CN115137297A

CN115137297A - Optical detection device, system and method for subcutaneous noninvasive detection

Info

Publication number: CN115137297A
Application number: CN202110336892.2A
Authority: CN
Inventors: 不公告发明人
Original assignee: Shanghai Jinguan Technology Co ltd
Current assignee: Shanghai Jinguan Technology Co ltd
Priority date: 2021-03-29
Filing date: 2021-03-29
Publication date: 2022-10-04

Abstract

The invention provides an optical detection device for subcutaneous noninvasive detection, which comprises an excitation module and a collection module, wherein the excitation module is used for exciting the excitation module; the excitation module comprises a laser and a first convergence part which are sequentially arranged along an excitation light path, the laser is used for emitting excitation light, and the excitation light emits signal light after being emitted or refracted by a subcutaneous biomarker; the collecting module comprises a CPC structure, a second converging part and a detector which are sequentially arranged along a collecting light path; the first converging part focuses and irradiates excitation light to tissues to be detected through the light transmitting area, and generated signal light is collimated through the reflecting area and then converged to a photosensitive receiving surface of the detector through the second converging part. The signal light has high collection efficiency, can detect biological characteristic signals with specific depth, and has simple structure and low cost. The optical detection system and the method have corresponding advantages due to the adoption of the optical detection device, and are beneficial to further popularization and application of subcutaneous noninvasive detection equipment.

Description

Optical detection device, system and method for subcutaneous noninvasive detection

Technical Field

The invention belongs to the technical field of optical detection, and particularly relates to an optical detection device, a detection system and an optical detection method for subcutaneous noninvasive detection.

Background

This section is intended to provide a background or context to the embodiments of the invention that are recited in the claims. The description herein is not intended to be exhaustive or to be construed as being limited to the precise forms disclosed should be considered prior art.

The application of the optical detection technology has been popularized in various fields in life, and particularly, the optical detection technology has a universal application in medical examination related to human health and has further deep and popular requirements. The biological characteristics can be reflected through the characteristics of the optical information, and treatment and daily health monitoring can be powerfully supported after analysis.

For example, the Raman spectrum detection technology is widely applied to the fields of food safety, biomedical archaeological public and the like, and has great value on qualitative analysis and substructure solution of substances. Especially in the application of the biomedical field, the Raman spectrum detection technology can reflect the change of human tissue cell molecules, and is a new technology for early-stage lesion detection. The method has the characteristics of no pain, no wound, simplicity, rapidness and the like, can solve the problems of the conventional detection method, and is one of potential methods for applying the non-invasive biochemical analysis of blood. Different Raman peaks are the characteristics of certain specific molecules, so that the Raman spectrum has the functions of qualitative analysis and distinguishing similar substances, the peak intensity of the Raman spectrum is in direct proportion to the concentration of the corresponding molecules, and the Raman spectrum can also be used for quantitative analysis and can provide a theoretical basis for clinical diagnosis. Whether the blood sample is affected by the disease can be judged according to the characteristic peak intensity of the blood sample in the Raman spectrum in the future.

Taking raman detection system as an example, the existing optical detection system generally includes a laser light source, a light path component, and a detection component. The laser used for exciting the Raman signal light is focused by the lens of the excitation light path component and then irradiates the tested sample. The excitation light path component filters and focuses the excitation light; the Raman signal light is collected, filtered and transmitted to a detection component, and the Raman signal intensity at different wavelengths is detected. The exciting light is focused into a point to irradiate the surface of the sample, the generated Raman signal light radiates to the periphery by taking the exciting light irradiation point as the center, and the Raman light collection system of the light path component is limited by the numerical aperture NA and the working distance of the lens and can only collect Raman radiation signals within a very small range angle, so that the relatively weak Raman signals are weaker and difficult to detect.

Therefore, how to effectively and sufficiently collect signals in optical detection is a prominent problem of optical path design in an optical detection system and is one of the key designs to be optimized in the prior art. On the other hand, the problem before collection is how to accurately focus the excitation light to the location to be detected, which concerns the complexity of sample preparation and whether it can be deployed outside the laboratory.

Of which the application in subcutaneous biomarker detection is particularly prominent. The skin, the organ with the largest surface area and the most useful, accounts for approximately eight percent of the total weight of the human body, contains 25 to 30 percent of the total circulating blood of the human body, and consists of epidermis, dermis and subcutaneous fat. Interstitial fluid or blood under the skin contains many biospecific markers that are closely related to the health and disease status of the human body. However, many of the current medical techniques are difficult to detect the biomarkers through the skin in a non-invasive manner, for example, blood glucose detection requires blood drawing tests or finger-prick blood drawing tests. The use of optical detection techniques is essential if they can be used for non-invasive subcutaneous medical detection, especially if the general population can monitor the health of an individual outside a medical laboratory. For example, in the application of the conventional raman spectroscopy, which can only measure the depth of hundreds of micrometers below the surface, and detect the spectral information of the deep subcutaneous biomarkers without damage, as shown in fig. 1, the excitation light L1 is focused and irradiated on the tissue to be measured, raman signal light is generated at the excitation region and different tissue depths (skin a, subcutaneous tissue B, blood vessels U) around the excitation region, and according to the photon migration theory, the larger the offset distance Δ s from the central excitation point along the spatial offset direction X, the larger the proportion of the signal light from deeper samples. It is obvious that new optical detection means are required to detect the signal light of a deeper layer. Therefore, there is a need to develop an optical detection device, system and corresponding optical detection method for subcutaneous noninvasive detection, which can effectively detect a specific subcutaneous depth part, is beneficial to improving the collection efficiency, and has reliable detection results. The method is very important for the application and development of the optical detection technology and has profound significance.

The above information disclosed in the background section is only for enhancement of understanding of the background of the present disclosure and therefore it may contain information that does not constitute prior art that is known to a person of ordinary skill in the art. The statements in this background section merely represent techniques known to the public and are not, of course, representative of the prior art.

Disclosure of Invention

The present invention is to solve all or part of the above problems in the prior art, and the present invention provides an optical detection device for subcutaneous non-invasive detection, and a corresponding optical detection system and method.

The following description is made of some principles and concepts which may be related to the invention and are intended to be illustrative or schematic in nature and not restrictive in character, and is not intended to limit the scope of the invention.

A Compound Parabolic Concentrator (CPC) is a non-imaging, low focal power device designed according to the edge-optics principle that collects and concentrates light within a specified acceptance angle range. The structure of the solar heat collector comprises an internal reflection area which is in a parabolic curved surface and is generally used in the solar heat collector, and incident sunlight enters from an opening of the parabolic curved surface and reaches a receiving surface at the bottom of the parabolic curved surface through several reflections in a CPC. The invention is based on the structure (CPC structure) of a compound parabolic curved surface condenser and the related principle thereof, but is not directly applied to the existing compound parabolic curved surface condenser, and is designed to collect subcutaneous signal light, the signal light enters from a light transmission area at the bottom of the parabolic curved surface, the inner surface of the parabolic curved surface in the invention is a reflection area formed by high-reflectivity materials, and the reflection area collimates the scattered incident light and then outputs the collimated incident light from an opening (opening area) of the parabolic curved surface.

Gradient index lenses, also known as variable index lenses or non-uniform dielectric lenses, commonly referred to as GRIN lenses, have a radially graded refractive index profile that provides focusing and imaging functions. The structural characteristics of the material enable the material with the structure to refract light transmitted along the axial direction, and the distribution of the refractive index is gradually reduced along the radial direction, so that emergent light rays are smoothly and continuously converged to one point.

The invention provides an optical detection device for subcutaneous noninvasive detection, which comprises an excitation module and a collection module, wherein the excitation module is used for exciting the excitation module; the excitation module comprises a laser and a first convergence part which are sequentially arranged along an excitation light path, the laser is used for emitting excitation light, and the excitation light emits signal light after being emitted or refracted by a subcutaneous biomarker; the collecting module comprises a CPC structure, a second converging part and a detector which are sequentially arranged along a collecting light path; the CPC structure includes a reflective region, a transmissive region, and an open region; the clear aperture of the light-transmitting area is larger than that of the first converging part; the first converging part focuses and irradiates excitation light to tissues to be detected through the light transmitting area, and generated signal light is collimated through the light transmitting area and the reflecting area and then converged to a photosensitive receiving surface of the detector through the second converging part. The CPC structure is adopted in the collection light path, signal light which is generated in the excitation area and at different tissue depths around the excitation area and is diverged to different directions is fully collected and collimated through the reflection area, and then is converged to the detector, so that the collection efficiency is greatly improved, and the structure is simple.

A cover shell is arranged outside the first convergence part and made of opaque materials; the housing is provided with an aperture diaphragm along the direction of the excitation light path to form a light-transmitting aperture of the first convergence part; the size of the aperture diaphragm is matched with the numerical aperture of the first convergence part. The cover can be with the abundant irradiation tissue that awaits measuring of exciting light, again with exciting light with the other parts of CPC structure separate and avoided signal crosstalk, central excitation point and near skin top layer signal light also can be sheltered from by the cover, be favorable to subsequent subcutaneous deep signal light to collect.

The reflecting area is a parabolic curved surface formed by rotating a parabola around the central axis of the CPC structure; the optical center of the first and/or second converging means is located on the central axis.

The first converging component is in the form of a GRIN lens structure. The structure is a cylindrical lens, the internal refractive index of the cylindrical lens is in a gradual change design, and the function of the cylindrical lens is to enable divergent light to be incident at one end and convert the divergent light into focused light at the other end.

The laser is connected with the first converging part through a fiber coupler and an optical fiber. The numerical aperture of the fiber coupler was 0.22. The focusing optical fiber is matched with the optical fiber coupler to realize the connection of the optical path, so that the design of the optical path is more flexible, the turning of the optical path can be realized according to the design requirement of an actual structure, and the miniaturization or portability requirement of the design of subcutaneous noninvasive detection equipment is better met.

The optical fiber and the first converging part are of an integrated structure, and the first converging part is an optical fiber collimating mirror or an optical fiber lens. The material of the integrated structure is preferably glass material, the length is preferably 5mm, the diameter range of the optical fiber is 1.5-2mm, and the preferred value is 2mm.

The numerical aperture of the fiber collimator or the fiber lens is preferably 0.5. I.e. the numerical aperture of said first converging means is preferably 0.5.

The first converging part is a fiber lens, the distance between the light-emitting end face of the fiber lens and the outer surface of the tissue to be measured is preset based on the focal length of the fiber lens, the distance range is 0.1-5mm, and preferably, the distance is 1mm.

The focal length of the first focusing member ranges from 5mm to 900mm. Preferably, the focal length of the first focusing part is 30mm.

The second converging means comprises a number of convex lenses. The second converging means comprises a lens group of at least 2 convex lenses, the focal length of which is adjustable. The focal length of the second converging part can be adjusted, so that signal light from different positions can be collected to the detector.

Including but not limited to 830nm semiconductor lasers, 785nm semiconductor lasers.

The light passing diameter of the second condensing member is larger than the diameter of the opening area. The signal light collected from the opening area of the CPC structure can completely enter the second converging part, the collection loss is minimum, and the collection effect is good.

A shading mechanical piece is arranged on the plane of the light transmitting area, the shading mechanical piece comprises a first shading frame and a second shading frame which are concentric, and the second shading frame is positioned on the shading frame in the light transmitting area; the second shading frame divides the light transmission area into a first light transmission part positioned in the second shading frame and a second light transmission part between the second shading frame and the first shading frame; the excitation light of the excitation light path irradiates the tissue to be detected through the first light transmission part, and the signal light of the collection light path is incident to the reflection area through the second light transmission part; the light transmission aperture of the first light transmission part is matched with the numerical aperture of the first converging part; the vertical distance range between the bottom surface of the shading mechanical piece and the outer surface of the tissue to be detected is 0.1mm-10mm.

The position and the size of the second light transmission part can be set by adjusting the second light shielding frames with different preset widths and changing the size of the light shielding area, so that signal light collection at different positions is realized, and the signal light with specific depth of the tissue to be detected can be detected.

The second shading frame is a structure with adjustable width. The width of the second shading frame can be adjusted within a certain range by nesting and stacking mechanical sheets with different widths or adopting a similar design of an iris diaphragm. Of course, the second light-shielding frame having a different width may be directly replaced. The design can be carried out according to the cost and the application scene. Because the shading mechanical part is a simple mechanical part, the whole mechanical shape and the width of the light transmission area between the first shading frame and the second shading frame are high in customizability and easy to manufacture, and the shading mechanical part with different sizes can be directly replaced to carry out rapid conversion of the collecting effect in application.

The center of the second shading frame is positioned at the center of the light-transmitting area; the second shading frame is a regular polygon frame or a circular frame.

The distance between the center of the second light transmission part and the center of the light transmission area is recorded as r, and has a numerical relation with the offset distance deltas, and is recorded as r-deltas = offset, and the value range of the offset is 0mm-5mm, preferably 2mm. The offset exists because the CPC structure has a certain incident light receiving limit, generally characterized by a receiving half angle, and a certain deviation exists between r and Δ s to ensure that most of collected signal light enters the CPC structure at an angle larger than the receiving half angle, thereby greatly improving the collection efficiency.

The width range of the gap from the outer edge of the second shading frame to the inner edge of the first shading frame is 1mm-50mm. Preferably 8mm.

The shading mechanical piece is made of an aluminum material subjected to oxidation blackening; the thickness range of the shading mechanical part is 1mm-3mm.

In another aspect, the present invention further provides an optical detection method, which includes: s1, irradiating the tissue to be detected through the excitation light of a laser through the excitation light path; s2, determining the depth of a specific tissue according to a photon migration theory the offset distance of the generated signal light from the central excitation; and S3, setting the CPC structure according to the offset distance, and collecting the signal light to the detector through the collection light path for subsequent biological characteristic signal analysis.

The invention also provides an optical detection system for non-invasively detecting the blood biomarker information of the nail bed, which comprises an optical chamber and a support, wherein the optical chamber and the support form a finger or toe end placing chamber for accommodating a finger or toe; the support piece is movably connected with the optical bin; the optical chamber is used for integrating the parts of the optical detection device except the laser and the detector; one surface of the optical bin, which faces the supporting piece, is provided with an optical window, and the placing bin corresponds to the optical window; the excitation light provided by the optical bin is projected to the nail bed of the finger or toe to be detected through the optical window, the biological marker in the blood of the nail bed is detected, and the reflected or refracted signal light is collected, so that the information of the biological marker in the blood of the nail bed is obtained.

The optical bin provides exciting light and collects returned signal light, the exciting light is emitted through the optical window, and the returned signal light is collected. The support is used for supporting the finger or toe end of the living being to be detected. The detection system is used for non-invasively detecting nail bed characteristic signals of the finger or toe end of a living being. When the biological marker in the nail bed blood is detected, the biological finger or toe end to be detected is placed in the biological finger or toe end placing bin, and the nail is correspondingly placed under the optical window, so that noninvasive detection can be performed, the operation is simple and efficient, the information of the biological marker in the nail bed blood is detected, and the disease or health condition of the nail bed is accurately reflected.

The optical chamber is connected with the supporting piece through a rotating piece, and a biological finger or toe end placing chamber is formed between the optical chamber and the supporting piece. The biological finger or toe end placing bin is used for placing the biological finger or toe end to be detected.

The rotating member is a hinge or a bearing. The optical bin can rotate anticlockwise through the hinge or the bearing, the optical bin preferably rotates 90 degrees anticlockwise, the light transmission condition of the optical window is convenient to check, and the optical window is convenient to replace when damaged.

The entrance of the biological finger or toe end placing bin is provided with a detachable rubber ring. The rubber ring is used for fixing the finger or toe end of the living creature to be detected and can be replaced according to the size of the finger or toe end of the living creature to be detected. The diameter of the rubber ring is preferably 10mm to 20mm.

The optical bin and the support can also be slidably connected. A sliding groove is formed in the optical bin, and a sliding rail is arranged on the supporting piece; the supporting piece is fixed, the optical bin slides towards the direction far away from the supporting piece, and a biological finger or toe end placing bin is formed between the optical bin and the supporting piece according to the size of the biological finger or toe end to be detected.

Or a sliding rail is arranged on the optical bin, and a sliding groove is arranged on the supporting piece; the optical bin is fixed, the supporting piece slides towards the direction far away from the optical bin, and a biological finger or toe end placing bin is formed between the optical bin and the supporting piece according to the size of the biological finger or toe end to be detected.

Or the optical bin and the supporting piece are in sliding connection through a sliding connecting piece. The optical cartridge and the support are simultaneously slidable, forming the biological finger or toe end placement cartridge between the optical cartridge and the support.

The optical window is a sheet structure. The thickness range of the optical window is 0.5mm-10mm, and preferably 1mm; when the optical window is a circular sheet structure, the diameter of the optical window ranges from 0.5mm to 25mm, and preferably ranges from 5mm.

The optical window is made of transparent resin or quartz glass. The optical window should be selected of a material that has a high transmittance and allows excitation light of preferably 785nm or 830nm wavelength to pass through.

The invention also provides another optical detection system for detecting biomarker information under limb skin, which comprises an optical bin, an optical fiber transmission structure and a bandage, wherein the optical fiber transmission structure is used for optically connecting the optical bin and the bandage, and the bandage is used for accommodating limbs in a surrounding manner; the surface of the optical bin is provided with a light through hole, and the optical bin is used for integrating the parts of the optical detection device except the laser and the detector; the optical fiber transmission structure comprises an optical fiber bundle, a first optical fiber coupling system and a second optical fiber coupling system, wherein the optical fiber coupling systems are connected with two ends of the optical fiber bundle, the first optical fiber coupling system is used for guiding the exciting light out of the optical bin, guiding the exciting light into the binding band along the optical fiber bundle and the second optical fiber coupling system in sequence, and emitting the signal light after being reflected or refracted by the biomarker under limb skin, and the signal light is guided into the optical bin along the second optical fiber coupling system, the optical fiber bundle and the first optical fiber coupling system in sequence; the optical fiber bundle is connected with the light through hole through the optical fiber coupling system. Transmitting the exciting light provided in the optical bin to the surface of the limb to be measured through the optical fiber transmission structure; and re-couples and re-transmits the signal light returned by the surface into the optical bin. The optical detection device is suitable for different scenes, the length of the optical fiber bundle is changed to meet the requirement that the optical bin and the limb to be detected are located at different spatial positions, and the optical detection device is integrated through the optical bin and is convenient to use.

Compared with the prior art, the invention has the main beneficial effects that:

1. according to the optical detection device for subcutaneous noninvasive detection, the CPC structure is adopted, signal light in a larger range can be collected, the signal light at a subcutaneous specific depth position can be effectively collected, and the signal collection efficiency of subcutaneous noninvasive detection equipment is improved; the reliability and accuracy of optical non-invasive detection are improved. Through the combination of the CPC structure and the replaceable and customizable shading mechanical piece, the quick switching of signal collection selection of different skin offset positions can be realized, and the method has the advantages of high efficiency and flexibility. The two optical detection systems are integrated with the optical detection device, so that the optical detection system is suitable for application requirements of specific scenes, and has the advantages of good portability, simple structure and convenience in use.

2. The optical detection system and the optical detection method provided by the invention have corresponding advantages due to the adoption of the optical detection device, can acquire biological characteristic information of a tissue to be detected, particularly a preset depth under skin, and are favorable for further popularization and application of subcutaneous noninvasive detection equipment.

Drawings

Fig. 1 is a schematic diagram of spatial offset.

Fig. 2 is a schematic diagram of an optical detection apparatus according to a first embodiment of the invention.

Fig. 3 is a schematic diagram of an optical detection method according to a first embodiment of the invention.

Fig. 4 is a schematic diagram of an optical detection apparatus according to a second embodiment of the present invention.

Fig. 5 is a schematic view of a second light-shielding frame according to a second embodiment of the invention.

Fig. 6 is a schematic diagram of an optical chamber according to a third embodiment of the present invention.

Fig. 7 is a schematic diagram of a detection system in a third embodiment of the invention.

Fig. 8 is a schematic diagram illustrating the rotation of an optical chamber according to a third embodiment of the present invention.

Fig. 9 is a schematic diagram of a detection system and a related structure in a fourth embodiment of the invention.

Detailed Description

The technical solutions in the specific embodiments of the present invention will be clearly and completely described below, and it should be understood that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.

The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings. In the figures, parts of the same structure or function are denoted by the same reference numerals, and not all parts shown are denoted by the associated reference numerals in all figures for reasons of clarity of presentation.

Example one

As shown in fig. 2, the optical detection apparatus of the present embodiment includes an excitation module and a collection module; the excitation module comprises a laser 1 and a first convergence part 3 which are sequentially arranged along an excitation light path, wherein the laser 1 is used for emitting excitation light, and the excitation light emits signal light after being emitted or refracted by a subcutaneous biomarker; the collecting module comprises a CPC structure 2, a second converging part 4 and a detector 5 which are sequentially arranged along a collecting light path; the CPC structure 2 comprises a reflective region 21, a transmissive region 22 and an open region 23; the first converging part 3 focuses the exciting light L1 to a tissue to be detected (at a specific depth under the skin) through the light transmitting area 22, and the generated signal light L2 is converged to a photosensitive receiving surface of the detector 5 through the light transmitting area 22, then collimated through the reflecting area 23 and the second converging part 4. In this embodiment, the signal light L2 to be collected is from the subcutaneous tissue as an example. In one case of the embodiment, the components other than the laser 1 and the detector 5 are integrated in one optical chamber.

In this embodiment, a cover 30 is disposed outside the first focusing member 3, and the cover 30 is made of opaque material; the housing 30 is provided with an aperture diaphragm M along the direction of the excitation light path to form a clear aperture of the first converging part; the size of the aperture diaphragm M is matched with the numerical aperture of the first convergence part 3, namely emergent light of the first convergence part 3 is not lost due to the housing 30, and excitation is not influenced.

In the present embodiment, the reflection area 21 is a parabolic curved surface formed by rotating a parabola around the central axis N of the CPC structure 2; the optical centers of the first and second converging

means

3, 4 are located on said central axis N. In other embodiments, the reflective region 21 is formed by splicing 2 parabolic curved surfaces or a plurality of parabolic curved surfaces. The cross section of the opening area 23 may be an area having only two parallel edges or a rectangular and polygonal shape, and is not limited. The clear aperture of the light-transmitting region 22 is the diameter of the light-transmitting aperture stop K, and is larger than the clear aperture of the first condensing element 3. The first focusing member 3 in this embodiment is a GRIN lens structure.

In this embodiment, a semiconductor laser having a wavelength of 785nm is used as the laser 1, and the laser 1 is connected to an optical fiber 101 in cooperation with an optical fiber coupler. The numerical aperture of the fiber coupler in this example is 0.22. The focal length of the first focusing member 3 preferably ranges from 5mm to 900mm. In the preferred embodiment, the focal length is 30mm. In this embodiment, the optical fiber 101 and the first converging part 3 are an integral structure, and the first converging part 3 is a fiber collimator or a fiber lens. The material of the integrated structure, i.e. the optical fiber 101 and the first focusing member 3, is preferably of glass material, with a length of 5mm in this embodiment and a fiber diameter in the range of 1.5-2mm, a preferred value in this embodiment being 2mm. The numerical aperture of the fiber collimator or the fiber lens is 0.5 in this embodiment, that is, the numerical aperture of the first focusing member is 0.5. In a specific practice of this embodiment, the first focusing member 3 is a fiber lens, a distance D between a light-emitting end surface of the fiber lens and an outer surface of a tissue to be measured, that is, a surface of the skin a, is preset based on a focal length of the fiber lens, the distance D ranges from 0.1mm to 5mm, and a preferred distance D in this embodiment is 1mm. The focal length of the first focusing member 3 in this embodiment ranges from 5mm to 900mm. In one specific implementation, the focal length of the first focusing member 3 is 300mm.

The second converging means 4 in this embodiment comprises 1 convex lens. There are also embodiments in which the second converging means comprises a lens group formed by at least 2 convex lenses, the focal length of said lens group being adjustable. The focal length of the second converging means can be adjusted to facilitate the collection of signal light from different positions onto the detector 5. The light passing diameter of the second condensing element 4 in this embodiment is larger than the diameter of the opening area 23.

As shown in fig. 3, the optical detection method in the present embodiment includes: s1, irradiating the tissue to be detected through the excitation light path of a laser; s2, determining the offset distance of signal light generated at a specific tissue depth from center excitation according to a photon migration theory; and S3, setting the CPC structure according to the offset distance, and collecting the signal light to the detector through the collection light path for subsequent biological characteristic signal analysis. In this embodiment, the offset distance is obtained by specifically adopting a monte carlo simulation algorithm in step S2. The CPC structure designed in step S3 is offset by a distance located within its light-transmitting region and outside of the housing 30.

Example two

The main difference between the second embodiment of the present invention and the first embodiment of the present invention is that, as shown in fig. 4 and fig. 5, a light-shielding mechanical component is disposed in a plane where the light-transmitting area 22 is located, and includes a first light-shielding frame and a second light-shielding frame 8 that are concentrically disposed, in this embodiment, an inner edge (circle) of the first light-shielding frame is a light-transmitting aperture stop K, and the light-transmitting area 22 is disposed with the second light-shielding frame 8; the second light-shielding frame 8 divides the light-transmitting area 22 into a first light-transmitting portion 22a located inside the second light-shielding frame 8 and a second light-transmitting portion 22b located between the second light-shielding frame 8 and the light-transmitting aperture stop K. The excitation light L1 irradiates the tissue to be measured through the first light transmission portion 22a, and the signal light L2 enters the reflection region through the second light transmission portion 22b, that is, only the signal light L2 entering the second light transmission portion 22b is collected by the collection light path. The perpendicular distance H between the light-blocking mechanism and the surface of the skin a is in the range of 0.1mm to 10mm, preferably 2mm in this embodiment.

The light shielding area is changed and the area between the second light shielding frame 8 and the light-transmitting aperture diaphragm K is adjusted by adjusting the second light shielding frame 8 with different preset widths, so that the positions and the sizes of the first light-transmitting area 22a and the second light-transmitting area 22b can be set, the signal light L1 at different positions is collected, and the biological characteristic signal of subcutaneous specific depth can be detected.

The center of the second light-shielding frame 8 in this embodiment is located at the center of the light-transmitting region 22, i.e., on the central axis N. The second light-shielding frame 8 may be a regular polygonal frame or a ring frame. In this embodiment, the light-shielding mechanical member is an annular frame, specifically, a concentric ring subjected to blackening treatment, the inner ring serves as the second light-shielding frame 8, the outer ring serves as the first light-shielding frame, the distance between the inner ring and the outer ring is Δ r, that is, the range of the radial gap width Δ r from the outer edge (outer circle) of the second light-shielding frame 8 to the edge E of the light-transmitting region 22 is 1mm to 50mm. A preferred value for Δ r is 8mm. The reception of different position offsets can be achieved by directly replacing concentric rings with different deltar.The clear aperture of the first light-transmitting portion 22a is the diameter D of the inner circle of the second light-shielding frame 8 _c Matching the numerical aperture of the first condensing element 3 ensures that the excitation light L1 is not lost due to the second light-shielding frame 8.

One way in this embodiment is that the second light-shielding frame 8 is a width-adjustable structure, and the width of the second light-shielding frame can be adjusted within a certain range by adopting a similar design of the iris diaphragm. Another way in this embodiment is to directly replace the second light-shielding frame 8 having a different width. The design can be carried out according to the cost and the application scene. Because the shading mechanical part is a simple mechanical part, the whole mechanical shape and the ring width of the shading mechanical part are high in customizability and easy to manufacture, and the shading ring can be directly replaced to carry out rapid conversion of the collecting effect in application.

The distance from the center of the second light transmission part 22b to the center of the light transmission region, i.e., the radius of a circle, in this embodiment, is denoted as r, and has a numerical relationship with the offset distance Δ s, and is denoted as r- Δ s = offset, and the value of offset ranges from 0mm to 5mm in this embodiment, and is preferably 2mm. The offset exists because the CPC structure has a certain incident light receiving limit and is generally characterized by a receiving half-angle theta, and a certain deviation exists between r and deltas to ensure that most of collected signal light enters the CPC structure at an angle larger than the receiving half-angle theta, so that the collection efficiency is greatly improved.

In the embodiment, the shading mechanical piece is made of an aluminum material subjected to oxidation blackening; the thickness range of the second light-shielding frame 8 and the light-transmitting aperture stop K is 1mm to 3mm.

EXAMPLE III

The optical detection device of any one of the first to third embodiments of the present embodiment provides an optical detection system for non-invasive detection of biomarkers in blood of nail beds, and referring to fig. 6 and 7, the optical detection system comprises an optical chamber i-1 and a support member i-5, the optical chamber i-1 is movably connected with the support member i-5, in particular, connected through a rotating member, and a finger or toe end placing chamber i-4 is formed between the optical chamber i-1 and the support member i-5 to accommodate a finger or toe. The optical bin I-1 is used for integrating the parts of any optical detection device except the laser and the detector in the first embodiment to the third embodiment of the invention, when in use, the optical bin is externally connected with the laser and the detector and used for providing exciting light, and the optical bin is used for collecting signal light reflected or refracted by skin; an optical window I-2 is further arranged on the optical bin I-1, and the optical window I-2 is arranged on one surface, facing the support piece I-5, of the optical bin I-1.

In this embodiment, the optical window I-2 is in a square sheet structure, but not limited to a square sheet structure, and the side length of the optical window I-2 is 10mm, and the thickness is 1mm; the material of the optical window I-2 is quartz glass, and the selected material has high transmittance and can allow excitation light with the wavelength of 785nm or 830nm to transmit. The excitation light provided by the optical bin I-1 is projected to a nail bed to be detected through the optical window I-2, the biological marker in the blood of the nail bed is detected, and the returned signal light is collected, so that the information of the biological marker in the blood of the nail bed is obtained.

Referring to fig. 8, the optical bin I-1 is connected with the support piece I-5 through a rotating piece I-3, the rotating piece I-3 is a hinge, the optical bin I-1 can rotate counterclockwise through the hinge, the counterclockwise rotation angle of the optical bin I-1 is preferably 90 degrees, the light transmission condition of the optical window I-2 can be conveniently checked, and the optical window I-2 can be conveniently replaced when damaged.

A finger or toe end placing bin I-4 is formed between the optical bin I-1 and the supporting piece I-5, the finger or toe end placing bin I-4 corresponds to the optical window I-2 to contain a finger or toe, and the finger or toe end placing bin I-4 is used for placing a finger to be detected; the support piece I-5 is used for supporting the finger to be detected. When a finger to be detected is placed in the finger or toe end placing bin I-4, the fingernail of the finger to be detected is placed right below the optical window I-2. The rubber ring I-6 is arranged at the entrance of the finger or toe end placing bin I-4, and the rubber ring I-6 can be detached and replaced and is used for fixing the finger to be detected and preventing detection errors caused by accidental sliding of the finger to be detected. The rubber ring I-6 can be made into different sizes so as to be suitable for fingers to be detected with different thicknesses. In the present embodiment, it is preferred that, the diameter of the rubber ring I-6 is preferably 15mm.

When the biomarkers in the nail bed blood of the finger need to be detected, the finger to be detected is placed in the finger or toe end placing bin I-4, the nail of the finger to be detected is correspondingly placed under the optical window I-2, the excitation light provided by the optical bin I-1 is projected to the nail bed to be detected through the optical window I-2, the biomarkers in the nail bed blood are detected, and the returned signal light is collected, so that the information of the biomarkers in the nail bed blood is obtained.

Preferably, the optical chamber i-1 is used for integrating any one of the optical detection devices of the first to third embodiments of the present invention, including the laser and the detector.

Example four

The present embodiment integrates any one of the optical detection devices in the first to third embodiments, and provides an optical detection system for detecting biomarker information under limb skin. Referring to fig. 9, the signal collection system includes an optical bin i-1, an optical fiber transmission structure for optically connecting the optical bin i-1 and the strap ii-5, and a strap ii-5 for encircling the accommodation limb ii-7. The optical bin I-1 is used for integrating the parts of any optical detection device except the laser and the detector in the first embodiment to the third embodiment of the invention; when the device is used, the optical bin is externally connected with the laser and the detector and used for providing exciting light to be transmitted to the skin through the optical bin, and the optical bin is used for collecting signal light reflected or refracted by the skin and analyzing the signal light. And a detection window II-4 is arranged on the binding band.

The optical fiber transmission structure comprises a first optical fiber coupling system II-2 and a second optical fiber coupling system II-3 which are connected with the light through hole, and an optical fiber bundle II-6 which is connected with the first optical fiber coupling system II-2 and the second optical fiber coupling system II-3. The optical fiber transmission structure transmits the exciting light provided in the optical bin I-1 to the skin surface of the limb to be detected; and the signal light returned from the skin surface is transmitted to the optical bin I-1 for analysis. The optical fiber transmission structure connects the optical bin I-1 with the detection window II-4. The detection windows II-4 are arranged on the outer side of the binding band II-5, the number of the detection windows II-4 is 4-15, and the detection windows II-4 are uniformly distributed on the binding band II-5; preferably, the number of collection windows II-4 is 12. Each detection window II-4 can be correspondingly connected with an optical bin I-1, when the biological markers in tissue fluid or blood below the skin of the limb are detected, the limb II-7 is placed on the inner side of the binding band II-5, in the embodiment, the binding band II-5 is made of nylon materials and can be directly attached to the limb, the excitation light in the optical bin I-1 is transmitted to the surface of the skin of the limb to be detected through the optical fiber transmission structure, and then the signals returned by the detected skin are transmitted to the optical bin I-1 through the optical fiber transmission structure and are analyzed.

The use of certain common english terms or letters for the clarity of the description is intended for illustrative purposes only and is not intended to limit the scope of the invention to the particular use or interpretation of the invention, and the possible chinese translations or specific letters used therein. It is further noted that, herein, relational terms such as first and second, and the like may be used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. The structure and operation of the present invention are explained by applying specific examples, and the above description of the embodiments is only used to help understanding the method and core idea of the present invention. It will be apparent to those skilled in the art that various changes and modifications can be made without departing from the principles of the invention, and it is intended to cover such changes and modifications as fall within the scope of the appended claims.

Claims

1. An optical detection device for subcutaneous non-invasive detection, characterized by: comprises an excitation module and a collection module;

the excitation module comprises a laser and a first convergence part which are sequentially arranged along an excitation light path, the laser is used for emitting excitation light, and the excitation light emits signal light after being emitted or refracted by a subcutaneous biomarker; the collecting module comprises a CPC structure, a second converging part and a detector which are sequentially arranged along a collecting light path;

the CPC structure comprises a reflection area, a light transmission area and an opening area; the clear aperture of the light-transmitting area is larger than that of the first converging part;

the first converging component focuses and irradiates excitation light to a tissue to be detected through the light transmitting area, and generated signal light is converged to a photosensitive receiving surface of the detector through the light transmitting area, then is collimated through the reflecting area and then is converged by the second converging component.

2. An optical detection device for subcutaneous non-invasive detection according to claim 1, characterized in that: a cover shell is arranged outside the first convergence part and made of opaque materials;

the housing is provided with an aperture diaphragm along the direction of the excitation light path to form a light-transmitting aperture of the first convergence part; the size of the aperture diaphragm is matched with the numerical aperture of the first convergence part.

3. An optical detection device for subcutaneous non-invasive detection according to claim 1, characterized in that: the reflecting area is a parabolic curved surface formed by rotating a parabola around the central axis of the CPC structure; the optical center of the first converging means and/or the second converging means is located on the central axis.

4. An optical detection device for subcutaneous non-invasive detection according to claim 1, characterized in that: the first converging component is in the form of a GRIN lens structure.

5. An optical detection device for subcutaneous non-invasive detection according to claim 4, characterized in that: the first converging part is a fiber lens, the distance between the light-emitting end face of the fiber lens and the outer surface of the tissue to be detected is preset based on the focal length of the fiber lens, and the preset distance range is 0.1mm-5mm.

6. An optical detection device for subcutaneous non-invasive detection according to any one of claims 1-5, characterized in that: a shading mechanical piece is arranged on the plane of the light transmitting area, the shading mechanical piece comprises a first shading frame and a second shading frame which are concentric, and the second shading frame is positioned on the shading frame in the light transmitting area;

the second shading frame divides the light transmission area into a first light transmission part positioned in the second shading frame and a second light transmission part between the second shading frame and the first shading frame;

the excitation light of the excitation light path irradiates the tissue to be detected through the first light transmission part, and the signal light of the collection light path is incident to the reflection area through the second light transmission part;

the light transmission aperture of the first light transmission part is matched with the numerical aperture of the first converging part;

the vertical distance range between the bottom surface of the shading mechanical piece and the outer surface of the tissue to be detected is 0.1mm-10mm.

7. An optical detection device for subcutaneous non-invasive detection according to claim 6, characterized in that: the center of the second shading frame is positioned at the center of the light-transmitting area; the second shading frame is a regular polygon frame or a circular frame; the width range of the gap from the outer edge of the second shading frame to the inner edge of the first shading frame is 1mm-50mm;

the distance between the center of the second light transmission part and the center of the light transmission area is marked as r, a numerical relationship exists between the distance and an offset distance delta s, the distance is marked as r-delta s = offset, and the value range of the offset is 0mm-5mm;

the shading mechanical part adopts a process manufacturing an aluminum material subjected to oxidation blackening treatment; the thickness range of the shading mechanical piece is 1mm-3mm.

8. An optical detection system for non-invasively detecting blood biomarker information of a nail bed, comprising: comprises an optical chamber and a support member, the optical chamber and the support member forming a finger or toe end placement chamber for accommodating a finger or toe; the optical chamber is used for integrating the optical detection device of any one of claims 1 to 7 except the laser and the detector; one surface of the optical bin, which faces the supporting piece, is provided with an optical window, and the placing bin corresponds to the optical window; the excitation light provided by the optical bin is projected to the nail bed of the finger or toe to be detected through the optical window, the biological marker in the blood of the nail bed is detected, and the reflected or refracted signal light is collected, so that the information of the biological marker in the blood of the nail bed is obtained.

9. An optical detection system for detecting biomarker information under the skin of a limb, characterized by: comprising an optical cartridge, an optical fiber transmission structure for optically connecting the optical cartridge and the strap, and a strap for encircling a receiving limb; the optical chamber is used for integrating the optical detection device of any one of claims 1 to 7 except the laser and the detector; the optical fiber transmission structure comprises an optical fiber bundle, a first optical fiber coupling system and a second optical fiber coupling system, wherein the first optical fiber coupling system and the second optical fiber coupling system are connected with two ends of the optical fiber bundle, the first optical fiber coupling system is used for leading exciting light out of the optical bin, the exciting light is led into the binding band along the optical fiber bundle and the second optical fiber coupling system in sequence, signal light is emitted after being reflected or refracted by biological markers under limb skin, and the signal light is led into the optical bin along the second optical fiber coupling system, the optical fiber bundle and the first optical fiber coupling system in sequence.

10. An optical detection method, characterized by: an optical detection apparatus for subcutaneous non-invasive detection using any one of claims 1 to 7, comprising:

s1, irradiating the tissue to be detected through the excitation light path;

s2, determining the offset distance of signal light generated at a specific tissue depth from center excitation according to a photon migration theory;

and S3, setting the CPC structure according to the offset distance, and collecting the signal light to the detector through the collection light path for subsequent biological characteristic signal analysis.