A line-field confocal OCT device

Abstract

The present application provides a line-field confocal OCT device, which relates to the field of medical diagnosis technology. The key points of its technical solution are: including a light source module for providing a line beam; a beam splitting module for receiving the line beam and splitting the line beam into a reference beam and a sample light; a reference module for receiving the reference light and reflecting the reference light to the beam splitting module, the reference module is connected to a first displacement mechanism for driving the reference module to move; a sample module for receiving the sample light, the sample light passes through the sample module into the sample tissue and is reflected back to the beam splitting module along the optical path, the sample module is connected to a second displacement mechanism for driving the sample module to move; an imaging module is used to receive the reference light reflected back by the reference module and the interference light formed by the sample light reflected back by the sample tissue on the beam splitting module, and generate an image based on the interference light. The line-field confocal OCT device provided by the present application has the advantages of high resolution and large detection depth.

Description

Technical Field

[0001] The present application relates to the field of medical diagnosis technology, and in particular to a line-field confocal OCT device. Background Art

[0002] For early diagnosis of cancer, diagnostic modalities using noninvasive imaging technologies have been developed to provide earlier and more accurate detection of malignant lesions.

[0003] Clinically available techniques that can image the skin in vivo with the highest spatial resolution are, for example, reflectance confocal microscopy (RCM), optical coherence tomography (OCT), and fluorescence microscopy. RCM is an optical technique that provides frontal cross-sectional images of tissues with a spatial resolution comparable to that of histology, approximately 1 μm. RCM has been shown to improve diagnostic accuracy. However, the main limitation of RCM is the relatively poor penetration in tissues, which is only about 200 μm, making it impossible to image structures located in the tissue. Another major problem is the interpretation of RCM slices, since they are oriented frontally, i.e. perpendicular to the traditional vertical orientation of tissue slices. OCT is an interferometric optical imaging modality. OCT produces cross-sectional images of the skin with a resolution of a few microns, which is significantly lower than that of RCM. However, the skin penetration depth of OCT is higher than that of RCM, which is approximately 1 mm. The possibility to evaluate OCT images in a vertically oriented view makes them easier to compare with traditional tissue slices. OCT has been applied in the diagnosis of various cancers. However, diagnosis using OCT is not as accurate as using RCM, mainly because of the insufficient imaging resolution of OCT.

[0004] In order to solve the above problems, the inventors combined the advantages of RCM and OCT in terms of spatial resolution, penetration and image direction and proposed a line-field confocal OCT solution. Summary of the invention

[0005] The purpose of the present application is to provide a line-field confocal OCT device having the advantages of high resolution and large detection depth.

[0006] In the first aspect, the present application provides a line-field confocal OCT device, and the technical solution is as follows:

[0007] The invention comprises a light source module for providing a line light beam, and further comprises:

[0008] A beam splitting module, used for receiving the line light beam and splitting the line light beam into a reference light and a sample light;

[0009] A reference module, used for receiving the reference light and reflecting the reference light to the beam splitting module, wherein the reference module is connected to a first displacement mechanism for driving the reference module to move;

[0010] A sample module, used for receiving the sample light, the sample light passes through the sample module, enters the sample tissue, and is reflected back to the beam splitting module along the optical path, and the sample module is connected to a second displacement mechanism for driving the sample module to move;

[0011] The imaging module is used to receive 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 generate an image according to the interference light.

[0012] A light source module is used to provide a line beam, which is divided into a reference light and a sample light after passing through a beam splitting module. The reference light is reflected back to the beam splitting module along the original light path after passing through the reference module. The sample light is reflected back to the beam splitting module along the original light path after passing through the sample module and reaching the sample tissue. The reflected reference light and the reflected sample light are mixed on the beam splitting module to form interference light, which is irradiated on the imaging module to generate an image. In this process, the reference module is moved by a first displacement mechanism, and the sample module is moved by a second displacement mechanism to achieve 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. The advantages of RCM and OCT are combined, and the beneficial effects of high resolution and large detection depth are achieved.

[0013] Furthermore, in the present application, the reference module includes a first double-cemented lens, a first microscope objective and a reflective plate, the first double-cemented lens is used to receive the reference light emitted from the beam splitting module, the first microscope objective is used to receive the reference light passing through the first double-cemented lens, and the reflective plate is used to receive and reflect the reference light passing through the first microscope objective, so that the reference light returns to the beam splitting module along the incident light path.

[0014] The first double cemented lens is used to eliminate chromatic aberration, thereby improving the imaging quality.

[0015] Furthermore, in the present application, the first double-glued lens is formed by gluing a first double convex lens and a first concave-convex lens, and the first double convex lens is arranged on the side close to the beam splitting module, the curvature radius of the first double convex lens close to the beam splitting module is 31.69mm, the curvature radius on the other side is -28.45mm, and the thickness is 8mm; the curvature radius of the first concave-convex lens close to the beam splitting module is -28.45mm, the curvature radius on the other side is -161.05mm, and the thickness is 4mm.

[0016] Furthermore, in the present application, the sample module includes a second double-cemented lens, a second microscope objective and a window plate, the second double-cemented lens is used to receive the sample light emitted from the beam splitting module, the second microscope objective is used to receive the sample light passing through the second double-cemented lens, and the window plate is used to receive the sample light passing through the second microscope objective, and the sample light passes through the window plate into the sample tissue.

[0017] The second double-cemented lens is used to eliminate chromatic aberration and thus improve image quality.

[0018] Furthermore, in the present application, the second double-glued lens is formed by gluing a second double convex lens and a second concave-convex lens, and the second double convex lens is arranged on the side close to the beam splitting module, the curvature radius of the second double convex lens close to the beam splitting module is 31.69mm, the curvature radius on the other side is -28.45mm, and the thickness is 8mm, the curvature radius of the second concave-convex lens close to the beam splitting module is -28.45mm, the curvature radius on the other side is -161.05mm, and the thickness is 4mm.

[0019] Furthermore, in the present application, the imaging module includes a third doublet lens and a line array camera, the third doublet lens is used to receive the interference light and focus the interference light on the line array camera, and the line array camera converts the interference light into an electrical signal to generate an image.

[0020] Furthermore, in the present application, the third double-glued lens is formed by gluing a third double convex lens and a third concave-convex lens, and the third double convex lens is arranged on the side close to the beam splitting module, the curvature radius of the third double convex lens close to the beam splitting module is 36.27mm, the curvature radius on the other side is -33.8mm, and the thickness is 8mm; the curvature radius of the third concave-convex lens close to the beam splitting module is -33.8mm, the curvature radius on the other side is -248.86mm, and the thickness is 4mm.

[0021] Furthermore, in the present application, the beam splitting module is a non-polarizing beam splitting cube.

[0022] Furthermore, in the present application, the light source module includes a laser, a fourth double-cemented lens and a fifth double-cemented lens, the laser outputs light to the fourth double-cemented lens, the fourth double-cemented lens converts the light into a Gaussian beam, and the fifth double-cemented lens is used to receive the Gaussian beam and focus it into the line beam.

[0023] Further, in the present application, the fourth double-cemented lens is formed by cementing a fourth convex-concave lens and a fourth biconvex lens, the fourth convex-concave lens is arranged on the side close to the laser, the curvature radius of the fourth convex-concave lens 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 biconvex lens close to the laser is 9.545mm, the curvature radius of the other side is -9.545mm, and the thickness is 6.5mm, the fifth double-cemented lens is formed by cementing a fifth biconvex lens and a fourth biconvex lens, the fourth convex-concave lens is arranged on the side close to the laser, the curvature radius of the fourth convex-concave lens 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 biconvex lens close to the laser is 9.545mm, the curvature radius of the other side is -9.545mm, and the thickness is 6.5mm, Five concave-convex lenses are glued together, the fifth biconvex lens is arranged on the side close to the fourth biconvex lens, the curvature radius of the fifth biconvex lens close to the fourth biconvex lens 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 concave-convex lens close to the fourth biconvex lens is -40.11mm, the curvature radius of the other side is -254.462mm, and the thickness is 4.18mm. The distance between the fourth biconvex lens and the fifth biconvex lens is 80mm.

[0024] As can be seen from the above, a line-field confocal OCT device provided by the present application utilizes a light source module to provide a line light beam, and the line light beam is divided into a reference light and a sample light through a beam splitting module. After passing through the reference module, the reference light is reflected back to the beam splitting module along the original light path, and after passing through the sample module and reaching the sample tissue, the sample light is reflected back to the beam splitting module along the original light path. 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. In this process, the reference module is moved by a first displacement mechanism, and the sample module is moved by a second displacement mechanism to achieve 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. The advantages of RCM and OCT are combined, and the beneficial effects of high resolution and large detection depth are achieved.

[0025] Other features and advantages of the present application will be described in the following description, and partly become apparent from the description, or be understood by practicing the present application. The purpose and other advantages of the present application can be realized and obtained by the structures specifically pointed out in the written description, claims, and drawings. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 This is a schematic diagram of the structure of a line-field confocal OCT device provided in this application.

[0027] Figure 2 This is a schematic diagram of the structure of a line-field confocal OCT device provided in this application.

[0028] Figure 3This is a schematic diagram of the structure of a line-field confocal OCT device provided in this application.

[0029] Figure 4 A resolution-field-of-view diagram of a line-field confocal OCT device provided in the present application.

[0030] 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, fourth double-cemented lens; 130, fifth double-cemented lens; 210, non-polarizing beam splitting cube; 310, first double-cemented lens; 320, first microscope objective; 330, reflector; 410, second double-cemented lens; 420, second microscope objective; 430, window plate; 510, third double-cemented lens; 520, linear array camera. DETAILED DESCRIPTION

[0031] The technical solutions in the present application will be clearly and completely described below in conjunction with the 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 shown in the drawings here can be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present application provided in the drawings is not intended to limit the scope of the present application for protection, but merely represents the selected embodiments of the present application. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without making creative work belong to the scope of protection of the present application.

[0032] It should be noted that similar reference numerals and letters represent similar items in the following drawings, so once an item is defined in one drawing, it does not need to be further defined and explained in subsequent drawings. At the same time, in the description of this application, the terms "first", "second", etc. are only used to distinguish the description and cannot be understood as indicating or implying relative importance.

[0033] Please refer to Figures 1 to 4 , a line-field confocal OCT device, the technical solution of which specifically includes:

[0034] The light source module 100 is used to provide a line beam;

[0035] A beam splitting module 200, used for receiving a line beam and splitting the line beam into a reference beam and a sample beam;

[0036] A reference module 300, used for receiving reference light and reflecting the reference light to the beam splitting module 200, the reference module 300 is connected to a first displacement mechanism 700 for driving the reference module 300 to move;

[0037] The sample module 400 is used to receive the sample light. The sample light passes through the sample module 400 and enters the sample tissue and is reflected back to the beam splitting module 200 along the optical path. The sample module 400 is connected to a second displacement mechanism 600 for driving the sample module 400 to move.

[0038] The imaging module 500 is used to receive the interference light formed on the beam splitting module 200 by the reference light reflected by the reference module 300 and the sample light reflected by the sample tissue, and to generate an image according to the interference light.

[0039] Through the above technical solution, the light source module 100 is used to provide a line light beam, and the line light beam is divided into a reference light and a sample light through the beam splitting module 200. The reference light passes through the reference module 300 and is reflected back to the beam splitting module 200 along the original light path. The sample light passes through the sample module 400 and reaches the sample tissue and is reflected back to the beam splitting module 200 along the original light 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 generate an image. 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 detection of different depths of the sample tissue. After the sample light passes through the sample module 400, the focus falls on the sample tissue, and the interference light formed by reflection and mixing is focused on the imaging module 500. Therefore, the advantages of RCM and OCT are combined, and the beneficial effects of high resolution and large detection depth are achieved.

[0040] Furthermore, if Figure 2 , Figure 3 As shown, in some embodiments, the reference module 300 includes a first double-cemented lens 310, a first microscope objective lens 320 and a reflective plate 330. The first double-cemented lens 310 is used to receive the reference light emitted from the beam splitting module 200, the first microscope objective lens 320 is used to receive the reference light passing through the first double-cemented lens 310, and the reflective plate 330 is used to receive and reflect the reference light passing through the first microscope objective lens 320, so that the reference light returns to the beam splitting module 200 along the incident light path.

[0041] Through the above technical solution, the first double-cemented lens 310 focuses the reference light on the first microscope objective lens 320. After passing through the first microscope objective lens 320, the reference light is irradiated on the reflective plate 330, and then reflected back to the beam splitting module 200 along the optical path. In this process, the first double-cemented lens 310 is used to eliminate chromatic aberration and focus the reference light on the first microscope objective lens 320, thereby reducing loss and improving imaging quality.

[0042] In some specific implementations, the first microscope objective lens 320 can be a microscope objective lens commonly used in the market. As a preferred solution, the first microscope objective lens 320 in the present application is a 20x0.85na microscope objective lens of the Nikon CFI Super Fluor series.

[0043] In some specific embodiments, the first double-cemented lens 310 is formed by gluing a first double convex lens and a first concave-convex lens. The first double convex lens is arranged on the side close to the beam splitting module 200. The radius of curvature of the first double convex lens close to the beam splitting module 200 is 31.69 mm, the radius of curvature of the other side is -28.45 mm, and the thickness is 8 mm. The radius of curvature of the first concave-convex lens close to the beam splitting module 200 is -28.45 mm, the radius of curvature of the other side is -161.05 mm, and the thickness is 4 mm. The material of the first double convex lens is n-lak22, and the material of the first concave-convex lens is n-sf6. In addition, the distance between the first concave-convex lens and the first microscope objective lens 320 is 80 mm, the distance between the first microscope objective lens 320 and the reflector 330 is 1 mm, and the distance between the first double convex lens and the beam splitting module 200 is 42.605 mm.

[0044] The focal length of the first double-cemented lens 310 is 50 mm.

[0045] In some specific embodiments, the reflector 330 is a neutral density reflector, which is a coated glass sheet. According to the principle of thin film interference, it transmits part of the light and reflects the other part of the light. The light intensity of the reference light reflected to the beam splitting module 200 can be adjusted as needed.

[0046] Furthermore, in some embodiments, the sample module 400 includes a second doublet lens 410, a second microscope objective lens 420 and a window piece 430. The second doublet lens 410 is used to receive the sample light emitted from the beam splitting module 200, the second microscope objective lens 420 is used to receive the sample light passing through the second doublet lens 410, and the window piece 430 is used to receive the sample light passing through the second microscope objective lens 420. The sample light passes through the window piece 430 and enters the sample tissue.

[0047] Through the above technical solution, the second double-cemented 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 passes through the window piece 430 to illuminate the sample tissue, and then is reflected back to the beam splitting module 200 along the optical path. In this process, the second double-cemented lens 410 is used to focus the sample light on the second microscope objective lens 420, reducing loss and at the same time reducing chromatic aberration, thereby improving imaging quality.

[0048] In some specific implementations, the second microscope objective lens 420 can be a microscope objective lens commonly used in the market. As a preferred solution, the second microscope objective lens 420 in the present application is a 20x0.85na microscope objective lens of the Nikon CFI Super Fluor series.

[0049] In some specific embodiments, the second double-cemented lens 410 is formed by gluing a second double convex lens and a second concave-convex lens. The second double convex lens is arranged on the side close to the beam splitting module 200. The radius of curvature of the second double convex lens close to the beam splitting module 200 is 31.69 mm, the radius of curvature of the other side is -28.45 mm, and the thickness is 8 mm. The radius of curvature of the second concave-convex lens close to the beam splitting module 200 is -28.45 mm, the radius of curvature of the other side is -161.05 mm, and the thickness is 4 mm. The material of the second double convex lens is n-lak22, and the material of the second concave-convex lens is n-sf6. In addition, the distance between the second concave-convex lens and the second microscope objective lens 420 is 80 mm, the distance between the second microscope objective lens 420 and the window 430 is 1 mm, and the distance between the second double convex lens and the beam splitting module 200 is 42.605 mm.

[0050] The focal length of the second double-cemented lens 410 is 50 mm.

[0051] The window sheet 430 is used to provide protection to prevent the sample light from being disturbed by the external environment when being transmitted in the sample module 400. In other embodiments, the window sheet 430 may also be removed.

[0052] Furthermore, in some of the embodiments, the imaging module 500 includes a third doublet lens 510 and a line array camera 520, the third doublet lens 510 is used to receive interference light and focus the interference light on the line array camera 520, and the line array camera 520 converts the interference light into an electrical signal to generate an image.

[0053] Through the above technical solution, the third double-cemented lens 510 focuses the interference light on the line array camera 520, and the third double-cemented lens 510 is used to focus and eliminate chromatic aberration. In the line field confocal optical path, only the light emitted by the lines on the focal plane can reach the line array camera 520 for imaging; the light emitted by the lines outside the focal plane is defocused on the image plane, and most of it cannot reach the photosensitive element of the line array camera 520. Therefore, the observation target on the focal plane appears bright, while the non-observation point appears black as the background, which increases the contrast and makes the image clearer. The third double-cemented lens 510 allows the focus to fall on the photosensitive element of the line array camera 520, so that the line array camera 520 forms a high-quality image.

[0054] Furthermore, in some of the embodiments, the third double-cemented lens 510 is formed by gluing a third double convex lens and a third concave-convex lens, the third double convex lens is arranged on the side close to the beam splitting module 200, the radius of curvature of the third double convex lens close to the beam splitting module 200 is 36.27 mm, the radius of curvature of the other side is -33.8 mm, and the thickness is 8 mm, the radius of curvature of the third concave-convex lens close to the beam splitting module 200 is -33.8 mm, the radius of curvature of the other side is -248.86 mm, and the thickness is 4 mm. Among them, the material of the third double convex lens is n-lak22, and the material of the third concave-convex lens is n-sf6. In addition, the distance between the third concave-convex lens and the linear array camera 520 is 52.955 mm, and the distance between the third double convex lens and the beam splitting module 200 is 52.955 mm.

[0055] In some specific implementations, the focal length of the third doublet lens 510 is 60 mm.

[0056] As a preferred implementation, the line array camera 520 may adopt the 2048-pixel CMOS camera EV71YO1CUB2210-BB1 produced by e2v. In addition, the line array camera 520 may also be replaced by an area array camera.

[0057] Furthermore, in some of the embodiments, the beam splitting module 200 is a non-polarizing beam splitting cube 210 .

[0058] Through the above technical solution, the non-polarizing beam splitter cube 210 can split the light into two directions at the same ratio regardless of the wavelength and polarization state of the light, thereby forming reference light and sample light for subsequent formation of interference light and imaging through interference light.

[0059] Furthermore, 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. The laser 110 is used to output light to the fourth double-cemented lens 120. The fourth double-cemented lens 120 is used to convert the light into a Gaussian beam. The fifth double-cemented lens 130 is used to receive the Gaussian beam and focus it into a line beam. In some specific embodiments, a xenon lamp can be used as a light source instead of the laser 110.

[0060] Through the above technical solution, the laser 110 generates light, wherein the laser 110 can be a supercontinuum laser, and uses ultrashort pulse laser to couple into a high nonlinear optical fiber, usually a photonic crystal fiber PCF. Due to the nonlinear effect, four-wave mixing and soliton effect of the optical fiber, the pulse spectrum of the output light is broadened, and the spectrum width is from 0.4um to 2.4um, thereby achieving ultra-wide spectrum output, and the light is emitted to the fourth double-cemented lens 120, and the fourth double-cemented lens 120 converts the light into a Gaussian beam of approximately parallel light. The Gaussian beam is irradiated on the fifth double-cemented lens 130, and the fifth double-cemented lens 130 focuses the Gaussian beam into a line beam and outputs it.

[0061] Among them, in some specific embodiments, the fourth double-cemented lens 120 is formed by bonding a fourth convex-concave lens and a fourth biconvex lens, the fourth convex-concave lens is arranged on the side close to the laser 110, the curvature radius of the fourth convex-concave lens close to the laser 110 is 57.3mm, the curvature radius of the other side is 9.545mm, and the thickness is 2mm, the curvature radius of the fourth biconvex lens close to the laser 110 is 9.545mm, the curvature radius of the other side is -9.545mm, and the thickness is 6.5mm, the fifth double-cemented lens 130 is formed by bonding a fifth biconvex lens and a fifth concave-convex lens, and the fifth biconvex lens The mirror is arranged on the side close to the fourth double-glued lens 120, the curvature radius of the fifth double-convex lens close to the fourth double-glued lens 120 is 30.922mm, the curvature radius on the other side is -40.11mm, and the thickness is 6.12mm, the curvature radius of the fifth concave-convex lens close to the fourth double-glued lens 120 is -40.11mm, the curvature radius on the other side is -254.462mm, and the thickness is 4.18mm, the distance between the fourth double-glued lens 120 and the fifth double-glued lens 130 is 80mm, and the distance between the fifth double-glued lens 130 and the beam splitting module 200 is 62.605mm.

[0062] In some specific implementations, the focal length of the fourth doublet lens 120 is 15 mm, and the focal length of the fifth doublet lens 130 is 75 mm.

[0063] Specifically, as a preferred solution, in this application, the optical system parameters of the light from the laser 110 to the window 430 are shown in the following table:

[0064]

[0065] The light system parameters of the light from the laser 110 to the reflector 330 are shown in the following table:

[0066]

[0067] The optical system parameters of the interference light from the beam splitting module 220 to the line array camera 520 are shown in the following table:

[0068]

[0069] In addition, in some specific embodiments, the first displacement mechanism 700 and the second displacement mechanism 600 are PZT moving stages. In order to ensure the clarity of the imaging, the second displacement mechanism 600 drives the second microscope objective lens 420 and the window plate 430 to move, thereby performing a full-depth scan of the sample tissue. Among them, the PZT translation stage is a piezoelectric translation stage driven by piezoelectric ceramics as the 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.

[0070] The first displacement mechanism 700 drives the first microscope lens 320 and the reflector 330 to move, and the moving position is determined by the moving position of the second microscope lens 420 and the window sheet 430 driven by the second displacement mechanism 600 .

[0071] 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 80 mm-80.7 mm.

[0072] Similarly, the distance between the second microscope objective lens 420 and the second doublet lens 410 is 80 mm-80.7 mm.

[0073] Moreover, in the solution of the present application, a 5-frame phase shift method is used to improve the signal-to-noise ratio of the image. The algorithm needs to be calculated from 5 related frames E1, E2, E3, E4, and E5. According to (E4−E2)^2−(E1− E3)(E3− E5), the phase difference between each two adjacent frames is π∕2. In some embodiments, the central wavelength of the light source is 800nm, 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)=133.3nm. This displacement produces an optical phase shift of π∕2. During the entire process of the second displacement mechanism 600 performing the depth scan, the first displacement mechanism 700 must oscillate in this way. Among them, in the above formula, one wavelength is 2Pi, so the distance corresponding to pi / 2 needs to be divided by 4.

[0074] Compared with traditional OCT, the technical solution of the present application uses an ultra-wideband light source to provide light for detection, focuses the light through the fifth double-cemented lens 130, and only performs one-dimensional imaging, thereby improving the signal-to-noise ratio, and does not require expensive spectral devices such as practical gratings, spectrometers, and swept lasers, thereby effectively reducing costs while ensuring detection quality.

[0075] Specific imaging effects such as Figure 4 As shown, through the solution of the present application, the resolution can reach 1.4um and the field of view is 0.98mm.

[0076] The above description is only an embodiment of the present application and is not intended to limit the scope of protection of the present application. For those skilled in the art, the present application may have various modifications and variations. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application shall be included in the scope of protection of the present application.

Claims

1. A line-field confocal OCT device, comprising a light source module (100) for providing a line beam, characterized in that: Also includes: A beam splitting module (200), used for receiving the line light beam and splitting the line light beam into reference light and sample light; A reference module (300) for receiving the reference light and reflecting the reference light to the beam splitting module (200), the reference module (300) being connected to a first displacement mechanism (700) for driving the reference module (300) to perform displacement; A sample module (400) is used to receive the sample light, the sample light passes through the sample module (400) and enters the sample tissue and is reflected back to the beam splitting module (200) along the optical path, and the sample module (400) is connected to a second displacement mechanism (600) for driving the sample module (400) to move; The imaging module (500) is used 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 by the sample tissue, and to generate an image based on the interference light.

2. A line-field confocal OCT device according to claim 1, characterized in that: The reference module (300) comprises a first double-cemented lens (310), a first microscope objective lens (320) and a reflective sheet (330); the first double-cemented lens (310) is used to receive the reference light emitted from the beam splitting module (200); the first microscope objective lens (320) is used to receive the reference light passing through the first double-cemented lens (310); and the reflective sheet (330) is used to receive and reflect the reference light passing through the first microscope objective lens (320), so that the reference light returns to the beam splitting module (200) along the incident light path.

3. A line-field confocal OCT device according to claim 2, characterized in that: The first double-glued lens (310) is formed by gluing a first double-convex lens and a first concave-convex lens, the first double-convex lens is arranged on a side close to the beam splitting module (200), the radius of curvature of the first double-convex lens on the side close to the beam splitting module (200) is 31.69 mm, the radius of curvature of the other side is -28.45 mm, and the thickness is 8 mm, the radius of curvature of the first concave-convex lens on the side close to the beam splitting module (200) is -28.45 mm, the radius of curvature of the other side is -161.05 mm, and the thickness is 4 mm.

4. The linear field confocal OCT device according to claim 1, characterized in that: The sample module (400) includes a second doublet lens (410), a second microscope objective lens (420), and a window plate (430); the second doublet lens (410) is used to receive the sample light emitted from the beam splitting module (200); the second microscope objective lens (420) is used to receive the sample light passing through the second doublet lens (410); the window plate (430) is used to receive the sample light passing through the second microscope objective lens (420); and the sample light passes through the window plate (430) and enters the sample tissue.

5. A line-field confocal OCT device according to claim 4, characterized in that: The second double-cemented lens (410) is formed by gluing a second double-convex lens and a second concave-convex lens, the second double-convex lens is arranged on a side close to the beam splitting module (200), the radius of curvature of the second double-convex lens on the side close to the beam splitting module (200) is 31.69 mm, the radius of curvature on the other side is -28.45 mm, and the thickness is 8 mm; the radius of curvature of the second concave-convex lens on the side close to the beam splitting module (200) is -28.45 mm, the radius of curvature on the other side is -161.05 mm, and the thickness is 4 mm.

6. The linear field confocal OCT device according to claim 1, characterized in that: The imaging module (500) comprises a third doublet lens (510) and a line array camera (520), wherein the third doublet lens (510) is used to receive the interference light and focus the interference light on the line array camera (520), and the line array camera (520) converts the interference light into an electrical signal to generate an image.

7. A line-field confocal OCT device according to claim 6, characterized in that: The third double-glued lens (510) is formed by gluing 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 (200). The radius of curvature of the third double-convex lens on the side close to the beam splitting module (200) is 36.27 mm, the radius of curvature of the other side is -33.8 mm, and the thickness is 8 mm. The radius of curvature of the third concave-convex lens on the side close to the beam splitting module (200) is -33.8 mm, the radius of curvature of the other side is -248.86 mm, and the thickness is 4 mm.

8. The linear field confocal OCT device according to claim 1, characterized in that: The beam splitting module (200) is a non-polarizing beam splitting cube (210).

9. The linear field confocal OCT device according to claim 1, characterized in that: The light source module (100) comprises a laser (110), a fourth double-cemented lens (120) and a fifth double-cemented lens (130), wherein the laser (110) is used to output light to the fourth double-cemented lens (120), the fourth double-cemented lens (120) is used to convert the light into a Gaussian beam, and the fifth double-cemented lens (130) is used to receive the Gaussian beam and focus it into the line beam.

10. The linear field confocal OCT device according to claim 9, characterized in that: The fourth double-cemented lens (120) is formed by cementing a fourth convex-concave lens and a fourth biconvex lens. The fourth convex-concave lens is arranged on a side close to the laser (110). The curvature radius of the fourth convex-concave lens on the side close to the laser (110) is 57.3 mm, the curvature radius of the other side is 9.545 mm, and the thickness is 2 mm. The curvature radius of the fourth biconvex lens on the side close to the laser (110) is 9.545 mm, the curvature radius of the other side is -9.545 mm, and the thickness is 6.5 mm. The fifth double-cemented lens (130) is formed by cementing a fifth biconvex lens and a fifth concave-convex lens. The fifth double convex lens is arranged on a side close to the fourth double glued lens (120); the curvature radius of the fifth double convex lens on the side close to the fourth double glued lens (120) is 30.922 mm, the curvature radius on the other side is -40.11 mm, and the thickness is 6.12 mm; the curvature radius of the fifth concave-convex lens on the side close to the fourth double glued lens (120) is -40.11 mm, the curvature radius on the other side is -254.462 mm, and the thickness is 4.18 mm; the distance between the fourth double glued lens (120) and the fifth double glued lens (130) is 80 mm.

Images