CN118592899A - In vivo skin optical detection device - Google Patents

Abstract

The present application relates to the technical field of skin micro-region structure imaging, and provides an in vivo skin optical detection device, including an epidermal imaging module, a confocal microscopy module and a Raman scattering module, wherein the epidermal imaging module is used to obtain an original image of the epidermis of a target skin area to be measured, the confocal microscopy module is used to obtain three-dimensional structural information of the target skin area to be measured, and the Raman scattering module is used to obtain three-dimensional component information of the target skin area to be measured. It can be seen that the above-mentioned in vivo skin optical detection device realizes non-invasive detection of three-dimensional structural information and three-dimensional component information of the skin through the coordinated cooperation of the epidermal imaging module, the confocal microscopy module and the Raman scattering module, thereby avoiding the risk of loss of activity and introduction of iatrogenic damage in performing live skin sections.

Description

In vivo skin optical detection device

Technical Field

The present application belongs to the technical field of skin micro-region structure imaging, and more specifically, to an in-vivo skin optical detection device.

Background Art

Skin refers to the biological tissue that covers the surface of the human body and is in direct contact with the external environment. It has a relatively complex morphological structure and composition. In order to gain a deeper understanding of the physiological and pathological mechanisms of the skin, and thereby achieve the purposes of medical screening, disease treatment, and related research, the commonly used detection method in the medical field was to perform a live skin slice and then obtain the structural and composition information of the skin through a detection instrument. However, the above detection method has the risk of losing activity and introducing iatrogenic damage, which leads to limitations in practical applications.

Summary of the invention

The purpose of the present application is to provide an in vivo skin optical detection device, which aims to solve the problem that when the structural information and composition information of the skin is currently detected through slices, there is a risk of loss of activity and introduction of iatrogenic damage, which leads to limitations in practical applications.

To achieve the above-mentioned purpose, an in vivo skin optical detection device is provided, comprising an epidermal imaging module, a confocal microscopy module and a Raman scattering module. The epidermal imaging module, the confocal microscopy module and the Raman scattering module share a part of the optical path structure. The epidermal imaging module is used to obtain an original image of the epidermis of a target skin area to be measured, the confocal microscopy module is used to obtain three-dimensional structural information of the target skin area to be measured, and the Raman scattering module is used to obtain three-dimensional composition information of the target skin area to be measured.

In one embodiment, the epidermal imaging module includes a Kohler illumination module, a first beam splitter prism, an objective lens module, a scanning lens-tube lens assembly, a first lens, and a first imaging module;

The Kohler illumination module is used to emit illumination light, which is reflected by the first beam splitter prism in sequence, focused by the objective lens module, and then incident on the target skin area to be measured to generate reflected light, which is transmitted by the objective lens module, the first beam splitter prism, the scanning lens-tube lens group, and focused by the first lens before being incident on the first imaging module to generate an original image of the epidermis of the target skin area to be measured.

In one embodiment, the partial optical path structure shared by the epidermal imaging module, the confocal microscopy module and the Raman scattering module at least includes the first beam splitter prism, the objective lens module and the scanning lens-tube lens assembly.

In one embodiment, the objective lens module includes a fixed lens barrel and an objective lens body movably disposed in the fixed lens barrel along the axial direction of the fixed lens barrel, and the fixed lens barrel has two openings at both ends and one end facing the target skin area to be measured is provided with a sapphire light-transmitting lens that closes the corresponding opening;

The corresponding illumination light is sequentially reflected by the first beam splitter prism, focused by the objective lens body, and transmitted through the sapphire light-transmitting lens before entering the target skin area to be measured. The reflected light is sequentially transmitted through the sapphire light-transmitting lens, the objective lens body, the first beam splitter prism, the scanning lens-tube lens group, and focused by the first lens before entering the first imaging module to generate an original epidermal image of the target skin area to be measured.

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 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 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 polarizing beam splitter prism, reflected by a scanning galvanometer, transmitted by a second beam splitter prism, transmitted by a scanning lens-tube lens group, a quarter wave plate, transmitted by a first beam splitter prism, focused by an objective lens body, and transmitted by a sapphire light-transmitting lens before being incident on a target skin area to be measured to generate scattered light, and the scattered light is sequentially transmitted by a sapphire light-transmitting lens, transmitted by an objective lens body, transmitted by a first beam splitter prism, polarized by a quarter wave plate, transmitted by a scanning lens-tube lens group, transmitted by a second beam splitter prism, reflected by a scanning galvanometer, transmitted by a polarizing beam splitter prism, focused by a fourth lens, and filtered by a second confocal pinhole structure before being incident on a second imaging module to generate 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 transmitted through the sapphire light-transmitting lens before being incident on the target skin area to be measured; the reflected light is sequentially transmitted through the sapphire light-transmitting lens, the objective lens body, the first beam splitter prism, polarized by a quarter-wave plate, and transmitted through the scanning lens-tube lens group; the reflected light is sequentially transmitted through the second beam splitter prism, focused by the first lens, and then incident on the first imaging module to generate an original epidermal image of the target skin area to be measured.

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 reflector, a grating, a second concave reflector and a third imaging module;

The laser light source module is used to emit excitation light, which 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 polarizing 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, focused by an objective lens body, and transmitted by a sapphire light-transmitting lens, and then incident on a target skin area to be measured and generates scattered light. The scattered light is sequentially transmitted by a sapphire light-transmitting lens, transmitted by an objective lens body, transmitted by a first beam splitter prism, polarized by a quarter wave plate, transmitted by a scanning lens-tube lens group, transmitted by a second beam splitter prism, reflected by a scanning galvanometer, reflected by a third beam splitter prism, filtered by a long-pass filter, focused by a fifth lens, filtered by an adjustable slit, reflected by a first concave reflector, diffracted by a grating, and reflected by a second concave reflector, and then incident on a third imaging module to generate three-dimensional composition information of the target skin area to be measured;

The corresponding excitation light is 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 polarizing 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, focused by an objective lens body, and transmitted by a sapphire light-transmitting lens before being incident on a target skin area to be measured. The scattered light is transmitted by a sapphire light-transmitting lens, transmitted by an objective lens body, transmitted by a first beam splitter prism, polarized by a quarter wave plate, transmitted by a scanning lens-tube lens group, transmitted by a second beam splitter prism, reflected by a scanning galvanometer, transmitted by a third beam splitter prism, transmitted by a polarizing beam splitter prism, focused by a fourth lens, and filtered by a second confocal pinhole structure before being incident on a second imaging module to generate three-dimensional structural information of the target skin area to be measured.

In one embodiment, an optical path adjustment module is also included, which includes a first plane reflector and a second plane reflector. The excitation light is collimated by a 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.

In one embodiment, the excitation light is a collimated light with a wavelength of 810-850 nm.

In one embodiment, it also includes a fixed platform and a three-axis motion module drivingly connected to the fixed platform.

The beneficial effect of the in vivo skin optical detection device provided by the present application is that, compared with the prior art, the above-mentioned in vivo skin optical detection device includes an epidermal imaging module, a confocal microscopy module and a Raman scattering module, wherein the epidermal imaging module is used to obtain the original image of the epidermis of the target skin area to be tested, the confocal microscopy module is used to obtain the three-dimensional structural information of the target skin area to be tested, and the Raman scattering module is used to obtain the three-dimensional composition information of the target skin area to be tested. It can be seen that the above-mentioned in vivo skin optical detection device realizes non-invasive detection of the three-dimensional structural information and three-dimensional composition information of the skin through the coordinated cooperation of the epidermal imaging module, the confocal microscopy module and the Raman scattering module, thereby avoiding the risk of loss of activity and introduction of iatrogenic damage in live skin sections.

BRIEF DESCRIPTION OF THE DRAWINGS

In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

FIG1 is a schematic diagram of the optical path structure of an in-body skin optical detection device according to an embodiment of the present application;

FIG2 is a schematic diagram of the optical path structure of the epidermal imaging module in the in-vivo skin optical detection device shown in FIG1 ;

FIG3 is a schematic diagram of the optical path structure of a co-focusing microscopy module in the in vivo skin optical detection device shown in FIG1 ;

FIG4 is a schematic diagram of the optical path structure of the Raman scattering module in the in-vivo skin optical detection device shown in FIG1 ;

FIG5 is a schematic diagram of skin three-dimensional structure information;

FIG. 6 is a schematic diagram of three-dimensional skin composition information.

In the figure: 10, in vivo skin optical detection device; 20, target skin area to be tested; 100, epidermal imaging module; 110, Kohler illumination module; 120, first beam splitter 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 splitter prism; 270, scanning galvanometer; 280, second beam splitter prism; 290, quarter wave plate; 292, fourth lens; 294, second confocal pinhole structure; 296, second imaging module; 300, Raman scattering module; 310, third beam splitter prism; 320, long pass filter; 330, fifth lens; 340, adjustable slit; 350, first concave reflector; 360, grating; 370, second concave reflector; 380, third imaging module; 400, optical path adjustment module; 410, first plane reflector; 420, second plane reflector.

DETAILED DESCRIPTION

In order to make the technical problems, technical solutions and beneficial effects to be solved by this application more clearly understood, this application is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain this application and are not used to limit this application.

It should be noted that when an element is referred to as being "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 being "connected to" another element, it can be directly connected to the other element or indirectly connected to the other element.

It should be understood that the terms "length", "width", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating the orientation or position relationship, are based on the orientation or position relationship shown in the drawings, and are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as a limitation on the present application.

In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of the features. In the description of this application, the meaning of "plurality" is two or more, unless otherwise clearly and specifically defined.

Skin refers to the biological tissue that covers the surface of the human body and is in direct contact with the external environment. It has a relatively complex morphological structure and components. In order to gain a deeper understanding of the physiological and pathological mechanisms of the skin, and thereby achieve the purposes of medical screening, disease treatment, and related research, previously, the commonly used detection method in the medical field was to perform a live skin slice, and then obtain the skin's morphological and composition information through a detection instrument. However, the above detection method has the risk of losing activity and introducing iatrogenic damage, which leads to limitations in practical applications.

With the advancement of science and technology and the increase in industrial demand, in recent years, skin testing based on the body surface has begun to pursue real-time in-body 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, and deeply understand the physiological and pathological mechanisms of the skin, but also monitor the penetration, accumulation and action process of active ingredients of drugs/cosmetics in the human epidermis online, and then clarify the information of skin tissue metabolism and penetration pathways through the absorption mechanism and transport dynamics of skin tissue, and develop and evaluate new drugs or cosmetics.

However, there is no instrument that can achieve high-resolution microscopic imaging of skin microstructure and spatial tomography of molecular structure analysis under the consideration of factors such as human skin hazard, imaging depth, optical resolution, and cost. That is, it is impossible to obtain both the structural information and the composition information of the skin at the same time. In the field of skin imaging based on the body surface, the equipment and technical methods that can reach the commercial application stage for the in vivo three-dimensional structure detection of the skin include dermatoscopes, OCT optical coherence imaging, confocal microscopes, etc., which are often used to provide measurements of physiological parameters of skin conditions (such as color, erythema and pigmentation, nodules, 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 structure based on the analysis of the internal components of skin tissue is more about applying the corresponding substances to the skin, and then extracting and detecting the substances for quantitative application through tape stripping procedures and high-performance liquid chromatography. However, this method is destructive to the in vivo skin itself, so it is usually limited in practical applications. Non-destructive and more comprehensive analytical detection technology is urgently needed.

In response to the above problems, please refer to Figure 1. The present application provides an in vivo skin optical detection device 10. The above-mentioned in vivo skin optical detection device 10 is suitable for real-time detection of the skin, and then obtaining the original image of the epidermis, three-dimensional structure information and three-dimensional composition information of the target area 20 of the skin to be tested. It can be understood that the above-mentioned skin to be tested can be in vivo skin or a skin slice.

Please refer to Figures 1 to 6 together. In this embodiment, the above-mentioned in vivo skin optical detection device 10 includes an epidermal imaging module 100, a confocal microscopy module 200 and a Raman scattering module 300. The epidermal imaging module 100, the confocal microscopy module 200 and the Raman scattering module 300 share part of the optical path structure, wherein the epidermal imaging module 100 is used to obtain the original image of the epidermis of the target skin area 20 to be measured, the confocal microscopy module 200 is used to obtain the three-dimensional structural information of the target skin area 20 to be measured (i.e., as shown in Figure 5), and the Raman scattering module 300 is used to obtain the three-dimensional composition information of the target skin area to be measured (i.e., as shown in Figure 6).

The beneficial effect of the in vivo skin optical detection device 10 provided in the present application is that, compared with the prior art, the above-mentioned in vivo skin optical detection device 10 realizes non-invasive detection of the three-dimensional structural information and three-dimensional composition 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, thereby avoiding the risk of loss of activity and introduction of iatrogenic damage in live skin sections.

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 assembly 140, a first lens 150 and a first imaging module 160, wherein the Kohler illumination module 110 is used to emit uniform illumination light, the scanning lens-tube lens assembly 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, and the first imaging module 160 is a CCD or CMOS optical sensor.

Furthermore, in the present embodiment, the illumination light is sequentially reflected by the first beam splitter prism 120, focused by the objective lens module 130, and then incident on the target skin area 20 to be measured to generate reflected light; the reflected light is sequentially transmitted by the objective lens module 130, the first beam splitter prism 120, the scanning lens-tube lens assembly 140, and focused by the first lens 150, and then incident on the first imaging module 160 to generate an original image of the epidermis of the target skin area 20 to be measured.

Furthermore, in the present embodiment, the objective lens module 130 includes a fixed lens barrel 132, an objective lens body 134 and a sapphire light-transmitting lens 136, wherein both ends of the fixed lens barrel 132 are opened, the sapphire light-transmitting lens 136 is sealed in the opening of the fixed lens barrel 132 at one end facing the target skin area 20 to be measured, and the objective lens body 134 is movably arranged in the fixed lens barrel 132 along the axial direction of the fixed lens barrel 132, so that the focusing depth of the objective lens body 134 on the target skin area 20 to be measured can be adaptively adjusted by adjusting the position of the objective lens body 134, and, during the detection process, the target skin 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 is immediately isolated from ambient light and irradiated on the target skin area 20 to be measured.

Please refer to Figure 2. In this embodiment, the above-mentioned illumination light is respectively reflected by the first beam splitter prism 120, focused by the objective lens body 134, and transmitted by the sapphire transparent lens 136, and then incident on the target skin area 20 to be measured and generates reflected light. The reflected light is sequentially transmitted by the sapphire transparent lens 136, the objective lens body 134, the first beam splitter prism 120, the scanning lens-tube lens group 140, and focused by the first lens 150, and then incident on the first imaging module 160 to generate an original image of the epidermis of the target skin area 20 to be measured.

Please refer to Figures 2 and 3. In this embodiment, the above-mentioned 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, and the scanning lens-tube lens group 140 constitutes a 4f optical system, wherein the laser light source module 210 is used to emit collimated excitation light with a wavelength of 810-850nm, the neutral density filter 220 is used to control the light intensity of the excitation light, and the 4f optical system constituted by the scanning lens-tube lens group 140 is used to ensure that during the scanning process of the scanning galvanometer 270, the quality of the light spot reflected by the scanning galvanometer 270 is consistent when the scanning galvanometer 270 is at different angles, and the second imaging module 296 is an APD optical sensor.

Further, in this embodiment, the 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 assembly 140, polarized by the quarter wave plate 290, transmitted by the first beam splitter prism 120, focused by the objective lens body 134, and transmitted by the sapphire light-transmitting lens 136 before being incident on the skin to be measured. The skin target area 20 generates scattered light, which is sequentially transmitted through the sapphire transparent lens 136, the objective lens body 134, the first beam splitter prism 120, the quarter wave plate 290 polarization, the scanning lens-tube lens assembly 140, the second beam splitter prism 280, the scanning galvanometer 270, the polarization beam splitter prism 260, the fourth lens 292 focusing, the second confocal pinhole structure 294 filtering, and then incident on the second imaging module 296 to generate three-dimensional structural information of the skin target area 20 to be measured.

Please refer to Figure 2. In this embodiment, the above-mentioned illumination light is respectively reflected by the first beam splitter prism 120, focused by the objective lens body 134, and transmitted by the sapphire transparent lens 136 before being incident on the target skin area 20 to be measured. The reflected light is sequentially transmitted by the sapphire transparent 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 before being incident on the first imaging module 160 to generate an original image of the epidermis of the target skin area 20 to be measured.

Please refer to FIG. 4. In this embodiment, the above

The wavelength of the excitation light is 830nm. The Raman scattering module 300 includes a third beam splitter prism 310, a long-pass filter 320, a fifth lens 330, an adjustable slit 340, a first concave reflector 350, a grating 360, a second concave reflector 370 and a third imaging module 380. The central wavelength of the long-pass filter 320 is consistent with the wavelength of the excitation light emitted by the laser light source module 210, that is, 830nm, and is further 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.

Further, in the present embodiment, the 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, transmitted by the third beam splitter prism 310, reflected by the scanning galvanometer 270, transmitted by the second beam splitter prism 280, transmitted by the scanning lens-tube lens assembly 140, polarized by the quarter wave plate 290, transmitted by the first beam splitter prism 120, focused by the objective lens body 134, and transmitted by the sapphire light-transmitting lens 136, and then incident on the target skin area 20 to be measured and generates scattered light. The scattered light is sequentially transmitted through the sapphire light-transmitting lens 136, the objective lens body 134, the first beam splitter prism 120, the quarter-wave plate 290 for polarization, the scanning lens-tube lens assembly 140, the second beam splitter prism 280, the scanning galvanometer 270, the third beam splitter prism 310, the long-pass filter 320, the fifth lens 330 for focusing, the adjustable slit 340 for filtering, the first concave reflector 350 for reflection, the grating 360 for diffraction, and the second concave reflector 370 for reflection before entering the third imaging module 380 to generate three-dimensional composition information of the target skin area 20 to be measured.

Please refer to FIG. 3 . In the present embodiment, the excitation light is 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 260, transmitted by the third beam splitter prism 310, reflected by the scanning galvanometer 270, transmitted by the second beam splitter prism 280, transmitted by the scanning lens-tube lens assembly 140, polarized by the quarter wave plate 290, transmitted by the first beam splitter prism 120, focused by the objective lens body 134, and incident by the sapphire light-transmitting lens 136. To the target skin area 20 to be measured, the scattered light is transmitted in sequence through the sapphire transparent lens 136, the objective lens body 134, the first beam splitter prism 120, the quarter wave plate 290 polarization, the scanning lens-tube lens assembly 140, the second beam splitter prism 280, the scanning galvanometer 270, the third beam splitter prism 310, the polarization beam splitter prism 260, the fourth lens 292 focuses, and the second confocal pinhole structure 294 filters the light before entering the second imaging module 296 to generate the three-dimensional structural information of the target skin area 20 to be measured.

Please refer to Figure 3. In this embodiment, the above-mentioned in vivo skin optical detection device 10 also includes an optical path adjustment module 400, and the optical path adjustment module 400 includes a first plane reflector 410 and a second plane reflector 420, wherein the excitation light is collimated by the third lens 250, and then vertically reflected to the polarization splitter prism 260 by the first plane reflector 410, and the scattered light is focused by the fourth lens 292, and then vertically reflected to the second confocal pinhole structure 294 by the second plane reflector 420. It should be noted that the first plane reflector 410 and the second plane reflector 420 are only used to change the corresponding light path direction in the in vivo skin optical detection device 10, thereby facilitating the compact layout of related optical elements in the in vivo skin optical detection device 10, and effectively reducing the overall size of the in vivo skin optical detection device 10.

It can be seen that the epidermal 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 image of the epidermis, the three-dimensional structure information and the three-dimensional composition information of the target skin area 20 to be tested, and the epidermal 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, which effectively reduces the overall size and installation cost of the in vivo skin optical detection device 10.

Furthermore, in the present embodiment, the above-mentioned in vivo skin optical detection device 10 also includes a three-axis motion module (not shown in the figure) and a fixed platform (not shown in the figure), wherein the three-axis motion module drives the connection to the fixed platform. Thus, during the detection of the in vivo skin, the limb having the target skin area 20 to be tested can be placed on the fixed platform, or the skin slice having the target skin area 20 to be tested can be placed on the fixed platform. The three-axis motion module then drives the fixed platform to move, so that the objective lens body 134 can be accurately focused on the target skin area 20 to be tested under different circumstances.

The above description is only a preferred embodiment of the present application and is not intended to limit the present application. Any modifications, equivalent substitutions and improvements made within the spirit and principles of the present application should be included in the protection scope of the present application.

Claims (9)

1. The utility model provides an in-vivo skin optical detection device which characterized in that, includes epidermis imaging module, confocal microscopic module and raman scattering module, epidermis imaging module confocal microscopic module with raman scattering module shares partial light path structure, epidermis imaging module is used for obtaining the epidermis primitive image of skin target area that awaits measuring, confocal microscopic module is used for obtaining the three-dimensional structure information of skin target area that awaits measuring, raman scattering module is used for obtaining the three-dimensional composition information of skin target area that awaits measuring.

2. The in-vivo skin optical detection device of claim 1, wherein the epidermal imaging module comprises a kohler illumination module, a first beam splitting prism, an objective lens module, a scanning lens-tube lens group, a first lens, and a first imaging module;

The kohler illumination module is used for emitting illumination light, the illumination light is reflected by the first light splitting prism in sequence, is focused by the objective lens module and then is incident to the skin target area to be detected, and generates reflected light, and the reflected light is transmitted by the objective lens module, is transmitted by the first light splitting prism, is transmitted by the scanning lens-tube lens group, is focused by the first lens and then is incident to the first imaging module, so that the epidermis original image of the skin target area to be detected is generated.

3. The in-vivo skin optical detection device of claim 2, wherein the portion of the light path structure shared by the epidermis imaging module, the confocal microscopy module, and the raman scattering module comprises at least the first beam splitting prism, the objective lens module, and the scanning lens-tube lens group.

4. The in-vivo skin optical detection device according to claim 2, wherein the objective module comprises a fixed lens barrel and an objective main body movably arranged in the fixed lens barrel along the axial direction of the fixed lens barrel, wherein two ends of the fixed lens barrel are opened, and one end of the fixed lens barrel, which faces the skin target area to be detected, is provided with a sapphire light-transmitting lens for closing the corresponding opening;

The corresponding illumination light is sequentially reflected by the first light-splitting prism, focused by the objective lens main body and transmitted by the sapphire light-transmitting lens and then enters the skin target area to be detected, the reflected light is sequentially transmitted by the sapphire light-transmitting lens, the objective lens main body is transmitted, the first light-splitting prism is transmitted, the scanning lens-tube lens group is transmitted, and the first lens is focused and then enters the first imaging module to generate the original epidermis image of the skin target area to be detected.

5. The in-vivo skin optical detection device according to claim 4, wherein the confocal microscopy module comprises a laser light source module, a neutral density filter, a second lens, a first confocal pinhole structure, a third lens, a polarizing prism, a scanning galvanometer, a second dichroic prism and quarter-wave plate, a fourth lens, a second confocal pinhole structure and a second imaging module, and the scanning lens-tube lens group forms a 4f optical system;

The laser light source module is used for emitting excitation light, the excitation light is sequentially filtered through the neutral density filter, focused by the second lens, filtered through the first confocal pinhole structure, collimated by the third lens, vertically polarized by the polarized beam splitting prism, reflected by the scanning galvanometer, transmitted by the second beam splitting prism, transmitted by the scanning lens-tube lens group, polarized by the quarter wave plate, transmitted by the first beam splitting prism, focused by the objective lens main body, transmitted by the sapphire light transmitting lens, and then incident to the skin target area to be detected to generate scattered light, and the scattered light is sequentially transmitted through the sapphire light transmitting lens, transmitted by the objective lens main body, transmitted by the first beam splitting prism, transmitted by the quarter wave plate, transmitted by the scanning lens-tube lens group, reflected by the scanning galvanometer, transmitted by the polarized beam splitting prism, focused by the fourth lens, and then incident to the second imaging module to generate the three-dimensional structure information of the skin target area to be detected;

The corresponding illumination light is sequentially reflected by the first light-splitting prism, focused by the objective lens main body and transmitted by the sapphire light-transmitting lens and then enters the skin target area to be detected, the reflected light is sequentially transmitted by the sapphire light-transmitting lens, the objective lens main body is transmitted, the first light-splitting prism is transmitted, the quarter wave plate is polarized and the scanning lens-tube lens group is transmitted, the second light-splitting prism is reflected, the first lens is focused and then enters the first imaging module to generate the epidermis original image of the skin target area to be detected.

6. The in-vivo skin optical detection device of claim 5, wherein the raman scattering module comprises 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;

The laser light source module is used for emitting the excitation light, the excitation light is sequentially filtered through the neutral density filter, focused through the second lens, filtered through the first confocal pinhole structure, collimated through the third lens, vertically polarized through the polarizing beam splitter prism, transmitted through the third beam splitter prism, reflected through the scanning galvanometer, transmitted through the second beam splitter prism, transmitted through the scanning lens-tube lens group, polarized through the quarter wave plate, transmitted through the first beam splitter prism, focused through the objective lens main body, transmitted through the sapphire light-transmitting lens, incident on the skin target area to be detected and generated the scattered light, sequentially transmitted through the sapphire light-transmitting lens, transmitted through the objective lens main body, transmitted through the first beam splitter prism, transmitted through the quarter wave plate, transmitted through the scanning lens-tube lens group, transmitted through the second beam splitter prism, reflected through the scanning galvanometer, reflected through the third beam splitter prism, filtered through the long-pass filter, focused through the fifth lens, filtered through the adjustable slit, transmitted through the first grating reflector, reflected through the third light splitter prism, and reflected through the third lens to the concave surface to be detected as the three-dimensional diffraction component;

The corresponding excitation light is sequentially filtered through 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, focused by the objective lens main body, transmitted by the sapphire light-transmitting lens, and then incident into the skin target area to be detected, and the scattered light is sequentially transmitted through the sapphire light-transmitting lens, transmitted by the objective lens main body, transmitted by the first beam splitter prism, transmitted 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 polarized beam splitter prism, focused by the fourth lens pinhole, and incident into the second imaging module after being filtered by the second confocal structure, so as to generate the three-dimensional structure information of the skin target area to be detected.

7. The in-vivo skin optical detection device according to claim 6, further comprising an optical path adjustment module, wherein the optical path adjustment module comprises a first plane mirror and a second plane mirror, the excitation light is collimated by the third lens, then reflected by the first plane mirror to the polarization beam splitter prism, and the scattered light is focused by the third lens, then reflected by the second plane mirror to the second confocal pinhole structure.

8. The in-vivo skin optical detection apparatus according to any one of claims 5-7 wherein said excitation light is collimated light having a wavelength of 810-850 nm.

9. The in-vivo skin optical detection device of claim 1, further comprising a stationary platform and a triaxial motion module drivingly connected to the stationary platform.