CN115120184A - Signal collecting assembly - Google Patents
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- CN115120184A CN115120184A CN202110334433.0A CN202110334433A CN115120184A CN 115120184 A CN115120184 A CN 115120184A CN 202110334433 A CN202110334433 A CN 202110334433A CN 115120184 A CN115120184 A CN 115120184A
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
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- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
- A61B5/14507—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue specially adapted for measuring characteristics of body fluids other than blood
- A61B5/1451—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue specially adapted for measuring characteristics of body fluids other than blood for interstitial fluid
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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Abstract
The invention provides a signal collection assembly, which comprises an imaging system and a collection optical fiber bundle; the imaging system comprises a first imaging module and a second imaging module which are in a conjugate optical structure; the collecting optical fiber bundle is of an annular laminated structure and comprises a central optical fiber and a plurality of outer-layer optical fiber rings; the collection fiber bundle entrance pupil plane is coincident with an exit pupil plane of the imaging system; the second imaging module comprises a first focusing lens and a second focusing lens, and the relative positions of the first focusing lens and the second focusing lens can be adjusted; and the signal light sequentially enters the collection optical fiber bundle through the first imaging module and the second imaging module. The device can flexibly collect signal light at a specific spatial offset position, and has the advantages of simple structure, high operation efficiency and low cost.
Description
Technical Field
The invention belongs to the technical field of optical detection, and particularly relates to a signal collection assembly.
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 admitted to be prior art by inclusion in this section.
The application of the optical detection technology has been popularized in various fields in life, and particularly, the optical detection technology has universal application in medical examination related to human health, and meanwhile, the optical detection technology also has the requirements of further penetration and popularization. The biological characteristics can be reflected through the characteristics of the signal light, 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 analysis of substances. Especially in the application of the biomedical field, the Raman spectrum detection technology can reflect the change of human tissue cell molecules, is a new technology for detecting early lesions, can improve the problems of the conventional detection method by the characteristics of no pain, no wound, simplicity, rapidness and the like, and is one of potential methods for obtaining the application of the blood non-invasive biochemical analysis. 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 a raman detection system as an example, the existing detection system generally includes an excitation light source, a light path structure, and a detection component. Wherein the exciting light source irradiates to the tested sample through the exciting light path. The Raman signal light is collected through the collection light path and transmitted to the detection component, and the Raman signal intensity at different wavelengths is detected.
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 that need 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 the skin tissue is mainly composed 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 without any wound, for example, blood sugar detection requires blood drawing test or finger-prick to draw bloodAnd detecting. 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 in a location outside of a medical laboratory. For example, in the application of the conventional raman spectroscopy, which can only test the depth of hundreds of micrometers below the surface, and can detect the spectral information of deep subcutaneous biomarkers without damage, as shown in fig. 1, the excitation light L1 is focused and irradiated on the tissue to be tested, raman signal light is generated at different tissue depths (skin a, subcutaneous tissue B, blood vessel U) in the excitation area and around the excitation area, and according to the photon migration theory, the spatial offset distance Δ S from the central excitation point along the spatial offset direction X is determined by the photon migration theory 1 The larger the signal light from the deeper sample is. It is obvious that a new optical detection system is needed to detect the signal light of a deeper layer. Therefore, there is a need to develop a signal collecting assembly capable of effectively collecting signals reflecting biological characteristics of a specific subcutaneous depth part, which is beneficial to improving the collecting efficiency and ensuring reliable detection results.
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 statements in this background section merely indicate prior art as known to the public and are not, of course, representative of existing art in this field.
Disclosure of Invention
The following description is made for some of the principles and concepts related to the present invention and is presented for purposes of illustration and description only and is not intended to limit the scope of the invention.
Based on the principle of the SORS technology, the invention has the basic starting point of the photon migration theory, as shown in FIG. 1, when exciting light L1 is incident to the surface layer of a sample to be detected, the surface layer sample is excited or scattered to generate broadband fluorescence, wherein a part of scattered light reaches the inside of the sample, Raman scattered photons generated at the deep layer inside the sample are easier to migrate transversely in the scattering process compared with photons at the surface layer of the sample, and the Raman scattered photons return to the surface layer of the sample after multiple scattering and are collected. ToThe positions of the scattered light reaching different depths in the sample after returning to the surface layer have different spatial offset distances deltaS from the incident point of the exciting light L1 in the X direction on the surface layer of the sample 1 . When the space is shifted by a distance Δ S 1 When the value is equal to 0, the incident point of the light source is superposed with the signal light collection point, the density of the excited photons is maximum, most of the signals collected by the system come from the surface layer of the sample, and the signals in the deep layer of the sample are submerged; when the space is shifted by a distance Δ S 1 When the signal light attenuation is not equal to 0, the signal light from the surface layer in the collected signal light attenuates quickly, the signal light from the deep layer of the sample attenuates slowly, the specific gravity of the Raman scattering photons in the deeper layer is increased, so that the spectrum separation is realized, and the characteristic signals of different deep layers in the sample can be obtained by combining a multivariate data analysis method. The technical principle is generally applied to the scene of extraction of Raman spectrum of substances concealed under opaque packaging materials.
The invention provides a signal collecting assembly aiming at the particularity of characteristic signal detection of a marker in biological tissue based on the principle, and aims to solve all or part of problems in the prior art. In the invention, the position of the convergence of the signal light returned by the excitation point on the surface of the biological tissue is called a zero-order offset point; Δ S from the excitation point 1 The position where the signal light returned from the skin surface position converges is called a first order offset point, and so on, the signal light of several order offset points can be collected.
The invention provides a signal collecting assembly, which comprises an imaging system and a collecting optical fiber bundle; the imaging system comprises a first imaging module and a second imaging module which are in a conjugate optical structure; the collecting optical fiber bundle is of an annular laminated structure and comprises a central optical fiber and a plurality of outer-layer optical fiber rings; the collection fiber bundle entrance pupil plane coincides with an exit pupil plane of the imaging system; the second imaging module comprises a first focusing lens and a second focusing lens, and the relative positions of the first focusing lens and the second focusing lens can be adjusted; and the signal light sequentially enters the collection optical fiber bundle through the first imaging module and the second imaging module.
The second imaging module comprises a track fixed in a position parallel to the optical axis of the first focusing lens; the first focusing lens is connected with the track in a sliding mode; the optical axis of the second focusing lens coincides with the optical axis of the first focusing lens; the second focusing lens is connected with the track in a sliding mode or in a fixed mode. The second imaging module is a lens group with adjustable focal length, and when the relative position of the first focusing lens and the second focusing lens is changed, the focal length of the lens group is correspondingly adjusted, so that the purpose of continuously adjusting the actual detection position of the biological tissue is achieved.
When the excitation light irradiates the biological tissue to generate signal light, the convergence point of the excitation light and the incident surface of the collection optical fiber bundle are on a pair of conjugate surfaces; spatial offset distance Δ S of biological tissue surface 1 Spatial offset distance Δ S from the surface of the collection fiber 2 There is a certain numerical relationship, according to the principle of optical conjugation, Δ S 1 And Δ S 2 The numerical relationship between the first and second imaging modules and the focal length f of the first and second imaging modules 1 And f 2 In this connection, f is therefore the point of convergence of the excitation light when it is on a pair of conjugate planes with the plane of incidence of the collection bundle of optical fibers 1 Invariant sum Δ S 1 Presetting the focal length f of the second imaging module under the determined condition 2 The outer optical fiber ring can collect specific Delta S 1 （ΔS 1 Not equal to 0), i.e. the detector is able to detect a characteristic signal at a specific depth inside the biological tissue.
The outer layer optical fiber ring has at least two layers. Preferably, the outer fiber ring has 3, 4 or 5 layers. The signal light collected by the first layer of optical fiber ring is delta S from the excitation point 1 The signal light returned from the surface of the biological tissue can collect more level-shifted signal light when there are second or more layers of the outer fiber ring. The better range of the number of layers of the outer layer optical fiber ring is 1-9 layers, and the signal light of 0-9 level offset points can be obtained, namely biological characteristic signals of 9 different depths in the biological tissue can be detected. In the preferred embodiment, the outer layer optical fiber ring has 3 layers, 4 layers or 5 layers and can collect the signal light of 0-3 level, 0-4 level or 0-5 level offset points. The surface characteristic signals of the excitation area and the surrounding biological tissues and the characteristic signals at different depths are fully collected by the detector, and the focal length of the second imaging module can be changedf 2 The characteristic signals of the specific depth range in the biological tissue are collected, the collection efficiency is greatly improved, the detection flexibility is improved, the structure is simple, and the cost is low.
The second imaging module is arranged in a through sleeve, and the size of through openings at two ends of the sleeve is matched with the numerical aperture of the second imaging module; the track is disposed on the sleeve sidewall.
The rail is a sliding groove on the side wall of the sleeve; a sliding block is arranged in the sliding groove and comprises a limiting part and a control part for controlling the limiting part to move, and the limiting part is fixedly connected with the edge of the first focusing lens; the control end of the control part is arranged outside the side wall of the sleeve. The mechanical structure is adopted to control the position of the first focusing lens and adjust the focal length of the second imaging module, so that the imaging lens is easy to manufacture, low in cost and convenient to operate.
The sleeve is made of an aluminum material subjected to oxidation blackening treatment. Light weight, low material cost and avoidance of scattering of the sleeve to the signal light.
The focal length range of the first imaging module is 5mm-500 mm. Preferably, the focal length of the first imaging module is 20 mm.
The laser light-transmitting excitation optical fiber is connected with a collimation optical fiber coupler, and the excitation light is emitted after being collimated by the collimation optical fiber coupler. The collimating optical fiber coupler is of a single lens or a structure with a plurality of lenses, is directly connected with the laser through the exciting optical fiber and plays a role in converting light output by the laser into parallel light to enter a subsequent light path, and the numerical aperture of the exciting optical fiber connected with the laser and the collimating optical fiber coupler is preferably 0.22. The excitation optical fiber is matched with the collimation optical fiber coupler to realize the connection of the light path, so that the design of the light path is more flexible, the turning of the light path can be realized according to the design requirement of an actual structure, and the miniaturization or portability requirement of the design of the detection equipment is better met.
Including but not limited to 830nm semiconductor lasers, 785nm semiconductor lasers.
A dichroic mirror is arranged on a light path between the first imaging module and the second imaging module; the dichroic mirror reflects the excitation light, then converges the excitation light through the first imaging module, and transmits the signal light collected by the first imaging module to the second imaging module. And part of the excitation light path and the collection light path are combined through the dichroic mirror, so that the optical structure design is simplified, and the flexibility of the overall structure design of the detection system is improved.
A first light filtering component is arranged on a light path between the dichroic mirror and the second imaging module; the central wavelength of the first filtering component is matched with the wavelength of the laser and is used for filtering stray light with the wavelength shorter than the wavelength of the signal light.
Preferably, the dichroic mirror reflects the excitation light at an angle of 45 °.
And a second light filtering component is arranged on a light path between the dichroic mirror and the laser, and the second light filtering component comprises a narrow-band light filter matched with the laser and is used for filtering out other wavelengths except the wavelength emitted by the laser in the exciting light.
In another aspect, the present invention further provides a detection method, which uses the signal collection assembly of the present invention, including: s1, irradiating biological tissues by exciting light, and determining the position of a first imaging module according to the position of a convergence point of the exciting light; s2, determining a spatial offset distance corresponding to a specific tissue depth according to a photon migration theory; and S3, setting the focal length of the second imaging module according to the spatial offset distance, and collecting signal light to the detector for subsequent biological characteristic signal analysis.
In the step S3, the focal length of the second imaging module is adjusted to obtain signal light of a multi-level offset point.
Compared with the prior art, the invention has the main beneficial effects that:
according to the signal collecting assembly, the first imaging module and the second imaging module which are optically conjugated are adopted to combine with the collecting optical fiber, so that signal light corresponding to a specific space offset distance position can be collected, deep biological characteristic signals in biological tissues can be detected, and the signal collecting efficiency of detection equipment is improved; the reliability and the accuracy of optical noninvasive detection are favorably improved. The second imaging module with the adjustable focal length can enable the outer layer optical fiber ring to continuously collect the signal light corresponding to the multi-stage offset point, and the flexibility and the integrity of signal light collection are further improved. The whole structure is simple, the cost is low, the structure design is flexible, and the device is particularly suitable for detecting the internal signal of the biological tissue.
Drawings
Fig. 1 is a schematic diagram of spatial offset.
Fig. 2 is a schematic diagram of a detection system according to a first embodiment of the invention.
Fig. 3 is an enlarged schematic view of an incident end face of a signal collection assembly according to a first embodiment of the invention.
Fig. 4 is a schematic diagram of a detection method according to a first embodiment of the invention.
Fig. 5 is a schematic diagram of a detection system according to a second embodiment of the invention.
Fig. 6 is a schematic view of a sleeve and a second imaging module according to a second embodiment of the present invention.
Detailed Description
The technical solutions in the embodiments of the present invention will be described clearly and completely below, and it should be apparent 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 detection system of the present embodiment includes a laser 1, a first imaging module 3, a second imaging module 4, and a detector 2; the detector 2 is optically coupled with the second imaging module 4 through a collection optical fiber bundle 5; the first imaging module 3 and the second imaging module 4 are in a conjugate optical structure, and form the imaging system; laserThe optical device 1 emits exciting light L1 to irradiate biological tissues to generate signal light L2, and the signal light L2 enters the collecting optical fiber bundle 5 through the first imaging module and the second imaging module in sequence; the excitation light L1 converges on a pair of conjugate planes with the incident plane of the collection fiber bundle 5. The imaging system and the collection optical fiber bundle 5 of the present embodiment constitute the signal collection assembly of the present embodiment, wherein the incident end face of the signal collection assembly is as shown in fig. 3, and the collection optical fiber bundle 5 is a ring-shaped laminated structure, and includes a central optical fiber (light-passing fiber core 0), a plurality of dark cores 5a for supporting and stabilizing the structure of the optical fiber bundle, and an outer layer optical fiber ring 5b of the outer layer. In this embodiment, the signal light L2 to be collected is illustrated as an example of a biological characteristic signal from subcutaneous tissue, and referring to fig. 1, the spatial offset distance Δ S of the surface of the skin a 1 The spatial offset distance Δ S from the incident end face of the collecting optical fiber bundle 5 (the incident end face of the optical fiber coupler 50 at the end of the optical fiber bundle in the present embodiment) 2 There is a certain numerical relationship, Δ S, according to the principle of optical conjugation 1 And Δ S 2 Is related to the focal length f of the first and second imaging modules 3 and 4 1 And f 2 The specific relationship is as follows: delta S 2 /ΔS 1 =f 2 /f 1 . Therefore, when the convergence point of the excitation light L1 is on a pair of conjugate planes with respect to the incident plane of the collection optical fiber 5, f 1 Invariant sum Δ S 1 Under the determined condition, presetting the focal length f of the second imaging module 2 The outer fiber ring 5B is capable of collecting signal light at a specific spatial offset distance, i.e. the detector 2 is capable of detecting characteristic signals of the surface (skin a) of biological tissue and of a specific depth inside (e.g. subcutaneous tissue B, blood vessels U, etc.).
In this embodiment, the laser 1 is a 785nm wavelength semiconductor laser, and the laser may be an 830nm semiconductor laser, but is not limited thereto. The laser 1 is connected with an excitation fiber 101, the excitation fiber 101 comprises a fiber collimator lens and a convergent fiber lens at an exit end, the convergent fiber lens enters from top to bottom along an optical axis of the first imaging module 3, and the convergent fiber lens irradiates on the biological tissue. In addition to the laser 1 and the detector 2, other components are integrated by means of an optical bin I-1.
Of the first imaging module 3Focal length f 1 The range is 5mm-500 mm. In the preferred embodiment, the focal length f of the first imaging module 1 Is 20mm, a convex lens is used. The second imaging module 4 in this embodiment also employs a convex lens. By replacing convex lenses of different focal lengths, the focal length f of the second imaging module 4 is rapidly switched 2 The signal light from a predetermined position can be collected into the collection fiber bundle 7 according to the spatial offset distance. In this embodiment, the outer layer optical fiber ring 5b has 2 layers, and the convex lens second imaging module 4 with a preset focal length can collect the signal light of the excitation central area and the signal light of 2 different offset positions, that is, the detector 2 can detect biological characteristic signals of 2 different depths in the biological tissue. By increasing the number of the outer layer of the optical fiber ring 5b, the signal light at a specific position can be obtained by replacing the convex lens in practical application, and the signal requirement of detecting a certain depth inside the biological tissue is met. The outer layer optical fiber ring 5b may have a dark core at a specific position according to practical situations, so as to save material cost, and is not limited.
As shown in fig. 4, the detection method in this embodiment, which uses the signal collection assembly of this embodiment, includes: s1, irradiating biological tissues by exciting light, and determining the position of a first imaging module according to the position of a convergence point of the exciting light; s2, determining a spatial offset distance corresponding to a specific tissue depth according to a photon migration theory; and S3, setting the focal length of the second imaging module according to the spatial offset distance, and collecting signal light to the detector for subsequent biological characteristic signal analysis.
Example two
The second embodiment of the present invention is mainly different from the first embodiment of the present invention, and as shown in fig. 5 and fig. 6, the second imaging module 4 includes a first focusing lens 41, a second focusing lens 42, and a track fixed at a position parallel to the optical axis N of the first focusing lens 41; a first focusing lens 41 is slidably connected to the track; the optical axis of the second focusing lens 42 coincides with the optical axis N of the first focusing lens 41. The second imaging module 4 is a lens group with adjustable focal length, and when the relative position of the first focusing lens 41 and the second focusing lens 42 is changed, the focal length of the lens group is adjusted accordingly. Achieve the actual detection position of the biological tissueThe purpose of continuous adjustment is achieved. In this embodiment, the second focusing lens 42 may be slidably coupled to the rail or fixedly coupled to the rail. When the second focusing lens 42 is also slidably connected to the rail, the second focusing lens 42 can be adjusted, the first focusing lens 41 can be adjusted, or both can be adjusted, so as to adjust the focal length of the lens group of the second imaging module 4. When the second focusing lens 42 is fixedly connected to the track, only the first focusing lens 41 is adjusted, and the focal length of the lens group can be changed, which is not limited. The number of the first focusing lens 41 and the second focusing lens 42 and the positions thereof arranged on the track are also not limited. The first imaging module 3 may also be the same or similar lens set structure as the second imaging module 4, such that f 1 The value of (f) can be adjusted to match the convergence point of the specific excitation light L1 with the specific requirements and structural design of actual detection, and when the wavelength of the excitation light source changes or the depth of the excitation light L1 required to be focused to the subcutaneous part changes, the adjustment can be carried out correspondingly without replacing the first imaging module 3, f 1 The value of (b) is not limited and may be set according to the actual application.
In this embodiment, a dichroic mirror M is disposed on an optical path between the first imaging module 3 and the second imaging module 4; the dichroic mirror M reflects the excitation light L1 and then converges the reflected excitation light by the first imaging module 3, and the signal light L2 collected by the first imaging module 3 is transmitted to the second imaging module 4 by the dichroic mirror M. And part of the excitation light path and the collection light path are combined through the dichroic mirror, so that the optical structure design is simplified, and the flexibility of the overall structure layout of the detection system is improved. It is preferable in the present embodiment that the angle at which the dichroic mirror M reflects the excitation light L1 is 45 °. In this embodiment, the laser 1 is connected to the excitation fiber 101 and the collimating fiber coupler 102, and the numerical apertures of the excitation fiber 101 and the collimating fiber coupler 102 are 0.22. The excitation light L1 passes through the excitation fiber 101 and the collimating fiber coupler 102, and then parallel light is incident on the surface of the dichroic mirror M.
In the present embodiment, a first filtering component T1 is provided in the optical path between the dichroic mirror M and the second imaging module 4; the center wavelength of the first filter component T1 is matched to the laser 1 wavelength, and is used for filtering out stray light having a wavelength shorter than that of the signal light. The first filter component T1 of the present embodiment is a high-pass filter.
In this embodiment, a second optical filter T2 is further disposed between the dichroic mirror M and the laser 1, and the second optical filter T2 is a narrow-band filter adapted to the laser 1 and is used for filtering out wavelengths other than the laser emission wavelength in the excitation light.
In one implementation of this embodiment, as shown in fig. 6, the second imaging module 4 is disposed in a through sleeve 7, the size of the through opening at both ends of the sleeve 7 matches with the numerical aperture of the second imaging module, and the aperture stop formed by the opening does not affect the collection of the signal light. The tracks are provided on the sleeve side wall 71.
In the specific implementation of this embodiment, the rail is provided with a chute G on the side wall 71 of the sleeve; a sliding block is arranged in the sliding groove G, the sliding block comprises a limiting part 81 and a control part 82 for controlling the movement of the limiting part, and the limiting part 81 is fixedly connected with the edge of the first focusing lens 41; the control end 82a of the control portion 82 is disposed outside the sleeve sidewall. The position of the first focusing lens 41 is controlled by adopting a mechanical structure, the focal length of the second imaging module is adjusted, and the optical imaging module is easy to manufacture, low in cost and convenient to operate. It should be appreciated that in other embodiments of the present embodiment, the second focusing lens 42 may be slidably or fixedly connected to the rail using similar structures. The number of the sliding blocks and the sliding grooves G can be set according to practical application conditions, and is not limited. The sleeve 7 of this embodiment is made of an aluminum material subjected to oxidation blackening treatment.
Referring to fig. 1 and fig. 3 in combination, in this embodiment, the outer fiber ring 5b has 2 layers, each layer has a light-transmitting fiber core 1 and a light-transmitting fiber core 2, and signal light in the excitation central region, that is, zero-order offset point signal light L20, and signal light at 2 different spatial offset distances (first-order offset point signal light L21, second-order offset point signal light L22) can be collected by continuously adjusting the focal length of the second imaging module 4, that is, the detector 2 can detect biological characteristic signals at 3 different depths inside the biological tissue.
In the detection method of this embodiment, on the basis of the first embodiment, in the step S3, the focal length of the second imaging module is adjusted to obtain the signal light corresponding to the multiple levels of offset points.
For clarity of description, the use of certain conventional and specific terms and phrases is intended to be illustrative and not restrictive, but rather to limit the scope of the invention to the particular letter and translation thereof. 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. Also, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. The present invention has been described in detail, and the structure and operation principle of the present invention are explained by applying specific embodiments, 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 (9)
1. A signal collection assembly, comprising: comprises an imaging system and a collection fiber bundle;
the imaging system comprises a first imaging module and a second imaging module which are in a conjugate optical structure; the collecting optical fiber bundle is of an annular laminated structure and comprises a central optical fiber and a plurality of outer-layer optical fiber rings;
the collection fiber bundle entrance pupil plane coincides with an exit pupil plane of the imaging system; the second imaging module comprises a first focusing lens and a second focusing lens, and the relative positions of the first focusing lens and the second focusing lens can be adjusted;
the signal light sequentially enters the collecting optical fiber bundle through the first imaging module and the second imaging module.
2. A signal collection assembly according to claim 1, wherein: the second imaging module comprises a track fixed in a position parallel to the optical axis of the first focusing lens; the first focusing lens is connected with the track in a sliding mode; the optical axis of the second focusing lens coincides with the optical axis of the first focusing lens; the second focusing lens is connected with the track in a sliding mode or in a fixed mode.
3. A signal collection assembly according to claim 2, wherein: the second imaging module is arranged in a through sleeve, and the size of through openings at two ends of the sleeve is matched with the numerical aperture of the second imaging module; the track is disposed on the sleeve sidewall.
4. A signal collection assembly according to claim 3, wherein: the track is a sliding groove on the side wall of the sleeve; a sliding block is arranged in the sliding groove and comprises a limiting part and a control part for controlling the movement of the limiting part, and the limiting part is fixedly connected with the edge of the first focusing lens; the control end of the control part is arranged outside the side wall of the sleeve.
5. A signal collection assembly according to claim 3, wherein: the sleeve is made of an aluminum material subjected to oxidation blackening treatment.
6. A signal collection assembly according to claim 1, wherein: the focal length range of the first imaging module is 5mm-500 mm.
7. A signal collection assembly according to any one of claims 1 to 6, wherein: the outer layer optical fiber ring has at least two layers.
8. A signal collection assembly according to claim 6, wherein: the outer layer optical fiber ring has 3 layers, 4 layers or 5 layers.
9. A signal collection assembly according to claim 6, wherein: the number of the outer layer optical fiber ring layers ranges from 1 to 9.
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| CN202110334433.0A CN115120184A (en) | 2021-03-29 | 2021-03-29 | Signal collecting assembly |
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| CN117617962A (en) * | 2023-12-25 | 2024-03-01 | 暨南大学 | Subcutaneous blood sugar measurement method based on space shift Raman |
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