CN115120186A - A subcutaneous detection device, system and method based on conical mirror structure - Google Patents

Abstract

The present invention provides a subcutaneous detection device based on a conical mirror structure, comprising an excitation light source assembly, a conical mirror structure, a first imaging component, a second imaging component and a detector, the excitation light source component is used for emitting excitation light, and the The excitation light emits signal light after being emitted or refracted by the subcutaneous biomarker; the light emitted from the convex surface of the conical mirror structure is a ring-shaped light beam; the ring-shaped light beam forms a ring-shaped excitation area through the first optical path. The possible risk of point-shaped light spot excitation is avoided, the signal collection efficiency is improved, and the safety is high; the structure is simple, the cost is low, the depth of the detection position can be adjusted by adjusting the conical mirror structure, and the operation is flexible. The detection system and detection method of the present invention have corresponding advantages due to the use of the subcutaneous detection device based on the conical mirror structure of the present invention, the steps are simple and efficient, and the biological feature information of the same depth level under the skin can be obtained as required, which is beneficial to the non-invasive subcutaneous The further popularization and application of detection technology.

Description

A subcutaneous detection device, system and method based on conical mirror structure

technical field

The invention belongs to the technical field of non-invasive detection, and in particular relates to a subcutaneous detection device based on a conical mirror structure, a corresponding detection system and a detection method.

Background technique

This section is intended to provide a background or context for the embodiments of the invention that are recited in the claims. The descriptions herein should not be considered prior art by virtue of their inclusion in this section.

The application of non-invasive detection technology has been extended to all fields of life, especially in medical examinations related to human health, and there is also a need for further in-depth and popularization. The characteristics of light information can reflect biological characteristics, and after analysis, it can effectively support treatment and daily health monitoring.

In the application of biomedicine, Raman spectroscopy detection technology can reflect the changes of human tissue cells and molecules, and it is a new technology for early lesion detection. With the characteristics of painless, non-invasive, simple and fast, it can improve the problems of conventional testing methods, and is one of the potential methods for non-invasive biochemical analysis of blood. Different Raman peaks are the characteristics of some specific molecules, so that Raman spectrum has the function of qualitative analysis and distinguishing similar substances. The peak intensity of Raman spectrum is proportional to the concentration of the corresponding molecule, and can also be used for quantitative analysis. It can provide theoretical basis for clinical diagnosis. It is predicted that in the future, it can be judged whether there is a disease according to the characteristic peak intensity of the blood sample in the Raman spectrum.

Taking a Raman detection system as an example, an existing non-invasive detection system generally includes a laser light source, an optical path component, and a detection component. The laser light source is used as the laser that excites the Raman signal light, which is focused by the lens of the excitation optical path component and then irradiates the sample to be tested. The excitation light path component filters and focuses the excitation light; collects and filters the Raman signal light, and then transmits it to the detection component to detect the Raman signal intensity at different wavelengths. The excitation light is focused into a point and irradiated to the surface of the sample, and the generated Raman signal light is radiated around the point where the excitation light is irradiated.

Therefore, how to effectively and sufficiently collect signals in non-invasive detection is a prominent problem in the design of optical paths in non-invasive detection systems, and it is also one of the key designs that need to be optimized in the current technology. On the other hand, the problem before collection is how to accurately focus the excitation light to the position to be detected, which is related to the complexity of sample preparation and whether it can be applied outside the laboratory.

Among them, the application of subcutaneous biomarker detection is particularly prominent. The skin is the largest and most useful organ in the human body. The total weight is about 8% of the human body weight. It contains 25%-30% of the water in the entire circulating blood of the human body. The skin tissue is composed of epidermis, dermis and subcutaneous fat. The tissue fluid or blood under the skin contains many biomarkers, which are closely related to the health status and disease degree of the human body. However, many current medical technologies are difficult to non-invasively detect biomarkers through the skin. For example, blood sugar testing requires blood testing, or finger prick blood for testing. Non-invasive testing technology is of great significance for subcutaneous medical testing, especially if the general population can monitor personal health outside the medical laboratory, the application of non-invasive testing technology is essential. For example, traditional Raman spectroscopy can only test to a depth of several hundred micrometers below the surface. In the application of nondestructive detection of spectral information of deep subcutaneous biomarkers, as shown in Figure 1, the excitation light will be in the excitation area and its surrounding tissue depths (Skin A, subcutaneous tissue B, blood vessel U) Raman signal light is generated. According to the photon migration theory, the greater the offset distance ΔS ₁ from the central excitation point along the spatial offset direction X, the greater the signal light from the deeper sample. The larger the proportion. Therefore, it is necessary to develop a subcutaneous detection device, system and corresponding detection method based on a conical mirror structure that can effectively detect a specific depth of the subcutaneous, which is beneficial to improve the collection efficiency and the detection result is reliable.

The above information disclosed in this Background section is only for enhancement of understanding of the background of the disclosure and therefore it may contain information that does not form the prior art that is already known to a person of ordinary skill in the art. The contents in the background art section are only technologies known to the disclosed person, and do not necessarily represent the existing prior art in the field.

SUMMARY OF THE INVENTION

The present invention is to solve all or part of the above-mentioned problems of the prior art, and the present invention provides a subcutaneous detection device, system and corresponding detection method based on a conical mirror structure.

Some principles and concepts that may be involved in the present invention are described below. These descriptions are for the convenience of understanding the present invention, and are illustrative or principle descriptions rather than restrictive explanations, and should not limit the scope of the present invention.

The invention is based on the principle of SORS technology, and its fundamental starting point is the theory of photon migration. As shown in Figure 1, when the excitation light is incident on the surface of the sample to be tested, the surface sample is excited or scatters broadband fluorescence, and part of the scattered light will reach the interior of the sample , the Raman scattered photons generated in the deep inside of the sample are more likely to migrate laterally during the scattering process than the photons on the surface of the sample, and return to the surface of the sample to be collected after multiple scattering. The position of the scattered light reaching the same depth inside the sample and returning to the surface layer has the same spatial offset distance ΔS ₁ from the incident point of the excitation light in the X direction on the sample surface layer.

When the distance from the conical apex of the conical mirror structure to the imaging surface increases, the diameter of the formed halo will also increase, while the width of the halo remains unchanged. The beam has the characteristics of a Bessel beam, and the light intensity distribution along the beam propagation direction does not change. The size of the halo can be set by selecting a specific material, a conical mirror structure with a conical base angle, and/or adjusting the distance from the vertex of the conical mirror structure to the imaging surface, and vice versa. After the spatial offset distance, the ring-shaped excitation can be performed using the spatial offset distance as the inner diameter, and the signal light with the accumulated intensity generated by the excitation can be collected in the central area.

Dichroic beam splitting element refers to an optical beam splitting element with dichroism, which is characterized by almost completely transmitting light of a certain wavelength, and almost completely reflecting light of other wavelengths.

The present invention is based on the above principles, aiming at the particularity of the detection of the characteristic signals of the internal markers of biological tissues, especially in the acquisition of the biological characteristic signals in the deep subcutaneous tissue, in order to solve all or part of the problems of the above-mentioned prior art, a cone-based method is provided. A subcutaneous detection device with a mirror-shaped structure and a related detection system and method.

An aspect of the present invention provides a subcutaneous detection device based on a conical mirror structure, comprising an excitation light source assembly and a conical mirror structure arranged in sequence along a first optical path, wherein the first optical path is used to form an annular excitation region on the skin, The excitation light source assembly is used to emit excitation light, and the excitation light emits signal light after being emitted or refracted by the subcutaneous biomarker; the first imaging component, the second imaging component and the detector are sequentially arranged along the second optical path, so The second optical path is used to collect signal light; the excitation light source assembly includes a laser and an optical collimation structure, and the light output by the laser is converted into a parallel beam through the optical collimation structure and enters the plane side of the conical mirror structure, from The light emitted from the convex surface of the conical mirror structure is a ring-shaped light beam; the ring-shaped light beam forms a ring-shaped excitation area through the first optical path; the first imaging component and the second imaging component form a conjugate optical structure; the The central region of the annular excitation region and the receiving end of the detector are on a pair of conjugate planes.

The central area of the annular excitation area is the same position with the same spatial offset distance from the excitation point. The signal light here reflects the biosignature signals from the same depth level under the skin. The signals are accumulated and the intensity is high. The excitation energy of the annular excitation area is in the The position of its central area realizes more efficient single-point signal collection, and at the same time, by selecting a specific conical mirror structure (material, shape, size), and/or adjusting the position of the conical mirror structure, it is possible to detect the conical mirror structure that meets the actual requirements. Biometric information at specific depths under the skin. More importantly, the excitation in the annular excitation area can effectively reduce the side effects of local overheating, high energy density, and the risk of tissue burning caused by the injection of point-shaped spot excitation. High reliability.

The conical mirror structure includes an axicon. The number of the axicon lenses is single or multiple.

The cone angle of the axicon lens ranges from 0.5° to 40°. Among them, 20° is preferable. The radius of the annular excitation region ranges from 1 mm to 9 mm. In the preferred case it is 2mm.

The tapered mirror structure further includes a track fixed at a position parallel to the optical axis of the first optical path; the tapered lens is slidably connected to the track. When the axicon lens slides along the track, the distance from the conical vertex of the axicon lens to the imaging surface is adjusted.

The conical mirror structure is arranged in a through lens barrel, and the size of the through openings at both ends of the lens barrel is matched with the clear aperture of the conical mirror structure; the track is arranged on the side wall of the lens barrel.

The track is a chute on the side wall of the lens barrel; a slider is arranged in the chute, and the slider includes a limit part and a control part for controlling the movement of the limit part, and the limit part is connected to the The edge of the axicon lens is fixedly connected; the control end of the control part is arranged outside the side wall of the lens barrel. The mechanical structure is used to control the position of the cone lens and adjust the size of the annular excitation region, which is easy to manufacture, has low cost, and is convenient to operate.

The lens barrel is made of aluminum material that has been oxidized and blackened.

The conical mirror structure and the optical collimation structure are connected by an optical fiber.

The tapered mirror structure includes an optical fiber and a tapered lens arranged on the outgoing end face of the optical fiber.

The optical collimation structure includes an excitation fiber coupler, which is connected to the laser through an optical fiber, and converts the output light of the laser into a parallel beam; the excitation fiber coupler is a plurality of GRIN lenses. The numerical aperture of the excitation fiber coupler was 0.22. The use of optical fiber and excitation fiber coupler to realize optical path connection can not only generate parallel beams, but also facilitate more flexible optical path design. It can realize optical path bending according to the actual structural design requirements, and better meet the miniaturization or portability requirements of non-invasive detection equipment design. .

The first optical path and the second optical path are partially overlapped, and a dichroic light splitting element is arranged at the intersection of the two. The first light path or the second light path can be turned by using the dichroic light splitting element.

The dichroic light-splitting element is arranged between the first imaging part and the second imaging part, the dichroic light-splitting element is located between the conical mirror structure and the first imaging part, the The outgoing light from the conical mirror structure enters the first imaging component after being reflected, and is collimated by the first imaging component to form the annular excitation area; the signal light generated in the central area is imaged by the first imaging component Parts are collected and transmitted from the dichroic beam splitting element. The first optical path and the second optical path can be partially overlapped, and the excitation light and the signal light are separated, which is beneficial to the flexibility of the overall structural design of the subcutaneous detection device based on the conical mirror structure and the miniaturization requirements.

A band-pass filter component is arranged before the second imaging component along the second optical path, for filtering out stray light with a wavelength shorter than that of the signal light, the center wavelength of the band-pass filter component is the same as the wavelength of the signal light The wavelength of the laser is adapted.

The detector receives the signal light condensed by the second imaging component through the collection fiber bundle, and the receiving end of the detector is the incident end face of the collection fiber bundle.

The first imaging component and/or the second imaging component includes a focusing lens; the focal length of the focusing lens ranges from 5mm to 900mm. The focal length of the focusing lens is preferably 20mm or 50mm.

The first imaging component and/or the second imaging component includes a lens group formed by at least two focusing lenses, and the focal length of the lens group can be adjusted, which is beneficial to the flexibility of practical application.

The lasers include but are not limited to 830nm semiconductor lasers and 785nm semiconductor lasers.

On the other hand, the present invention also provides a detection method, using the subcutaneous detection device based on the conical mirror structure of the present invention, comprising: step S1. Determine the spatial offset distance according to the specific subcutaneous depth level to be detected; step S2. Select the conical mirror structure, set it at a preset position on the first optical path, and form an annular excitation region whose size satisfies the spatial offset distance; Step S3. Use the central region of the annular excitation region to connect with the detector The receiving end of the device is provided with a first imaging component and a second imaging component for a pair of conjugate surfaces; step S4 . The signal light generated by excitation is collected to the detector through the second optical path for biometric signal analysis.

In the step S2, the position of the conical mirror structure is also adjusted along the first optical path, to obtain annular excitation regions with different radii, and to excite signal light from different depths under the skin.

The present invention also provides a detection system for non-invasively detecting blood biomarker information of a finger or toenail bed, comprising an optical chamber and a supporting member, the optical chamber and the supporting member form a finger or toe end placement chamber to accommodate the finger or toe; the support is movably connected with the optical bin; the optical bin is used to integrate the above-mentioned parts of the subcutaneous detection device based on the conical mirror structure except the laser and the detector; the optical The side of the bin facing the support is provided with an optical window, and the placement 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 biomarkers in the nail bed blood are detected, and the reflected or refracted signal light is collected to obtain information of the biomarkers in the nail bed blood.

The optical bin provides excitation light and collects the returned signal light, emits the excitation light through the optical window, and collects the returned signal light. The support is used to support the finger or toe of the biological to be detected. The detection system is used for non-invasive detection of nail bed characteristic signals of biological fingers or toes. When detecting the biomarkers in the blood of the nail bed, the biological finger or toe to be detected is placed in the biological finger or toe placement bin, and the fingernail is correspondingly placed directly under the optical window. The non-invasive detection is simple and efficient, and the information of the biomarkers in the blood of the nail bed can be obtained by the detection, which can accurately reflect the disease or health status of the nail bed.

The optical chamber and the support member are connected by a rotating member, and a biological finger or toe placement chamber is formed between the optical chamber and the support member. The biological finger or toe placement chamber is used to place the biological finger or toe to be detected.

The rotating member is a hinge or a bearing. The optical compartment is rotated counterclockwise through the hinge or bearing, and the optical compartment is preferably rotated counterclockwise by 90°, which is convenient for checking the light transmittance of the optical window and easy to replace when the optical window is damaged.

A removable rubber ring is provided at the entrance of the biological finger or toe placement bin. The rubber ring is used to fix the biological finger or toe to be detected, and can be replaced according to the size of the biological finger or toe to be detected. The diameter of the rubber ring is preferably 10mm-20mm.

The optical bin and the support member can also be slidably connected. The optical bin is provided with a chute, and the support is provided with a slide rail; the support is fixed, and the optical bin slides away from the support, according to the finger or toe of the creature to be detected. dimension, the biological finger or toe placement chamber is formed between the optical chamber and the support.

Or the optical compartment is provided with a slide rail, and the support is provided with a chute; the optical compartment is fixed, and the support slides away from the optical compartment, according to the biological finger or toe to be detected. The size of the tip, the biological finger or toe placement chamber is formed between the optical chamber and the support.

Or the optical bin and the support member are slidably connected through a sliding connection member. The optical chamber and the support member can slide simultaneously, and the biological finger or toe placement chamber is formed between the optical chamber and the support member.

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

The optical window is made of transparent resin or quartz glass. The material selected for the optical window should have high transmittance and allow the excitation light with a wavelength of preferably 785 nm or 830 nm to pass therethrough.

The present invention also provides another detection system for detecting biomarker information under the skin of a limb, comprising an optical chamber, an optical fiber transmission structure and a strap, the optical fiber transmission structure is used for optically connecting the optical chamber and the a strap, which is used to surround and accommodate the limb; the optical chamber is provided with a light-passing hole on the surface, and the optical chamber is used to integrate the part of the subcutaneous detection device of the present invention 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 connecting two ends of the optical fiber bundle, and the first optical fiber coupling system is used for deriving the excitation light from the optical fiber into the bandage along the optical fiber bundle and the second optical fiber coupling system in turn, and emit the signal light after being reflected or refracted by the biomarker under the skin of the limb, and the signal light follows the The second optical fiber coupling system, the optical fiber bundle and the first optical fiber coupling system are introduced into the optical bin; the optical fiber bundle and the light-passing hole are connected through the optical fiber coupling system. The excitation light provided in the optical chamber is transmitted to the surface of the limb to be tested through the optical fiber transmission structure; the signal light returned from the surface is recoupled and then transmitted into the optical chamber. It is suitable for different scenarios, the length of the optical fiber bundle is changed to meet the different spatial positions of the optical bin and the limb to be measured, and the subcutaneous detection device of the present invention is integrated through the optical bin, which is convenient to use.

Compared with the prior art, the main beneficial effects of the present invention are:

1. A subcutaneous detection device based on a conical mirror structure of the present invention forms a ring-shaped excitation based on the conical mirror structure, and in combination with the first imaging component, the collection of signal light can be enhanced, and at the same time, the possible risks to the subcutaneous surface caused by the point-shaped spot excitation are avoided. , which improves the signal collection efficiency and safety of the subcutaneous non-invasive detection device; it is beneficial to further optimize the reliability and accuracy of the optical non-invasive detection. The detection system of the present invention integrates the subcutaneous detection device of the present invention, and has the advantages of simple structure, low cost, high efficiency, flexible design and convenient setting.

2. A detection method provided by another aspect of the present invention has corresponding advantages due to the use of the subcutaneous detection device of the present invention. The steps are simple and efficient, and the biometric information of the same depth level under the skin can be obtained as required, which is conducive to non-invasive subcutaneous detection. Further popularization of equipment.

Description of drawings

Figure 1 is a schematic diagram of spatial offset.

FIG. 2 is a schematic diagram of the annular excitation region and the central region according to the first embodiment of the present invention.

3 is a schematic diagram of a subcutaneous detection device based on a conical mirror structure according to Embodiment 1 of the present invention.

FIG. 4 is a schematic diagram of a detection method according to Embodiment 1 of the present invention.

FIG. 5 is a schematic diagram of a conical mirror structure and related components according to Embodiment 2 of the present invention.

FIG. 6 is a schematic diagram of a detection system in Embodiment 3 of the present invention.

FIG. 7 is a schematic diagram of a detection system in Embodiment 4 of the present invention.

FIG. 8 is a schematic diagram of the rotation of the optical bin in the fourth embodiment of the present invention.

FIG. 9 is a schematic diagram of a detection system and related structures in Embodiment 5 of the present invention.

Detailed ways

The technical solutions in the specific embodiments of the present invention will be clearly and completely described below. Obviously, the described embodiments are only a part of the embodiments of the present invention, but not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts 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 understood from the following description of the embodiments in conjunction with the accompanying drawings. In the figures, parts of the same structure or function are marked with the same reference numerals, and for reasons of clarity of illustration, if necessary, not all shown parts are marked with the associated reference numerals in all the figures.

Example 1

Referring to FIG. 1 , as shown in FIG. 3 , the subcutaneous detection device based on the conical mirror structure of this embodiment is integrated through an optical chamber I-1, including a laser 1 arranged along the first optical path L1, an excitation fiber coupler 102, The conical mirror structure 3, the laser 1 and the excitation fiber coupler 102 are used to emit excitation light, and the excitation light emits signal light after being emitted or refracted by the subcutaneous biomarker; the first imaging component 2, The second imaging component 4 and the detector 5; the excitation fiber coupler 102 is directly connected with the laser 1 through the optical fiber 101, and the light output by the laser 1 is converted into a parallel light beam and enters the plane side of the conical mirror structure 3, from the conical mirror structure 3 The light emitted from the convex surface is an annular beam; the annular beam is irradiated on the surface of the skin A through the first optical path L1 to form an annular excitation area Q; the first imaging component 2 and the second imaging component 4 are a pair of focusing lenses with a conjugate structure . The focal length range of the focusing lens is 5mm-900mm. The focal length f ₁ of the first imaging component 2 is preferably 20 mm, and the focal length of the second imaging component is preferably 50 mm. In this embodiment, the excitation light source assembly includes the laser 1 and the optical collimation structure of the excitation fiber coupler 102. For the convenience of description, the first imaging part 2 and the second imaging part 4 are respectively a focusing lens as an example, and Not limited. The excitation light source assembly can include other optical elements, and the optical collimation structure can also use other optical elements such as collimating lenses; there can also be multiple focusing lenses, and the focal length can be adjusted and set according to actual needs, which is not limited. In a practical application of this embodiment, except the laser 1 and the detector 2, other components are integrated in the optical bin I-1. The signal light in the central region C generated by the excitation of the annular excitation region Q enters the second optical path L2 and is collected by the second imaging component 4 . The detector 5 receives the signal light converged by the second imaging component 4 through the collection fiber bundle 51 . The incident end face of the collecting fiber bundle 51 and the central region C are on a pair of conjugate planes. In this embodiment, the incident end face of the collecting fiber bundle 51 is the incident face of the fiber coupler 52 . In this embodiment, the central area C is located on the optical axis of the second optical path L2. In this embodiment, the signal light to be collected is taken from the subcutaneous tissue as an example for description.

In this embodiment, the excitation fiber coupler 102 is a single or multiple GRIN lenses, and the numerical aperture of the excitation fiber coupler 102 is 0.22. The optical fiber is used in conjunction with the excitation fiber coupler 102 to realize the optical path connection, which can not only generate parallel beams but also realize optical path bending according to the actual structural design requirements. In this embodiment, the output wavelength of the laser is preferably 785 nm or 830 nm. The annular excitation region Q is generated based on the conical mirror structure 3, that is, the annular excitation is performed. The central region C of the annular excitation region is the position with the same spatial offset distance offset from the excitation point (the point on the circumference of the annular excitation region Q). The signal light reflects the biosignature signals from the same depth level under the skin. The signals are accumulated and the intensity is high. The excitation of the annular excitation region Q achieves efficient single-point signal collection at the central region C, and also effectively reduces the injection point-shaped spot excitation band. Side effects of local overheating, high energy density, and risk of burning tissue.

In the optical path structure design in this embodiment, the first optical path L1 and the second optical path L2 are partially overlapped, and a dichroic light splitting element 6 is arranged at the intersection of the two. The dichroic light splitting element 6 used in this embodiment is a dichroic mirror, which can turn the first optical path or the second optical path for beam separation. The dichroic spectroscopic element 6 can also be a component having dichroism, such as a dichroic film, a dichroic plate, and a dichroic beam splitter, and is not limited. In this embodiment, the dichroic light splitting element 6 is used to reflect the light emitted from the conical mirror structure 3 when it reaches between the first imaging component 2 and the second imaging component 4 , and transmit the signal light collected by the first imaging component 2 at the same time. . Specifically, the dichroic mirror turns the first optical path L1, converts the diverging annular light emitted by the conical mirror structure 3 into a collimated annular light beam and reflects it to the direction of the skin A, and can transmit the signal light returned at the skin A, In this embodiment, the reflection angle of the annular beam on the dichroic mirror is preferably 45°.

A band-pass filter element T is arranged before the second imaging element 4 along the second optical path L2 to filter out stray light whose wavelength is shorter than the wavelength of the signal light. The center wavelength of the band-pass filter element T is the same as that of the laser. wavelength matching. In this embodiment, the band-pass filter element T is disposed on the second optical path L2 between the second imaging element 4 and the dichroic light splitting element 6 . It is possible to improve the collection quality, avoid stray light being also collected as signal light, and reduce the risk of signal distortion of the detector 5 .

In this embodiment, the conical mirror structure 3 includes a conical lens. The cone angle of the axicon lens is in the range of 0.5°-40°, preferably 20°, and the radius of the corresponding annular excitation region Q is in the range of 1mm-9mm, preferably 2mm when the position of the axicon lens is fixed. The number of the axicon lenses may also be more than one. The tapered mirror structure 3 may include an optical fiber and a tapered lens disposed on the exit end face of the optical fiber, which is not limited. In a practice of this embodiment, the conical mirror structure 3 is connected with the excitation fiber coupler 102 through the optical fiber 101 .

As shown in FIG. 4 , the detection method in this embodiment includes: adopting the subcutaneous detection device based on the conical mirror structure of this embodiment, including: step S1. Determine the spatial offset distance according to the specific subcutaneous depth level to be detected; Step S2. Select the conical mirror structure, set it at a preset position on the first optical path, and form an annular excitation region whose size satisfies the spatial offset distance; Step S3. Use the central region of the annular excitation region and the detection The receiving end of the detector is provided with a first imaging part and a second imaging part for a pair of conjugate planes; step S4 . The signal light generated by excitation is collected to the detector through the second optical path for biometric signal analysis. In this embodiment, the size of the annular excitation region can be changed by replacing the cone lenses with different cone angles, thereby changing the spatial offset distance ΔS ₁ corresponding to the collected signal light in the central region, and obtaining a biometric signal of a specific subcutaneous depth.

Embodiment 2

The main difference between the second embodiment of the present invention and the first embodiment, with reference to FIG. 2 and FIG. 3 , as shown in FIG. 5 , the conical mirror structure 3 is arranged in the through lens barrel 7 , and the size of the through openings at both ends of the lens barrel 7 is the same as that of the cone. The clear aperture of the conical mirror structure 3 is matched, and the aperture stop formed by the opening will not weaken the excitation light incident to the conical mirror structure 3 . The track is to open a chute G on the side wall 71 of the lens barrel; a slider is provided in the chute G, and the slider includes a limit part 81 and a control part 82 for controlling the movement of the limit part. The edges of the conical mirror structure 3 are fixedly connected (in this embodiment, the conical mirror structure 3 is an axicon lens). The control end 82 a of the control part 82 is provided outside the side wall 71 of the lens barrel. Using the position controlled by the mechanical structure to adjust the position of the conical mirror structure 3 is easy to manufacture, low cost and easy to operate. The lens barrel 7 of this embodiment is made of aluminum material that has undergone oxidation and blackening treatment.

In the detection method of this embodiment, on the basis of Embodiment 1, in step S2, the position of the conical mirror structure 3 is also adjusted along the first optical path L1 to obtain annular excitation regions Q with different radii, and excitation Signal light at different depths under the skin.

Embodiment 3

The detection system in this embodiment is used for non-invasive detection of biomarkers in the blood of the nail bed under the nail. Referring to FIG. 6 , the detection system includes an optical bin I-1 and an optical window I-2 disposed on the optical bin I-1.

The optical bin I-1 is used to integrate the subcutaneous detection device of the present invention, provides excitation light and collects the returned signal light, projects the excitation light to the nail bed to be detected through the optical window I-2, and collects the returned signal Light.

In this embodiment, the optical window I-2 is a circular sheet-like structure. The thickness of the optical window I-2 is 1 mm, and the diameter of the optical window is 5 mm. In other embodiments, the optical window I-2 can also be set in an ellipse, a square, a rectangle, or the like. The material of the optical window I-2 is a transparent resin, and the selected material has high transmittance and can allow the excitation light with a wavelength of 785 nm or 830 nm to pass therethrough.

During detection, place the fingernail of the finger to be detected directly under the optical window I-2, and 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, and the The biomarkers in the blood of the nail bed are detected, and the returned signal light is collected to obtain the information of the biomarkers in the blood of the nail bed.

Embodiment 4

This embodiment integrates the subcutaneous detection device of any one of Embodiments 1 to 3, and provides a detection system for non-invasive detection of biomarkers in the blood of the nail bed of a finger or toenail, which is used for non-invasive detection of biomarkers in the blood in the nail bed under the nail. The object, referring to FIG. 7, includes an optical chamber I-1 and a support member I-5, and the optical chamber I-1 is movably connected with the support member I-5, in particular, connected by a rotating member; in the optical chamber A finger or toe end placement bin I-4 is formed between I-1 and the support member I-5.

The optical bin I-1 is used to integrate the part other than the laser and the detector of the subcutaneous detection device in any of the first to third embodiments of the present invention. When in use, the laser and the detector are externally connected. , used to provide excitation light, and the optical bin is used to collect the signal light reflected or refracted by the skin; an optical window I-2 is also provided on the optical bin I-1, and the optical window I-2 is arranged on the optical bin I-1. The cartridge I-1 faces the side of the support member I-5.

In this embodiment, the shape of the optical window I-2 is a square sheet-like structure, but is not limited to a square sheet-like structure, the side length of the optical window I-2 is 10mm, and the thickness is 1mm; the optical window The material of I-2 is quartz glass, the selected material has high transmittance and can allow the transmission of excitation light with a wavelength of 785nm or 830nm. 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 as to obtain the nail bed blood. Biomarker information.

8, the optical bin I-1 and the support member I-5 are connected by a rotating member I-3, the rotating member I-3 is a hinge, and the optical bin I-1 rotates counterclockwise through the hinge, The counterclockwise rotation angle of the optical bin I-1 is preferably 90°, which is convenient for checking the light transmittance of the optical window I-2, and secondly, when the optical window I-2 is damaged, it is easy to replace.

A finger or toe end placement chamber I-4 is formed between the optical chamber I-1 and the support member I-5, and the finger or toe end placement chamber I-4 corresponds to the optical window I-2 to accommodate Finger or toe, the finger or toe end placement bin I-4 is used to place the finger to be tested; the support member I-5 is used to support the finger to be tested. When the finger to be detected is placed in the finger or toe placement bin I-4, the fingernail of the finger to be detected is placed directly below the optical window I-2.

A rubber ring I-6 is provided at the entrance of the finger or toe placement bin I-4. The rubber ring I-6 can be disassembled and replaced to fix the finger to be detected and prevent the finger to be detected from accidentally sliding. detection error. The rubber ring I-6 can be made into different sizes to be suitable for fingers of different thicknesses to be detected. In this embodiment, the diameter of the rubber ring I-6 is preferably 15mm.

When it is necessary to detect the biomarkers in the blood of the nail bed of the finger, place the finger to be detected in the finger or toe end placement bin I-4, and place the fingernail of the finger to be detected in the optical window I-2 correspondingly 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 blood of the nail bed are detected, and the returned signal light is collected, thereby obtaining Information on biomarkers in nail bed blood.

Preferably, the optical bin I-1 is used to integrate any subcutaneous detection device in Embodiments 1 to 3 of the present invention, including the laser and the detector.

Embodiment 5

This embodiment integrates any of the subcutaneous detection devices in the first embodiment to the third embodiment to provide a detection system for detecting biomarker information under the skin of a limb. 9, the detection system includes an optical bin I-1, an optical fiber transmission structure and a strap II-5, and the optical fiber transmission structure is used to optically connect the optical bin I-1 and the strap II-5, The strap II-5 is used to wrap around and accommodate the limb II-7. The optical chamber I-1 is used to integrate the part of the subcutaneous detection device in any one of the first to third embodiments of the present invention except the laser and the detector; when in use, the optical chamber is connected to the excitation light source and the The detector is used for providing excitation light to be conducted to the skin through an optical chamber, and the optical chamber is used for collecting the signal light reflected or refracted by the skin and performing analysis. The strap is provided with a detection window II-4. The optical fiber transmission structure includes a first optical fiber coupling system II-2 connected with the light-passing hole, a second optical fiber coupling system II-3, and connecting the first optical fiber coupling system II-2 and the second optical fiber coupling system Fiber optic bundle II-6 of II-3. The optical fiber transmission structure transmits the excitation light provided in the optical bin I-1 to the skin surface of the limb to be tested; and transmits the signal light returned from the skin surface 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 window II-4 is arranged on the outside of the strap II-5, and the number of the detection windows II-4 is 4 to 15, which are evenly distributed on the strap II-5; preferably, the number of collection windows II-4 is for 12. Each detection window II-4 can be connected with an optical compartment I-1. When detecting the biomarkers in the tissue fluid or blood under the skin of the limb II-7, place the limb on the inner side of the strap II-5. The belt II-5 is made of nylon material, which can be directly attached to the limb. The excitation light in the optical bin I-1 is transmitted to the skin surface of the limb to be tested through the optical fiber transmission structure, and then the signal returned by the skin is detected. The optical bin I-1 is transmitted through the optical fiber transmission structure and analyzed.

Preferably, the optical bin I-1 is used to integrate any subcutaneous detection device in Embodiments 1 to 3 of the present invention, including the laser and the detector.

Some common English nouns or letters used in the present invention for the convenience of description are only used for exemplary designation rather than limited interpretation or specific usage, and their possible Chinese translations or specific letters should not limit the protection scope of the present invention . It should also be noted that in this document, relational terms such as first and second are used only to distinguish one entity or operation from another, and do not necessarily require or imply those entities or operations There is no such actual relationship or order between them. Moreover, the terms "comprising", "comprising" or any other variation thereof are intended to encompass a non-exclusive inclusion such that a process, method, article or device that includes a list of elements includes not only those elements, but also includes not explicitly listed or other elements inherent to such a process, method, article or apparatus. The present invention has been described in detail above, and the structure and working principle of the present invention are described with specific examples herein. The descriptions of the above embodiments are only used to help understand the method and core idea of the present invention. For those skilled in the art, without departing from the principles of the present invention, several improvements or modifications can be made, and these improvements also fall within the scope of protection of the claims of the present invention.

Claims (10)

1. A subcutaneous detection device based on a conical mirror structure, characterized in that it comprises an excitation light source assembly and a conical mirror structure arranged along a first optical path, the first optical path is used to form an annular excitation region on the skin, so The excitation light source assembly is used to emit excitation light, and the excitation light emits signal light after being emitted or refracted by the subcutaneous biomarker; a first imaging part, a second imaging part and a detector arranged along a second optical path, the second optical path is used for collecting signal light; The excitation light source assembly includes a laser and an optical collimation structure, and the light output by the laser is converted into a parallel beam by the optical collimation structure, enters the plane side of the conical mirror structure, and exits from the convex surface of the conical mirror structure The light is a ring beam; the ring beam forms a ring excitation area through the first optical path; The first imaging component and the second imaging component form a conjugate optical structure; the central area of the annular excitation region and the receiving end of the detector are on a pair of conjugate planes. 2 . The subcutaneous detection device based on a conical mirror structure according to claim 1 , wherein the conical mirror structure comprises an axicon lens, and the first imaging component and/or the second imaging component comprises a focusing component. 3 . lens. 3. A subcutaneous detection device based on a conical mirror structure according to claim 2, wherein the conical mirror structure further comprises a track fixed at a position parallel to the optical axis of the first optical path; The conical lens is slidably connected with the track. 4. A subcutaneous detection device based on a conical mirror structure according to any one of claims 1-3, wherein the first optical path and the second optical path are partially overlapped, and a two-way junction is provided at the intersection of the two. Color splitting element. 5 . The subcutaneous detection device based on the conical mirror structure according to claim 4 , wherein the dichroic light-splitting element is arranged between the first imaging component and the second imaging component, 5 . And it is located between the conical mirror structure and the first imaging component, and the light emitted from the conical mirror structure is reflected and then enters the first imaging component, and is collimated by the first imaging component to form the first imaging component. the annular excitation region; the signal light generated in the central region is collected by the first imaging component and then transmitted from the dichroic light splitting element. 6 . The subcutaneous detection device based on a conical mirror structure according to any one of claims 1 to 3 , wherein a bandpass filter is arranged along the second optical path before the second imaging component. 7 . The component is used for filtering out stray light with a wavelength shorter than that of the signal light, and the center wavelength of the band-pass filtering component is adapted to the wavelength of the laser. 7. A detection method, characterized in that: adopting the subcutaneous detection device based on the conical mirror structure according to any one of claims 1-6, comprising: Step S1. Determine the spatial offset distance according to the specific subcutaneous depth level to be detected; Step S2. Select the conical mirror structure, set it at a preset position on the first optical path, and form an annular excitation region whose size satisfies the spatial offset distance; Step S3. Set the first imaging component and the second imaging component with the central region of the annular excitation region and the receiving end of the detector as a pair of conjugate surfaces; Step S4. The signal light generated by excitation is collected to the detector through the second optical path for biometric signal analysis. 8 . The detection method according to claim 7 , wherein in the step S2 , the method further comprises adjusting the position of the conical mirror structure along the first optical path to obtain annular excitation regions with different radii, 9 . Signal light from different depths under the skin is excited. 9. A detection system for non-invasive detection of blood biomarker information in finger or toenail bed, characterized in that: comprising an optical chamber and a support, the optical chamber and the support form a finger or toe end placement chamber to accommodate Finger or toe; the optical compartment is used to integrate the part of the subcutaneous detection device according to any one of claims 1-6 except the laser and the detector; the optical compartment is opened on the side of the support There is an optical window, and the placement 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, and the biomarkers in the blood of the nail bed are detected. , and collect the reflected or refracted signal light, so as to obtain the information of the biomarkers in the blood of the nail bed. 10. A detection system for detecting biomarker information under the skin of a limb, characterized in that it comprises an optical chamber, an optical fiber transmission structure and a strap, and the optical fiber transmission structure is used for optically connecting the optical chamber and the a strap, which is used to surround and accommodate a limb; the optical compartment is used to integrate the part other than the laser and the detector of the subcutaneous detection device according to any one of claims 1-6; the The optical fiber transmission structure includes an optical fiber bundle, a first optical fiber coupling system and a second optical fiber coupling system connecting both ends of the optical fiber bundle, and the first optical fiber coupling system is used for leading the excitation light out of the optical bin, and sequentially along the optical fiber. The optical fiber bundle and the second optical fiber coupling system are introduced into the bandage, and the signal light is emitted after being reflected or refracted by the biomarker under the skin of the limb, and the signal light follows the second optical fiber coupling system, The fiber optic bundle and first fiber coupling system lead into the optical cartridge.

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