the above technical solution, the second doublet lens 410 focuses the sample light on the second microscope objective lens 420 , and the second microscope objective lens 420 focuses the sample light again. At this time, the sample light is highly focused and then irradiated through the window 430 On the sample tissue, it is then reflected back to the beam splitting module 200 along the optical path. During this process, the second doublet lens 410 is used to focus the sample light on the second microscope objective lens 420 to reduce loss and reduce chromatic aberration. to improve image quality.

Wherein, in some specific embodiments, the second microscope objective lens 420 can be a commonly used microscope objective lens in the market. As a preferred solution, the second microscope objective lens 420 in this application is a Nikon Nikon CFI Super Fluor series 20x0.85na microscope objective.

Wherein, in some specific embodiments, the second double-convex lens 410 is formed by cementing a second double-convex lens and a second concave-convex lens, the second double-convex lens is disposed on the side close to the beam splitting module 200 , and the second double-convex lens is close to the beam splitter The curvature radius of one side of the module 200 is 31.69mm, the curvature radius of the other side is -28.45mm, and the thickness is 8mm. The radius is -161.05mm and the thickness is 4mm. Wherein, the material of the second lenticular lens is n-lak22, and the material of the second meniscus lens is n-sf6. In addition, the distance between the second meniscus lens and the second microscope objective lens 420 is 80 mm, the distance between the second microscopic objective lens 420 and the window 430 is 1 mm, and the distance between the second lenticular lens and the beam splitting module 200 is 42.605 mm.

The focal length of the second doublet lens 410 is 50mm.

Among them, the window sheet 430 is used to provide protection, so as to avoid the interference of the external environment when the sample light is transmitted in the sample module 400 . In other embodiments, the window sheet 430 may also be removed.

Further, in some of the embodiments, the imaging module 500 includes a third doublet lens 510 and a line scan camera 520. The third doublet lens 510 is used for receiving the interference light and focusing the interference light on the line scan camera 520. The camera 520 converts the interference light into electrical signals to generate images.

Through the above technical solution, the third doublet lens 510 focuses the interference light on the line scan camera 520, and the third doublet lens 510 is used to focus and eliminate chromatic aberration. In the line-field confocal light path, only the lines on the focal plane are emitted. Only the light can reach the line scan camera 520 for imaging; the light emitted by the lines outside the focal plane is defocused on the image plane, and most of the light cannot reach the light sensor of the line scan camera 520 . Therefore, the observation object on the focal plane appears bright color, while the non-observation point appears black as the background, which increases the contrast and makes the image clearer. The line scan camera 520 is made to form high-quality images.

Further, in some of the embodiments, the third double-convex lens 510 is formed by cementing a third double-convex lens and a third concave-convex lens. The curvature radius of one side of the beam module 200 is 36.27mm, the curvature radius of the other side is -33.8mm, and the thickness is 8mm. The curvature radius of the third meniscus lens close to the beam splitting module 200 is -33.8mm. The radius of curvature is -248.86mm and the thickness is 4mm. The material of the third biconvex lens is n-lak22, and the material of the third meniscus lens is n-sf6. In addition, the distance between the third meniscus lens and the line scan camera 520 is 52.955 mm, and the distance between the third bi-convex lens and the beam splitting module 200 is 52.955 mm.

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

Among them, as a preferred embodiment, the line scan camera 520 can be a 2048-pixel cmos camera EV71YO1CUB2210-BB1 from e2v company, and an area scan camera can also be used to replace the line scan camera 520 .

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

Through the above technical solution, the non-polarization beam splitter cube 210 can divide the light into two directions at the same ratio regardless of the wavelength and polarization state of the light, thereby forming the reference light and the sample light, which are used for the subsequent formation of interference light, and pass through Interferometric light imaging.

Further, in some of the embodiments, the light source module 100 includes a laser 110 , a fourth doublet lens 120 and a fifth doublet lens 130 , the laser 110 is used for outputting light to the fourth doublet lens 120 , and the fourth doublet lens 120 is used to convert the light into a Gaussian beam, and the fifth doublet lens 130 is used to receive the Gaussian beam and focus it into a line beam. Wherein, in some specific embodiments, a xenon lamp can be used instead of the laser 110 as a light source.

Through the above technical solution, light is generated by the laser 110, wherein the laser 110 can be a supercontinuum laser, and an ultra-short pulse laser is used to couple into a highly nonlinear fiber, usually a photonic crystal fiber PCF, because the nonlinear effect of the fiber, four-wavelength The frequency mixing and optical soliton effect broaden the pulse spectrum of the output light, the spectrum width is from 0.4um to 2.4um, so as to achieve ultra-wide spectrum output, and the light is emitted to the fourth doublet lens 120, and the fourth doublet lens 120 The light is converted into a Gaussian beam of approximately parallel light, and the Gaussian beam is irradiated on the fifth doublet lens 130, and the fifth doublet lens 130 focuses the Gaussian beam into a line beam and outputs it.

Wherein, in some specific implementations, 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 on the side close to the laser 110 , and the fourth convex-concave lens is close to the laser 110 side The curvature radius of the lens is 57.3mm, the curvature radius of the other side is 9.545mm, and the thickness is 2mm. The curvature radius of the fourth lenticular lens near the laser 110 is 9.545mm. 6.5mm, the fifth doublet lens 130 is formed by cementing a fifth doublet lens and a fifth concave-convex lens, the fifth doublet lens is arranged on the side close to the fourth doublet lens 120, and the fifth doublet lens is close to the fourth doublet lens 120 The curvature radius of one side is 30.922mm, the curvature radius of the other side is -40.11mm, and the thickness is 6.12mm. The curvature radius of the fifth meniscus lens close to the fourth doublet 120 is -40.11mm. The radius of curvature is -254.462mm, the thickness is 4.18mm, the distance between the fourth doublet lens 120 and the fifth doublet lens 130 is 80mm, and the distance between the fifth doublet lens 130 and the beam splitting module 200 is 62.605mm.

Wherein, in some specific embodiments, the focal length of the fourth doublet lens 120 is 15mm, and the focal length of the fifth doublet lens 130 is 75mm.

Specifically, as a preferred solution, in this application, the optical system parameters of the light emitted from the laser 110 to the window 430 are shown in the following table:

The light system parameters of the light emitted from the laser 110 to the reflection sheet 330 are shown in the following table:

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

In addition, in some specific embodiments, the first displacement mechanism 700 and the second displacement mechanism 600 are PZT mobile stages. In order to ensure the imaging clarity, the second displacement mechanism 600 drives the second microscope objective lens 420 and the window 430 to move, A full-depth scan of the sample tissue is then performed. Among them, the PZT translation stage is a piezoelectric translation stage driven by piezoelectric ceramics as a basic element, and the driving form is a mechanism amplification type. Under the same driving voltage, the displacement of the mechanism amplification platform is several to dozens of times that of the direct drive platform, with nanometer-level resolution and millisecond-level response time.

The first displacement mechanism 700 drives the first objective microscope 320 and the reflection sheet 330 to move, and the moving positions are determined according to the moving positions of the second objective lens 420 and the window 430 driven by the second displacement mechanism 600 .

Wherein, since the first displacement mechanism 700 drives the first microscope objective lens 320 to move, in some embodiments, the distance between the first microscope objective lens 320 and the first doublet lens 310 is 80mm-80.7mm.

Similarly, the distance between the second microscope objective lens 420 and the second doublet lens 410 is 80mm-80.7mm.

Moreover, in the solution of the present 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 from five related frames E1, E2, E3, E4, and E5. According to (E4−E2)^2−(E1− E3)(E3− E5), between every two adjacent frames The phase difference is π∕2. In some embodiments, the central wavelength of the light source is 800 nm, and the refractive index of the sample tissue is set to 1.5, then the distance that the first displacement mechanism 700 needs to move per frame is 800/(4*1.5)=133.3 nm. This shift produces an optical phase shift of π∕2. During the whole process of the second displacement mechanism 600 performing the depth scan, the first displacement mechanism 700 should run in such an oscillating manner. Among them, 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 solution of the present application uses an ultra-broadband light source to provide light for detection, focuses the light through the fifth doublet lens 130, and only performs one-dimensional imaging, thereby improving the signal-to-noise ratio, and does not Expensive spectral devices such as practical gratings, spectrometers, and swept-frequency lasers are required, which effectively reduces costs while ensuring detection quality.

The specific imaging effect is shown in Fig. 4. With the solution of the present application, the resolution can reach 1.4um, and the field of view is 0.98mm.

The above descriptions are merely examples of the present application, and are not intended to limit the protection scope of the present application. For those skilled in the art, various modifications and changes may be made to the present application. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of this application shall be included within the protection scope of this application.

Claims (10)

1. A line-field confocal OCT device, comprising a light source module (100) for providing a line beam, characterized in that it also comprises: a beam splitting module (200) for receiving the line beam and dividing the line beam into reference light and sample light; A reference module (300), configured to receive the reference light and reflect the reference light to the beam splitting module (200), the reference module (300) is connected with a reference module (300) for driving the reference module (300) to displace the first displacement mechanism (700); A sample module (400) 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 an optical path, the sample module (400) A second displacement mechanism (600) for driving the sample module (400) to displace is connected; An imaging module (500), configured to receive the reference light reflected back by the reference module (300) and the interference formed on the beam splitting module (200) by the sample light reflected back by the sample tissue light from which an image is generated. 2 . The line-field confocal OCT device according to claim 1 , wherein the reference module ( 300 ) comprises a first doublet lens ( 310 ), a first microscope objective lens ( 320 ) and a reflection sheet. 3 . (330), the first doublet lens (310) is configured to receive the reference light emitted from the beam splitting module (200), and the first microscope objective lens (320) is configured to receive the reference light emitted from the beam splitting module (200). The reference light of a double cemented lens (310), the reflection sheet (330) is used for receiving and reflecting the reference light passing through the first microscope objective lens (320), so that the reference light follows the incident light path Return to the beam splitting module (200). 3. A line-field confocal OCT device according to claim 2, wherein the first doublet lens (310) is formed by cementing a first biconvex lens and a first meniscus lens, and the first doublet lens (310) The biconvex lens is arranged on the side close to the beam splitting module (200), the curvature radius of the first biconvex lens on the side close to the beam splitting module (200) is 31.69mm, and the curvature radius of the other side is -28.45mm , the thickness is 8mm, the curvature radius of one side of the first meniscus lens close to the beam splitting module (200) is -28.45mm, the curvature radius of the other side is -161.05mm, and the thickness is 4mm. The line-field confocal OCT device according to claim 1, wherein the sample module (400) comprises a second doublet lens (410), a second microscope objective lens (420) and a window (430), the second doublet lens (410) is used for receiving the sample light emitted from the beam splitting module (200), and the second microscope objective lens (420) is used for receiving the light passing through the first The sample light of the second doublet lens (410), the window (430) for receiving the sample light passing through the second microscope objective (420), the sample light passing through the window (430) into the sample tissue. 5. The line-field confocal OCT device according to claim 4, wherein the second doublet lens (410) is formed by cementing a second biconvex lens and a second meniscus lens, and the second doublet lens (410) The biconvex lens is arranged on the side close to the beam splitting module (200), the curvature radius of the second biconvex lens on the side close to the beam splitting module (200) is 31.69mm, and the curvature radius of the other side is -28.45mm , the thickness is 8mm, the curvature radius of one side of the second meniscus lens close to the beam splitting module (200) is -28.45mm, the curvature radius of the other side is -161.05mm, and the thickness is 4mm. 6. The line-field confocal OCT device according to claim 1, wherein the imaging module (500) comprises a third doublet lens (510) and a line scan camera (520), the third The doublet lens (510) is used for receiving the interference light and focusing the interference light on the line scan camera (520), and the line scan camera (520) converts the interference light into electrical signals to generate electrical signals image. 7 . The line-field confocal OCT device according to claim 6 , wherein the third doublet lens ( 510 ) is formed by cementing a third biconvex lens and a third meniscus lens, and the third The lenticular lens is arranged on the side close to the beam splitting module (200), the curvature radius of the third lenticular lens on one side close to the beam splitting module (200) is 36.27mm, and the curvature radius of the other side is -33.8mm , the thickness is 8mm, the curvature radius of one side of the third meniscus lens close to the beam splitting module (200) is -33.8mm, the curvature radius of the other side is -248.86mm, and the thickness is 4mm. 8. The line-field confocal OCT device according to claim 1, wherein the beam splitting module (200) is a non-polarized beam splitting cube (210). 9. The line-field confocal OCT device according to claim 1, wherein the light source module (100) comprises a laser (110), a fourth doublet lens (120) and a fifth doublet lens ( 130), the laser (110) is used for outputting light to the fourth doublet lens (120), the fourth doublet lens (120) is used for converting the light into a Gaussian beam, the fifth A doublet (130) is used to receive the Gaussian beam and focus it into the line beam. 10 . The line-field confocal OCT device according to claim 9 , wherein the fourth doublet lens (120) is formed by cementing a fourth convex-concave lens and a fourth biconvex lens, and the fourth The convex-concave lens is arranged on the side close to the laser (110), the curvature radius of the fourth convex-concave lens is 57.3mm on one side close to the laser (110), the curvature radius on the other side is 9.545mm, and the thickness is 2mm, The radius of curvature of one side of the fourth biconvex lens close to the laser (110) is 9.545mm, the radius of curvature of the other side is -9.545mm, and the thickness is 6.5mm, and the fifth doublet lens (130) is formed by the Five biconvex lenses and a fifth concave-convex lens are cemented together, the fifth biconvex lens is arranged on the side close to the fourth doublet lens (120), and the fifth biconvex lens is close to the fourth doublet lens (120). ) the radius of curvature of one side is 30.922mm, the radius of curvature of the other side is -40.11mm, the thickness is 6.12mm, the radius of curvature of the side of the fifth meniscus lens close to the fourth doublet lens (120) is - 40.11mm, the curvature radius of the other side is -254.462mm, the thickness is 4.18mm, and the distance between the fourth doublet lens (120) and the fifth doublet lens (130) is 80mm.

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