In-vivo skin optical detection device
Through the coordinated cooperation of epidermal imaging module, confocal microscopy module and Raman scattering module in the body skin optical detection device, the problems of inactivity and iatrogenic damage of skin live section detection in the prior art are solved, and non-invasive skin three-dimensional structure and component information detection is realized.
Patent Information
- Application Number
- CN202421437775.0
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- Filing Date
- 2024-06-21
- Publication Date
- 2025-06-17
- Estimated Expiration
- 2034-06-21
AI Technical Summary
The prior art When detecting skin structure information and component information through live skin slices, there is a risk of inactivity and introduction of iatrogenic damage, which limits practical application.
An optical detection device in body skin is provided, including an epidermal imaging module, a confocal microscope module and a Raman scattering module. Through the coordinated cooperation of these modules, the detection of non-invasive three-dimensional structural information and three-dimensional component information of the skin is realized.
Non-invasive detection of the skin is achieved, the risk of inactive and iatrogenic damage is avoided, and a safer and more effective skin detection method is provided.
Smart Images
Figure CN222983032U_ABST
Abstract
Description
Technical Field
[0001] This application belongs to the technical field of skin micro-region structure imaging, and more specifically, relates to an in-vivo skin optical detection device. Background Art
[0002] The skin refers to the biological tissue covering the surface of the human body and directly contacting the external environment. It has a relatively complex morphological structure and composition. In order to deeply understand the physiological and pathological mechanisms of the skin and thus achieve the purposes of medical screening, disease treatment, and related research, etc., previously, the commonly used detection method in the medical field was to perform a skin biopsy, and then obtain the structural information and component information of the skin through a detection instrument. However, the above detection method has the risks of losing activity and introducing iatrogenic damage, resulting in limitations in practical applications. Summary of the Utility Model
[0003] The purpose of this application is to provide an in-vivo skin optical detection device, aiming to solve the problem that when detecting the structural information and component information of the skin through slicing at present, there are risks of losing activity and introducing iatrogenic damage, resulting in limitations in practical applications.
[0004] To achieve the above purpose, an in-vivo skin optical detection device is provided, including an epidermis imaging module, a confocal microscopy module, and a Raman scattering module. The epidermis imaging module is used to obtain the original epidermis image of the target area of the skin to be measured. The confocal microscopy module is used to obtain the three-dimensional structural information of the target area of the skin to be measured. The Raman scattering module is used to obtain the three-dimensional component information of the target area of the skin to be measured.
[0005] The epidermis imaging module includes a Kohler illumination module, a first beam splitter prism, an objective lens module, a scanning lens-tube lens group, a first lens, and a first imaging module. The objective lens module includes a fixed lens barrel with openings at both ends and an objective lens body movably arranged along the axial direction of the fixed lens barrel within the fixed lens barrel.
[0006] The Kohler illumination module is used to emit illumination light. The illumination light is reflected by the first beam splitter prism and focused by the objective lens body in sequence and then incident on the target area of the skin to be measured. The reflected light is transmitted through the objective lens body, the first beam splitter prism, the scanning lens-tube lens group, and the first lens in sequence and then focused and incident on the first imaging module to generate the original epidermis image of the target area of the skin to be measured.
[0007] In one embodiment, the confocal microscopy module includes a laser light source module, a neutral density filter, a second lens, a first confocal pinhole structure, a third lens, a polarization beam splitter prism, a scanning galvanometer, a second beam splitter prism, a quarter-wave plate, a fourth lens, a second confocal pinhole structure, and a second imaging module, and the scanning lens-tube lens group constitutes a 4f optical system.
[0008] The laser light source module is used to emit excitation light, and the excitation light is successively filtered by a neutral density filter, focused by a second lens, filtered by a first confocal pinhole structure, collimated by a third lens, vertically polarized by a polarization beam splitter prism, reflected by a scanning galvanometer, transmitted by a second beam splitter prism, transmitted by a scanning lens - tube lens group, polarized by a quarter - wave plate, transmitted by a first beam splitter prism, focused by an objective lens body and then incident on the skin target area to be measured to generate scattered light. The scattered light is successively transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter - wave plate, transmitted by the scanning lens - tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, transmitted by the polarization beam splitter prism, focused by a fourth lens, filtered by a second confocal pinhole structure and then incident on the second imaging module to generate three - dimensional structure information of the skin target area to be measured;
[0009] The corresponding illumination light is successively reflected by the first beam splitter prism, focused by the objective lens body and then incident on the skin target area to be measured. The reflected light is successively transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter - wave plate, transmitted by the scanning lens - tube lens group, reflected by the second beam splitter prism, focused by a first lens and then incident on the first imaging module to generate an original epidermis image of the skin target area to be measured.
[0010] In one embodiment, the Raman scattering module includes a third beam splitter prism, a long - pass filter, a fifth lens, an adjustable slit, a first concave mirror, a grating, a second concave mirror and a third imaging module;
[0011] The laser light source module is used to emit excitation light, and the excitation light is successively filtered by a neutral density filter, focused by a second lens, filtered by a first confocal pinhole structure, collimated by a third lens, vertically polarized by a polarization beam splitter prism, transmitted by the third beam splitter prism, reflected by the scanning galvanometer, transmitted by the second beam splitter prism, transmitted by the scanning lens - tube lens group, polarized by a quarter - wave plate, transmitted by a first beam splitter prism, focused by the objective lens body and then incident on the skin target area to be measured to generate scattered light. The scattered light is successively transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter - wave plate, transmitted by the scanning lens - tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, reflected by the third beam splitter prism, filtered by the long - pass filter, focused by the fifth lens, filtered by the adjustable slit, reflected by the first concave mirror, diffracted by the grating, reflected by the second concave mirror and then incident on the third imaging module to generate three - dimensional component information of the skin target area to be measured;
[0012] The corresponding excitation light is sequentially filtered by a neutral density filter, focused by a second lens, filtered by a first confocal pinhole structure, collimated by a third lens, vertically polarized by a polarization beam splitter prism, transmitted by a third beam splitter prism, reflected by a scanning galvanometer, transmitted by a second beam splitter prism, transmitted by a scanning lens-tube lens group, polarized by a quarter-wave plate, transmitted by a first beam splitter prism, and focused by an objective lens body and then incident on the skin target area to be measured. The scattered light is sequentially transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter-wave plate, transmitted by the scanning lens-tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, transmitted by the third beam splitter prism, transmitted by the polarization beam splitter prism, focused by a fourth lens, filtered by a second confocal pinhole structure, and then incident on the second imaging module to generate three-dimensional structure information of the skin target area to be measured.
[0013] In one embodiment, an optical path adjustment module is further included. The optical path adjustment module includes a first plane mirror and a second plane mirror. After the excitation light is collimated by the third lens, it is reflected by the first plane mirror to the polarization beam splitter prism. After the scattered light is focused by the third lens, it is reflected by the second plane mirror to the second confocal pinhole structure.
[0014] In one embodiment, the excitation light is a collimated light with a wavelength of 810 - 850 nm.
[0015] In one embodiment, a fixed platform and a three-axis motion module drivingly connected to the fixed platform are further included.
[0016] The beneficial effect of the in-vivo skin optical detection device provided by this application is that, compared with the prior art, the above in-vivo skin optical detection device includes an epidermis imaging module, a confocal microscopy module, and a Raman scattering module. Among them, the epidermis imaging module is used to obtain the original epidermis image of the skin target area to be measured, the confocal microscopy module is used to obtain the three-dimensional structure information of the skin target area to be measured, and the Raman scattering module is used to obtain the three-dimensional composition information of the skin target area to be measured. It can be seen that the above in-vivo skin optical detection device realizes non-invasive detection of the three-dimensional structure information and three-dimensional composition information of the skin through the coordinated cooperation of the epidermis imaging module, the confocal microscopy module, and the Raman scattering module, avoiding the risks of loss of activity and introduction of iatrogenic injury caused by skin biopsy. Description of the Drawings
[0017] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the following will briefly introduce the drawings required for use in the embodiments or the description of the prior art. Obviously, the following drawings are only some embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.
[0018] Figure 1Schematic diagram of the optical path structure of an in-vivo skin optical detection device provided by an embodiment of the present application;
[0019] Figure 2 For Figure 1 Schematic diagram of the optical path structure of the epidermal imaging module in the in-vivo skin optical detection device shown;
[0020] Figure 3 For Figure 1 Schematic diagram of the optical path structure of the confocal microscopy module in the in-vivo skin optical detection device shown;
[0021] Figure 4 For Figure 1 Schematic diagram of the optical path structure of the Raman scattering module in the in-vivo skin optical detection device shown.
[0022] In the figure: 10, in-vivo skin optical detection device; 20, skin target area to be measured; 100, epidermal imaging module; 110, Kohler illumination module; 120, first beam splitting prism; 130, objective lens module; 132, fixed lens barrel; 134, objective lens body; 136, sapphire light-transmitting lens; 140, scanning lens - tube lens group; 150, first lens; 160, first imaging module; 200, confocal microscopy module; 210, laser light source module; 220, neutral density filter; 230, second lens; 240, first confocal pinhole structure; 250, third lens; 260, polarization beam splitting prism; 270, scanning galvanometer; 280, second beam splitting prism; 290, quarter-wave plate; 292, fourth lens; 294, second confocal pinhole structure; 296, second imaging module; 300, Raman scattering module; 310, third beam splitting prism; 320, long-pass filter; 330, fifth lens; 340, adjustable slit; 350, first concave mirror; 360, grating; 370, second concave mirror; 380, third imaging module; 400, optical path adjustment module; 410, first plane mirror; 420, second plane mirror. Detailed implementation manners
[0023] In order to make the technical problems, technical solutions and beneficial effects to be solved by the present application clearer and more understandable, the present application will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and are not used to limit the present application.
[0024] It should be noted that when an element is referred to as "fixed to" or "disposed on" another element, it can be directly on the other element or indirectly on the other element. When an element is referred to as "connected to" another element, it can be directly connected to the other element or indirectly connected to the other element.
[0025] It should be understood that the orientation or positional relationship indicated by terms such as "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. is based on the orientation or positional relationship shown in the drawings. It is only for the convenience of describing the present application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation. Therefore, it should not be construed as a limitation to the present application.
[0026] In addition, the terms "first" and "second" are only used for descriptive purposes and should not be construed as indicating or implying relative importance or implicitly specifying the quantity of the indicated technical features. Thus, features defined with "first" and "second" may explicitly or implicitly include one or more of such features. In the description of the present application, the meaning of "a plurality" is two or more, unless otherwise specifically defined.
[0027] The skin refers to the biological tissue covering the surface layer of the human body and directly contacting the external environment. It has a relatively complex morphological structure and composition. In order to deeply understand the physiological and pathological mechanisms of the skin and then achieve the purposes of medical screening, disease treatment, and related research, etc., previously, the commonly used detection method in the medical field was to perform a skin biopsy, and then obtain the morphological information and component information of the skin through a detection instrument. However, the above detection method has the risks of losing activity and introducing iatrogenic injuries, resulting in limitations in practical applications.
[0028] With the progress of technology and the improvement of industrial demands, in recent years, skin detection based on the body surface has begun to pursue a real-time in-vivo dynamic three-dimensional detection and diagnosis mode. This mode can not only obtain the micron-level 3D morphological structure, composition, and distribution information of human skin tissue, deeply understand the physiological and pathological mechanisms of the skin, but also can online monitor the penetration, accumulation, and action processes of drug / cosmetic active ingredients in the human epidermis, and then clarify the information on the skin tissue metabolism and penetration pathways through the absorption mechanism and transfer kinetics of the skin tissue, so as to develop and evaluate new drugs or cosmetics.
[0029] However, so far, no instrument has been able to achieve high-resolution microscopic imaging of skin micro-region structures and spatial tomography of molecular structure analysis considering factors such as human skin harmfulness, imaging depth, optical resolution, and cost. That is, it is impossible to obtain both the structural information and compositional information of the skin simultaneously. In the field of skin imaging based on the body surface, for the in-vivo three-dimensional structure detection of the skin, the devices and technical methods that can reach the commercial application stage include dermoscopes, OCT optical coherence imaging, confocal microscopes, etc. They are often used to provide measurements of physiological parameters of skin conditions (such as color, erythema and pigmentation, induration, sebum and stratum corneum lipids, etc.). Since the in-vivo diagnosis of skin-related diseases based solely on visual inspection is often challenging, the detection of molecular structures, which focuses on the internal composition analysis of skin tissues, is more about the extraction and detection of quantitatively applied substances through tape stripping procedures and high-performance liquid chromatography after applying the corresponding substances to the skin. However, this method is destructive to the in-vivo skin itself, so it is usually limited in practical applications. There is an urgent need for non-destructive and more comprehensive analysis and detection techniques.
[0030] For the above problems, please refer to Figure 1 , this application provides an in-vivo skin optical detection device 10. The above in-vivo skin optical detection device 10 is suitable for real-time detection of the skin, and then obtaining the original epidermal image, three-dimensional structure information, and three-dimensional compositional information of the target area 20 of the skin to be measured. It can be understood that the above skin to be measured can be in-vivo skin or a skin section.
[0031] Please refer to Figure 1 and Figure 4 , in this embodiment, the above in-vivo skin optical detection device 10 includes an epidermal imaging module 100, a confocal microscopy module 200, and a Raman scattering module 300. Among them, the epidermal imaging module 100 is used to obtain the original epidermal image of the target area 20 of the skin to be measured, the confocal microscopy module 200 is used to obtain the three-dimensional structure information of the target area 20 of the skin to be measured, and the Raman scattering module 300 is used to obtain the three-dimensional compositional information of the target area of the skin.
[0032] The beneficial effect of the in-vivo skin optical detection device 10 provided by this application is that, compared with the prior art, the above in-vivo skin optical detection device 10 realizes non-invasive detection of the three-dimensional structure information and three-dimensional compositional information of the skin through the coordinated cooperation of the epidermal imaging module 100, the confocal microscopy module 200, and the Raman scattering module 300, avoiding the risks of loss of activity and introduction of iatrogenic injury caused by performing skin biopsies.
[0033] Please refer to Figure 2, in this embodiment, the above-mentioned epidermal imaging module 100 includes a Kohler illumination module 110, a first beam splitter prism 120, an objective lens module 130, a scanning lens-tube lens group 140, a first lens 150 and a first imaging module 160. Among them, the Kohler illumination module 110 is used to emit uniform illumination light. The scanning lens-tube lens group 140 is composed of one or more scanning lenses (not shown in the figure) and one or more tube lenses (not shown in the figure), and is further used to magnify the object image. The first imaging module 160 is a CCD or CMOS optical sensor.
[0034] Further, in this embodiment, the above-mentioned illumination light is reflected by the first beam splitter prism 120, focused by the objective lens module 130 in sequence, and then incident on the skin target area 20 to be measured to generate reflected light. The reflected light is transmitted through the objective lens module 130, transmitted through the first beam splitter prism 120, transmitted through the scanning lens-tube lens group 140, and focused by the first lens 150 in sequence, and then incident on the first imaging module 160 to generate an original epidermal image of the skin target area 20 to be measured.
[0035] Further, in this embodiment, the above-mentioned objective lens module 130 includes a fixed lens barrel 132, an objective lens body 134 and a sapphire light-transmitting lens 136. Among them, both ends of the fixed lens barrel 132 are open. The sapphire light-transmitting lens 136 is sealed at the opening of one end of the fixed lens barrel 132 facing the skin target area 20 to be measured. And the objective lens body 134 is axially movably arranged in the fixed lens barrel 132. In this way, by adjusting the position of the objective lens body 134, the focusing depth of the objective lens body 134 on the skin target area 20 to be measured can be adaptively adjusted. And during the detection process, the skin target area 20 to be measured is attached to the side of the sapphire light-transmitting lens 136 facing away from the objective lens body 134, and the fixed lens barrel 132 immediately isolates the environmental light from irradiating on the skin target area 20 to be measured.
[0036] Please refer to Figure 2 , in this embodiment, the above-mentioned illumination light is reflected by the first beam splitter prism 120, focused by the objective lens body 134, and transmitted through the sapphire light-transmitting lens 136 in sequence, and then incident on the skin target area 20 to be measured to generate reflected light. The reflected light is transmitted through the sapphire light-transmitting lens 136, transmitted through the objective lens body 134, transmitted through the first beam splitter prism 120, transmitted through the scanning lens-tube lens group 140, and focused by the first lens 150 in sequence, and then incident on the first imaging module 160 to generate an original epidermal image of the skin target area 20 to be measured.
[0037] Please refer to Figure 2 and Figure 3, in this embodiment, the above confocal microscopy module 200 includes a laser light source module 210, a neutral density filter 220, a second lens 230, a first confocal pinhole structure 240, a third lens 250, a polarization beam splitter prism 260, a scanning galvanometer 270, a second beam splitter prism 280, a quarter-wave plate 290, a fourth lens 292, a second confocal pinhole structure 294, and a second imaging module 296. The scanning lens-tube lens group 140 forms a 4f optical system. Among them, the laser light source module 210 is used to emit collimated excitation light with a wavelength of 810 - 850 nm, the neutral density filter 220 is used to control the illumination intensity of the excitation light, and the 4f optical system formed by the scanning lens-tube lens group 140 is used to ensure that the spot quality of the light reflected by the scanning galvanometer 270 is consistent when the scanning galvanometer 270 is at different angles. The second imaging module 296 is an APD optical sensor.
[0038] Further, in this embodiment, the above excitation light is sequentially filtered by the neutral density filter 220, focused by the second lens 230, filtered by the first confocal pinhole structure 240, collimated by the third lens 250, vertically polarized by the polarization beam splitter prism 260, reflected by the scanning galvanometer 270, transmitted by the second beam splitter prism 280, transmitted by the scanning lens-tube lens group 140, polarized by the quarter-wave plate 290, transmitted by the first beam splitter prism 120, focused by the objective lens body 134, transmitted by the sapphire transmissive lens 136, and then incident on the skin target area 20 to be measured to generate scattered light. The scattered light is sequentially transmitted by the sapphire transmissive lens 136, transmitted by the objective lens body 134, transmitted by the first beam splitter prism 120, polarized by the quarter-wave plate 290, transmitted by the scanning lens-tube lens group 140, transmitted by the second beam splitter prism 280, reflected by the scanning galvanometer 270, transmitted by the polarization beam splitter prism 260, focused by the fourth lens 292, filtered by the second confocal pinhole structure 294, and then incident on the second imaging module 296 to generate the three-dimensional structure information of the skin target area 20 to be measured.
[0039] Please refer to Figure 2 , in this embodiment, the above illumination light is sequentially reflected by the first beam splitter prism 120, focused by the objective lens body 134, transmitted by the sapphire transmissive lens 136, and then incident on the skin target area 20 to be measured. The reflected light is sequentially transmitted by the sapphire transmissive lens 136, transmitted by the objective lens body 134, transmitted by the first beam splitter prism 120, polarized by the quarter-wave plate 290, transmitted by the scanning lens-tube lens group 140, reflected by the second beam splitter prism 280, and focused by the first lens 150, and then incident on the first imaging module 160 to generate the original epidermal image of the skin target area 20 to be measured.
[0040] Please refer to Figure 4, in this embodiment, the wavelength of the above excitation light is 830 nm. The Raman scattering module 300 includes a third beam splitting prism 310, a long-pass filter 320, a fifth lens 330, an adjustable slit 340, a first concave mirror 350, a grating 360, a second concave mirror 370, and a third imaging module 380. Among them, the central wavelength of the long-pass filter 320 is the same as the wavelength of the excitation light emitted by the laser light source module 210, that is, 830 nm. Thus, it is used to filter the excitation light and Rayleigh scattered light emitted by the laser light source module 210, and retain the Stokes Raman scattered light with a wavelength greater than the original laser wavelength. The third imaging module 380 is a CCD optical sensor.
[0041] Further, in this embodiment, the above excitation light is sequentially filtered by the neutral density filter 220, focused by the second lens 230, filtered by the first confocal pinhole structure 240, collimated by the third lens 250, vertically polarized by the polarization beam splitting prism 260, transmitted through the third beam splitting prism 310, reflected by the scanning galvanometer 270, transmitted through the second beam splitting prism 280, transmitted through the scanning lens - tube lens group 140, polarized by the quarter-wave plate 290, transmitted through the first beam splitting prism 120, focused by the objective body 134, transmitted through the sapphire light-transmitting lens 136, and then incident on the skin target area 20 to be measured to generate scattered light. The scattered light is sequentially transmitted through the sapphire light-transmitting lens 136, transmitted through the objective body 134, transmitted through the first beam splitting prism 120, polarized by the quarter-wave plate 290, transmitted through the scanning lens - tube lens group 140, transmitted through the second beam splitting prism 280, reflected by the scanning galvanometer 270, reflected by the third beam splitting prism 310, filtered by the long-pass filter 320, focused by the fifth lens 330, filtered by the adjustable slit 340, reflected by the first concave mirror 350, diffracted by the grating 360, reflected by the second concave mirror 370, and then incident on the third imaging module 380 to generate the three-dimensional component information of the skin target area 20 to be measured.
[0042] Please refer to Figure 3, in this embodiment, the above-mentioned excitation light sequentially passes through the neutral density filter 220 for filtering, the second lens 230 for focusing, the first confocal pinhole structure 240 for filtering, the third lens 250 for collimation, the polarization beam splitter prism 260 for vertical polarization, the third beam splitter prism 310 for transmission, the scanning galvanometer 270 for reflection, the second beam splitter prism 280 for transmission, the scanning lens - tube lens group 140 for transmission, the quarter-wave plate 290 for polarization, the first beam splitter prism 120 for transmission, the objective lens body 134 for focusing, and the sapphire light-transmitting lens 136 for transmission, and then enters the skin target area 20 to be measured. The scattered light sequentially passes through the sapphire light-transmitting lens 136 for transmission, the objective lens body 134 for transmission, the first beam splitter prism 120 for transmission, the quarter-wave plate 290 for polarization, the scanning lens - tube lens group 140 for transmission, the second beam splitter prism 280 for transmission, the scanning galvanometer 270 for reflection, the third beam splitter prism 310 for transmission, the polarization beam splitter prism 260 for transmission, the fourth lens 292 for focusing, and the second confocal pinhole structure 294 for filtering, and then enters the second imaging module 296 to generate the three-dimensional structure information of the skin target area 20 to be measured.
[0043] Please refer to Figure 3 , in this embodiment, the in-vivo skin optical detection device 10 further includes an optical path adjustment module 400. The optical path adjustment module 400 includes a first plane mirror 410 and a second plane mirror 420. Among them, after the excitation light is collimated by the third lens 250, it is vertically reflected by the first plane mirror 410 to the polarization beam splitter prism 260. After the scattered light is focused by the fourth lens 292, it is vertically reflected by the second plane mirror 420 to the second confocal pinhole structure 294. It should be noted that the first plane mirror 410 and the second plane mirror 420 are only used to change the corresponding optical path directions in the in-vivo skin optical detection device 10, so as to facilitate the compact layout of the relevant optical elements in the in-vivo skin optical detection device 10 and effectively reduce the overall size of the in-vivo skin optical detection device 10.
[0044] It can be seen that the epidermis imaging module 100, the confocal microscopy module 200, and the Raman scattering module 300 in the above-mentioned in-vivo skin optical detection device 10 can synchronously obtain the original epidermis image, three-dimensional structure information, and three-dimensional composition information of the skin target area 20 to be measured. Moreover, the epidermis imaging module 100, the confocal microscopy module 200, and the Raman scattering module 300 realize the reuse of part of the optical path and part of the optical elements, effectively reducing the overall size and installation cost of the in-vivo skin optical detection device 10.
[0045] Further, in the present embodiment, the in-vivo skin optical detection device 10 further includes a three-axis motion module (not shown in the figure) and a fixed platform (not shown in the figure). Among them, the three-axis motion module is drivingly connected to the fixed platform. Thus, during the detection of the in-vivo skin, a limb with a skin target area 20 to be measured can be placed on the fixed platform, or a skin section with a skin target area 20 to be measured can be placed on the fixed platform. Then, the three-axis motion module drives the fixed platform to displace, so that the objective lens body 134 can accurately focus on the skin target area 20 to be measured under different circumstances.
[0046] The above are only the preferred embodiments of the present application and are not intended to limit the present application. Any modifications, equivalent replacements, and improvements made within the spirit and principle of the present application shall be included in the protection scope of the present application.
Claims
1. An in-body skin optical detection device, characterized in that: It includes an epidermal imaging module, a confocal microscopy module and a Raman scattering module. The epidermal imaging module is used to obtain an original epidermal image of a target skin area to be tested, the confocal microscopy module is used to obtain three-dimensional structural information of the target skin area to be tested, and the Raman scattering module is used to obtain three-dimensional composition information of the target skin area to be tested; The epidermal imaging module includes a Kohler illumination module, a first beam splitter prism, an objective lens module, a scanning lens-tube lens group, a first lens and a first imaging module, and the objective lens module includes a fixed lens barrel with openings at both ends and an objective lens body movably arranged in the fixed lens barrel along the axial direction of the fixed lens barrel; The Kohler illumination module is used to emit illumination light, which is sequentially reflected by the first dichroic prism, focused by the objective lens body, and then incident on the target skin area to be measured to generate reflected light, and the reflected light is sequentially transmitted by the objective lens body, the first dichroic prism, the scanning lens-tube lens group, and focused by the first lens, and then incident on the first imaging module to generate the original image of the epidermis of the target skin area to be measured.
2. The in-vivo skin optical detection device according to claim 1, characterized in that: The confocal microscopy module includes a laser light source module, a neutral density filter, a second lens, a first confocal pinhole structure, a third lens, a polarization beam splitter prism, a scanning galvanometer, a second beam splitter prism and a quarter wave plate, a fourth lens, a second confocal pinhole structure and a second imaging module, and the scanning lens-tube lens group constitutes a 4f optical system; The laser light source module is used to emit excitation light, which is sequentially filtered by the neutral density filter, focused by the second lens, filtered by the first confocal pinhole structure, collimated by the third lens, vertically polarized by the polarization beam splitter prism, reflected by the scanning galvanometer, transmitted by the second beam splitter prism, transmitted by the scanning lens-tube lens group, polarized by the quarter wave plate, transmitted by the first beam splitter prism, and focused by the objective lens body before being incident on the target skin area to be measured to generate scattered light, and the scattered light is sequentially transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter wave plate, transmitted by the scanning lens-tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, transmitted by the polarization beam splitter prism, focused by the fourth lens, and filtered by the second confocal pinhole structure before being incident on the second imaging module to generate the three-dimensional structural information of the target skin area to be measured; The corresponding illumination light is sequentially reflected by the first beam splitter prism, focused by the objective lens body, and then incident on the target skin area to be measured; the reflected light is sequentially transmitted by the objective lens body, the first beam splitter prism, polarized by the quarter wave plate, and transmitted by the scanning lens-tube lens group; the second beam splitter prism is reflected, focused by the first lens, and then incident on the first imaging module to generate the original epidermis image of the target skin area to be measured.
3. The in-vivo skin optical detection device according to claim 2, characterized in that: The Raman scattering module includes a third beam splitter prism, a long-pass filter, a fifth lens, an adjustable slit, a first concave reflector, a grating, a second concave reflector and a third imaging module; The laser light source module is used to emit the excitation light, which is sequentially filtered by the neutral density filter, focused by the second lens, filtered by the first confocal pinhole structure, collimated by the third lens, vertically polarized by the polarization beam splitter prism, transmitted by the third beam splitter prism, reflected by the scanning galvanometer, transmitted by the second beam splitter prism, transmitted by the scanning lens-tube lens group, polarized by the quarter wave plate, transmitted by the first beam splitter prism, and focused by the objective lens body before being incident on the target skin area to be measured and generating the scattered light, and the scattered light is sequentially transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter wave plate, transmitted by the scanning lens-tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, reflected by the third beam splitter prism, filtered by the long-pass filter, focused by the fifth lens, filtered by the adjustable slit, reflected by the first concave reflector, diffracted by the grating, and reflected by the second concave reflector before being incident on the third imaging module to generate the three-dimensional component information of the target skin area to be measured; The corresponding excitation light is filtered by the neutral density filter, focused by the second lens, filtered by the first confocal pinhole structure, collimated by the third lens, vertically polarized by the polarization beam splitter prism, transmitted by the third beam splitter prism, reflected by the scanning galvanometer, transmitted by the second beam splitter prism, transmitted by the scanning lens-tube lens group, polarized by the quarter wave plate, transmitted by the first beam splitter prism, and focused by the objective lens body before being incident on the target skin area to be measured. The scattered light is transmitted by the objective lens body, transmitted by the first beam splitter prism, polarized by the quarter wave plate, transmitted by the scanning lens-tube lens group, transmitted by the second beam splitter prism, reflected by the scanning galvanometer, transmitted by the third beam splitter prism, transmitted by the polarization beam splitter prism, focused by the fourth lens, and filtered by the second confocal pinhole structure before being incident on the second imaging module to generate the three-dimensional structural information of the target skin area to be measured.
4. The in-vivo skin optical detection device according to claim 3, characterized in that: It also includes an optical path adjustment module, which includes a first plane reflector and a second plane reflector. The excitation light is collimated by the third lens and then reflected by the first plane reflector to the polarization splitter prism. The scattered light is focused by the third lens and then reflected by the second plane reflector to the second confocal pinhole structure.
5. The in-body skin optical detection device according to any one of claims 2 to 4, characterized in that: The excitation light is a collimated light with a wavelength of 810-850nm.
6. The in-body skin optical detection device according to any one of claims 1 to 4, characterized in that: It also includes a fixed platform and a three-axis motion module which is driven and connected to the fixed platform.