CN110037711B - Blood glucose optoacoustic accurate positioning detection device and method thereof - Google Patents
Blood glucose optoacoustic accurate positioning detection device and method thereof Download PDFInfo
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- CN110037711B CN110037711B CN201910329062.XA CN201910329062A CN110037711B CN 110037711 B CN110037711 B CN 110037711B CN 201910329062 A CN201910329062 A CN 201910329062A CN 110037711 B CN110037711 B CN 110037711B
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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
- A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
- A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
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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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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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, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
- A61B8/0833—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures
- A61B8/085—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures for locating body or organic structures, e.g. tumours, calculi, blood vessels, nodules
Abstract
The invention discloses a blood glucose optoacoustic accurate positioning detection device and a method thereof, wherein the device comprises a light source unit, a sample testing unit, a signal processing unit and a signal control unit, the light source unit comprises an OPO pulse laser, a diaphragm, a collimating lens, a first reflecting mirror, a second reflecting mirror, a third reflecting mirror and a focusing lens, the diaphragm, the collimating lens, the first reflecting mirror, the second reflecting mirror, the third reflecting mirror and the focusing lens are sequentially arranged on the right side of the OPO pulse laser along the light propagation direction, and the sample testing unit comprises an ultrasonic detector, a three-dimensional scanning translation stage and a three-dimensional scanning controller. The device is characterized in that the pulse excitation light spots fall into the blood vessel, ultrasonic mechanical waves are generated by exciting blood in the blood vessel, and the photoacoustic signals carrying blood glucose concentration information are released, so that blood glucose photoacoustic information in blood of the blood vessel is truly obtained, and then the accurate positioning of the blood vessel in the tissue to be tested is achieved, and the accuracy and reliability of blood glucose photoacoustic detection are greatly improved.
Description
Technical Field
The invention relates to the technical field of blood glucose photoacoustic accurate positioning detection, in particular to a blood glucose photoacoustic accurate positioning detection device and a blood glucose photoacoustic accurate positioning detection method.
Background
Diabetes is now severely threatening the life health and quality of life of people. However, at present, no method and medicine for radically treating diabetes is available, and the change of blood sugar concentration can be only monitored for a long time and controlled by using the medicine. The current methods for detecting blood glucose concentration are mainly invasive and minimally invasive methods, and the methods can cause certain damage to skin and human tissues, so that physical and psychological burden, economic pressure and even secondary infection risks are caused for patients needing frequent monitoring of blood glucose changes. Thus, noninvasive detection of blood glucose is an inevitable trend in detecting the development of diabetes. Currently, noninvasive blood glucose detection methods are most represented by optical detection methods, such as: near infrared/mid infrared spectroscopy, optical rotation, OCT, raman spectroscopy, and the like. The detection of the pure optical method is restricted and influenced to a certain extent due to the adverse effect caused by tissue light scattering. The photoacoustic noninvasive detection technology has the advantages of both optics and ultrasound, and the laser is used for exciting the tested tissue to generate ultrasonic mechanical waves, namely: the photoacoustic signal is captured by the ultrasonic detector, and then the photoacoustic signal carrying the blood glucose concentration information of the tested tissue is subjected to signal analysis processing, so that the blood glucose concentration in the body can be known. The method adopts the photoinduced ultrasonic technology, and avoids adverse effects caused by tissue light scattering in principle, thereby improving the accuracy of blood glucose detection. However, in many of the conventional studies of photoacoustic measurement of blood glucose, studies on a simulated body solution, an isolated blood, and an isolated tissue fluid are relatively few, and in the case of photoacoustic measurement, the measurement is performed at any position of a certain portion of a tissue to be measured, and in many cases, only the glucose content in the tissue fluid in a human tissue is studied. Research shows that the blood sugar content in tissue fluid is different from that in blood to some extent. Meanwhile, the detection accuracy is affected due to individual variability of different people and the characteristics of certain parts of the human body. The blood sugar in the blood can be detected to truly reflect the blood sugar content of the human body, so that the blood sugar concentration of the blood in the blood vessel of the human body needs to be detected. The blood glucose concentration detection of blood in the blood vessel is required to accurately position the blood vessel, and pulse excitation light spots fall into the blood vessel to excite the blood in the blood vessel to generate ultrasonic mechanical waves and release photoacoustic signals carrying blood glucose concentration information.
Disclosure of Invention
(one) solving the technical problems
Aiming at the defects of the prior art, the invention provides a blood sugar optoacoustic accurate positioning detection device and a method thereof, which solve the problems that in the past blood sugar optoacoustic detection research detection, the research on the in-vivo optoacoustic blood sugar detection is relatively less for an imitation body solution, in-vitro blood and in-vitro tissue fluid, and in the in-vivo optoacoustic detection research, the detection is carried out on any position of a certain part of a detected tissue, and in a great case, the research is only carried out on the glucose content in tissue fluid in human tissue, and the detection data is inaccurate due to the fact that the blood sugar content in the tissue fluid and the blood sugar content in the blood have certain difference.
(II) technical scheme
In order to achieve the above purpose, the present invention provides the following technical solutions: the blood sugar optoacoustic accurate positioning detection device comprises a light source unit, a sample test unit, a signal processing unit and a signal control unit, wherein the light source unit comprises an OPO pulse laser, a diaphragm, a collimating lens, a first reflecting mirror, a second reflecting mirror, a third reflecting mirror and a focusing lens, the diaphragm, the collimating lens, the first reflecting mirror, the second reflecting mirror, the third reflecting mirror and the focusing lens are sequentially arranged on the right side of the OPO pulse laser along the light propagation direction, the sample test unit comprises a tested tissue, a blood vessel, a medical coupling liquid, an ultrasonic detector, a sample bracket, a three-dimensional scanning translation stage and a three-dimensional scanning controller, the tested tissue is placed on the front end face of the ultrasonic detector, the medical coupling liquid is uniformly smeared between the tested tissue and the ultrasonic detector, the ultrasonic detector is placed on the sample bracket, the sample bracket is fixedly connected with a vertical panel of the three-dimensional scanning translation stage through a connecting rod, the three-dimensional scanning translation stage is provided with the three-dimensional scanning controller, the three-dimensional scanning translation stage is used for sequentially transmitting signals of the tested tissue and the tested tissue along the light propagation direction through the three-dimensional scanning controller, the three-dimensional scanning translation stage is used for sequentially carrying digital signal to a digital oscillograph along the digital signal acquisition interface, the digital signal acquisition device is used for acquiring signals along the digital signal acquisition interface of the digital oscillograph, the digital signal acquisition device comprises a digital signal acquisition interface, and a digital signal acquisition interface is used for acquiring signals, and the digital signal acquisition of the digital signal is used for acquiring signals, the computer is electrically connected with the OPO pulse laser through a data line.
Preferably, the OPO pulse laser parameters are adjustable, and the adjustable parameters include: output wavelength lambda, output energy E and repetition frequency f.
Preferably, the three-dimensional scanning translation stage controls the three-dimensional scanning translation stage X, Y and the three-dimensional scanning translation stage Z to move step sizes ax, ay and az and step numbers Nx, ny and Nz through a three-dimensional scanning controller.
Preferably, the signal filter is used for filtering to remove low-frequency noise interference in cooperation with the photoacoustic signal captured by the ultrasonic detector.
Preferably, the signal amplifier is used for performing voltage gain amplification in cooperation with the photoacoustic signal filtered by the signal filter, so that subsequent data analysis and processing are facilitated.
Preferably, a photoacoustic accurate positioning detection method for blood sugar is also provided, and the specific method is as follows:
firstly, placing a tested tissue with the surface uniformly coated with medical coupling liquid on the front end surface of an ultrasonic detector, and resetting a three-dimensional scanning translation stage to enable the tested sample to return to an initial position;
setting parameters of the OPO pulse laser, wherein the parameters specifically comprise: the output wavelength lambda, the output energy E and the repetition frequency f are output, and meanwhile, the three-dimensional scanning translation stage X, Y and the three-dimensional scanning translation stage Z are set through the three-dimensional scanning controller, namely the moving step length ax, ay, az and the step number Nx, ny and Nz, so that the length (Lx, ly and Lz) of the tested tissue in the X, Y and the three directions of Z are respectively as follows: lx=nx×ax, ly=ny×ay, lz=nz×az;
starting an OPO pulse laser, enabling the OPO pulse laser to emit pulse laser beams with certain wavelength and energy, removing part of stray light through a diaphragm, collimating by a collimating lens, sequentially enabling the laser beams with parallel angles to be incident at a vertical angle through a first reflecting mirror, a second reflecting mirror and a third reflecting mirror, and focusing the pulse laser beams to be incident on the surface of the tissue to be measured through a focusing lens, wherein the focal length of the focusing lens is exactly the distance between the focusing lens and the surface of the tissue to be measured;
fourthly, opening a control program, and driving the tissue to be tested and the ultrasonic detector to translate along X, Y and Z directions by the three-dimensional scanning translation stage according to the moving step length and the step number set by the three-dimensional scanning controller in the second step; the tissue to be measured is in the initial plane in the depth direction, namely: the three-dimensional scanning translation stage drives the tested tissue to perform progressive scanning in X and Y directions, continuous uninterrupted scanning is performed between rows according to an arc shape, and when each scanning point is completed, ix and iy are respectively added with 1 until ix and iy reach Nx and Ny respectively, two-dimensional scanning on an initial plane of the iz=1 is finished;
fifthly, capturing a photoacoustic voltage signal generated by exciting each focus spot of a focus spot on an initial plane by an ultrasonic detector while scanning in two dimensions, filtering by a signal filter and amplifying by a signal amplifier, acquiring and displaying by a digital oscilloscope, transmitting the photoacoustic voltage signal to a computer for storage by a GPIB-USB-HS interface card, and synchronously obtaining and storing the photoacoustic amplitude of the photoacoustic signal generated by each focus spot according to a software program;
step six, after two-dimensional scanning of an initial plane iz=1 is completed, a three-dimensional scanning translation stage translates by one step distance in the Z direction, namely iz=2, a focusing light spot enters a second depth position, and then the three-dimensional scanning translation stage drives a tested tissue to perform progressive scanning on a new depth plane along X and Y directions according to the moving step length and the step number which are set by a three-dimensional scanning controller in the step two, wherein the method is the same as that of the step four; on the second depth plane, after ix and iy reach Nx and Ny respectively, the two-dimensional scanning of the second depth plane is finished, and meanwhile, the photoacoustic amplitude generated by excitation at each focusing light spot on the second depth plane is obtained in the same way as in the fifth step;
seventh, after two-dimensional scanning of plane iz=1 is completed, the three-dimensional scanning translation stage translates by one step distance in the Z direction, namely iz=3, the focusing light spot enters into a third depth position, then the operations from the fourth step to the sixth step are repeated, finally, when ix, iy and iz all reach respective step numbers Nx, ny and Nz simultaneously, the whole three-dimensional scanning is finished, and at the moment, the photoacoustic amplitude of the tested tissue on all depth planes is obtained, namely: a three-dimensional photoacoustic amplitude data matrix;
eighth, three-dimensional photoacoustic images of the tissue to be tested or photoacoustic two-dimensional images on a certain depth plane are obtained through three-dimensional and two-dimensional image reconstruction algorithms, blood vessel images in the tissue to be tested can be obtained, and specific positions of blood vessels in the tissue to be tested can be obtained;
step nine, calculating the steps and the steps of the three-dimensional scanning translation stage which need to move in X, Y and Z directions according to the blood vessel position obtained in the step eight, and driving the tested tissue to move to accurately fall into the blood vessel of the tested tissue through the three-dimensional scanning translation stage;
tenth, the focused light spot in the blood vessel excites blood to generate a photoacoustic signal comprising blood sugar concentration, the photoacoustic signal of blood sugar is captured by an ultrasonic detector, then the photoacoustic amplitude of blood sugar in the blood vessel is obtained as in the fifth step, the photoacoustic amplitude of blood sugar in the blood vessel of the tested tissue can be accurately obtained according to the steps aiming at tested samples containing different blood sugar concentrations, then a relation model between concentration gradient and the photoacoustic amplitude of blood sugar in the blood vessel is established by utilizing a statistical modeling algorithm, and finally accurate prediction of the tested tissue with unknown blood sugar concentration is realized.
(III) beneficial effects
The invention provides a blood glucose photoacoustic accurate positioning detection device and a method thereof. The beneficial effects are as follows: according to the blood glucose photoacoustic accurate positioning detection device and the blood glucose photoacoustic accurate positioning detection method, through the arrangement of the light source unit, the OPO pulse laser, the diaphragm, the collimating lens, the first reflecting mirror, the second reflecting mirror, the third reflecting mirror, the focusing lens, the sample testing unit, the tissue to be tested, the blood vessel, medical coupling liquid, the ultrasonic detector, the sample bracket, the three-dimensional scanning translation stage, the three-dimensional scanning controller, the signal processing unit, the signal filter, the signal amplifier, the signal control unit, the digital oscilloscope, the GPIB-USB-HS interface card and the computer, the blood vessel is accurately positioned in a targeted manner when blood glucose concentration of blood in the blood vessel is detected, and through dropping pulse excitation light spots into the blood vessel, ultrasonic mechanical waves are generated by exciting the blood in the blood vessel, photoacoustic signals carrying blood glucose concentration information are released, so that the photoacoustic information in the blood vessel is truly obtained, and then accurate positioning of the blood vessel in the tissue to be tested is achieved, and accuracy and reliability of blood glucose photoacoustic detection are greatly improved.
Drawings
Fig. 1 is a schematic diagram of the photoacoustic accurate positioning detection principle of blood sugar with the structure of the present invention.
In the figure: 1. a light source unit; 101. an OPO pulse laser; 102. a diaphragm; 103. a collimating lens; 104. a first mirror; 105. a second mirror; 106. a third mirror; 107. a focusing lens; 2. a sample testing unit; 201. a tissue to be tested; 202. a blood vessel; 203. medical coupling liquid; 204. an ultrasound probe; 205. a sample holder; 206. a three-dimensional scanning translation stage; 207. a three-dimensional scan controller; 3. a signal processing unit; 301. a signal filter; 302. a signal amplifier; 4. a signal control unit; 401. a digital oscilloscope; 402. GPIB-USB-HS interface card; 403. and a computer.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
As shown in fig. 1, the present invention provides a technical solution: the blood glucose photoacoustic accurate positioning detection device comprises a light source unit 1, a sample testing unit 2, a signal processing unit 3 and a signal control unit 4, wherein the light source unit 1 comprises an OPO pulse laser 101, a diaphragm 102, a collimating lens 103, a first reflecting mirror 104, a second reflecting mirror 105, a third reflecting mirror 106 and a focusing lens 107, the diaphragm 102, the collimating lens 103, the first reflecting mirror 104, the second reflecting mirror 105, the third reflecting mirror 106 and the focusing lens 107 are sequentially arranged on the right side of the OPO pulse laser 101 along the light propagation direction, the sample testing unit 2 comprises a tested tissue 201, a blood vessel 202, a medical coupling liquid 203, an ultrasonic detector 204, a sample bracket 205, a three-dimensional scanning translation stage 206 and a three-dimensional scanning controller 207, the tested tissue 201 is arranged on the front end surface of the ultrasonic detector 204, a medical coupling liquid 203 is uniformly smeared between the tested tissue 201 and the ultrasonic detector 204, by setting the medical coupling liquid 203, the ultrasonic detector 204 is placed on the sample bracket 205, the sample bracket 205 is fixedly connected with the vertical panel of the three-dimensional scanning translation stage 206 through a connecting rod, the three-dimensional scanning translation stage 206 is provided with a three-dimensional scanning controller 207, the three-dimensional scanning translation stage 206 moves the sample bracket 205 carrying the ultrasonic detector 204 and the tested tissue 201 in parallel along the three-dimensional direction through the three-dimensional scanning controller 207, the three-dimensional scanning translation stage 206 controls the moving step sizes ax, ay, az and the step numbers Nx, ny and Nz of the three-dimensional scanning translation stage 206 and Z through the three-dimensional scanning controller 207, the signal processing unit 3 is sequentially provided with a signal filter 301 and a signal amplifier 302 along the signal propagation direction, the signal amplifier 302 is used for carrying out voltage gain amplification in cooperation with the photoacoustic signals filtered by the signal filter 301, the parameters of the OPO pulse laser 101 are adjustable for facilitating subsequent data analysis and processing, and the adjustable parameters include: the signal filter 301 is used for filtering to remove low-frequency noise interference in cooperation with a photoacoustic signal captured by the ultrasonic detector 204, the signal control unit 4 comprises a digital oscilloscope 401, a GPIB-USB-HS interface card 402 and a computer 403, a trigger signal of the OPO pulse laser 101 is electrically connected with the digital oscilloscope 401 through a wire and used for acquiring a synchronous trigger signal of the signal by the digital oscilloscope, the GPIB-USB-HS interface card 402 transmits photoacoustic data acquired by the digital oscilloscope 401 to the computer 403 for subsequent analysis, and the computer 403 is electrically connected with the OPO pulse laser 101 through a data wire, so that the effects of controlling the operations such as parameter setting and light source excitation output of the laser through OPO pulse laser control software installed in the computer are achieved.
When in use, firstly, medical coupling liquid 203 is uniformly smeared between a tested tissue 201 and an ultrasonic detector 204, the tested tissue 201 is placed on a sample bracket 205, then, a three-dimensional scanning translation stage 206 is used for controlling a three-dimensional scanning controller 207, the sample bracket 205 carrying the ultrasonic detector 204 and the tested tissue 201 moves in parallel along a three-dimensional direction, and meanwhile, an OPO pulse laser 101 is used for carrying out pulse excitation on a blood vessel 202 in the tested tissue 201 through a diaphragm 102, a collimating lens 103, a first reflecting mirror 104, a second reflecting mirror 105, a third reflecting mirror 106 and a focusing lens 107, an excitation light spot falls into the blood vessel 202, ultrasonic mechanical waves are generated by utilizing blood in the excited blood vessel, photoacoustic signals carrying blood glucose concentration information are released, the blood glucose photoacoustic information in the blood vessel 202 is truly obtained, meanwhile, a signal amplifier 302 is used for carrying out voltage gain amplification on the filtered photoacoustic signals, and finally, the digital oscilloscope 401 is transmitted to a computer 403 through a GPIB-USB-HS interface card 402 for carrying out subsequent analysis, and finally, the accurate positioning of the tested blood vessel 203 in the blood vessel 201 is well known in the prior art.
The invention also provides a blood sugar optoacoustic accurate positioning detection method, which comprises the following steps:
firstly, placing a tested tissue with the surface uniformly coated with the medical coupling liquid 203 on the front end surface of an ultrasonic detector 204, and resetting a three-dimensional scanning translation stage 206 to enable the tested sample to return to an initial position;
in the second step, parameters of the OPO pulse laser 101 are set, specifically including: the three-dimensional scanning translation stage 206X, Y and the three-dimensional scanning translation stage Z are set by the three-dimensional scanning controller 207, and the moving step length ax, ay, az and the step number Nx, ny, nz in the three directions of X, Y and Z are respectively: lx=nx×ax, ly=ny×ay, lz=nz×az;
thirdly, opening an OPO pulse laser 101, enabling the OPO pulse laser 101 to emit pulse laser beams with certain wavelength and energy, removing part of stray light through a diaphragm 102, collimating by a collimating lens 103, then sequentially enabling laser beams with parallel angles to be incident at a vertical angle through a first reflecting mirror 104, a second reflecting mirror 105 and a third reflecting mirror 106, and enabling the pulse laser beams to be incident on the surface of a tested tissue in a focusing mode through a focusing lens 107, wherein the focal length of the focusing lens 107 is exactly the distance between the focusing lens 107 and the surface of the tested tissue;
fourth, a control program is opened, and the three-dimensional scanning translation stage 206 drives the tested tissue 201 and the ultrasonic detector 204 to translate along X, Y and Z directions according to the moving step length and the step number set by the three-dimensional scanning controller 207 in the second step; the tissue 201 to be measured is in the initial plane in the depth direction, that is: the three-dimensional scanning translation stage 206 drives the tested tissue 201 to scan line by line in the X and Y directions, and continuous scanning is performed between the lines according to an arc shape, and each time a scanning point is completed, ix and iy are respectively added with 1, two-dimensional scanning on an initial plane of the iz=1 is finished until the ix and iy reach Nx and Ny respectively;
fifthly, capturing photoacoustic voltage signals generated by excitation of each focus spot of a focus spot on an initial plane by the ultrasonic detector 204 while scanning in two dimensions, filtering by the signal filter 301 and amplifying by the signal amplifier 302, acquiring and displaying by the digital oscilloscope 401, transmitting the photoacoustic voltage signals to the computer 403 for storage by the GPIB-USB-HS interface card 402, and synchronously obtaining and storing the photoacoustic amplitude of the photoacoustic signals generated by each focus spot according to a software program;
sixth, after two-dimensional scanning of the initial plane iz=1 is completed, the three-dimensional scanning translation stage 206 translates in the Z direction by a step distance, that is, iz=2, the focusing light spot enters into the second depth position, and then, according to the moving step length and the step number set by the three-dimensional scanning controller 207 in the second step, the three-dimensional scanning translation stage 206 drives the tested tissue 201 to perform progressive scanning in the X and Y directions on the new depth plane, and the method is the same as in the fourth step; on the second depth plane, after ix and iy reach Nx and Ny respectively, the two-dimensional scanning of the second depth plane is finished, and meanwhile, the photoacoustic amplitude generated by excitation at each focusing light spot on the second depth plane is obtained in the same way as in the fifth step;
seventh, after two-dimensional scanning of plane iz=1 is completed, the three-dimensional scanning translation stage 206 translates in Z direction by one step distance, i.e. iz=3, the focused light spot enters into the third depth position, then the operations from the fourth step to the sixth step are repeated, finally, when ix, iy and iz all reach respective step numbers Nx, ny and Nz simultaneously, the whole three-dimensional scanning is finished, and at this time, the photoacoustic amplitude of the measured tissue 201 on all depth planes is obtained, namely: a three-dimensional photoacoustic amplitude data matrix;
eighth, a three-dimensional photoacoustic image of the tissue 201 to be tested or a photoacoustic two-dimensional image on a certain depth plane is obtained through a three-dimensional and two-dimensional image reconstruction algorithm, and meanwhile, a blood vessel image in the tissue 201 to be tested can be obtained, and a specific position of a blood vessel in the tissue to be tested is obtained;
a ninth step of calculating steps and steps of the three-dimensional scanning translation stage 206 to be moved in X, Y and Z directions according to the blood vessel position obtained in the eighth step, and then driving the tested tissue 201 to move to accurately drop the focusing light spot into the blood vessel of the tested tissue 201 through the three-dimensional scanning translation stage 206;
tenth, the focused light spot in the blood vessel excites blood to generate a photoacoustic signal including blood sugar concentration, the photoacoustic signal including blood sugar concentration is captured by the ultrasonic detector 204, then the photoacoustic amplitude of blood sugar in the blood vessel is obtained as in the fifth step, the photoacoustic amplitude of blood sugar in the blood vessel of the tested tissue 201 can be accurately obtained according to the steps for tested samples with different blood sugar concentrations, then a relation model between concentration gradient and the photoacoustic amplitude of blood sugar in the blood vessel is established by using a statistical modeling algorithm, and finally accurate prediction of the tested tissue 201 with unknown blood sugar concentration is realized.
In summary, the blood glucose photoacoustic accurate positioning detection device and the use method thereof can be obtained, through the arrangement of the light source unit 1 and the cooperation of the OPO pulse laser 101, the diaphragm 102, the collimating lens 103, the first reflecting mirror 104, the second reflecting mirror 105, the third reflecting mirror 106, the focusing lens 107, the sample testing unit 2, the tissue 201, the blood vessel 202, the medical coupling liquid 203, the ultrasonic detector 204, the sample bracket 205, the three-dimensional scanning translation stage 206, the three-dimensional scanning controller 207, the signal processing unit 3, the signal filter 301, the signal amplifier 302, the signal control unit 4, the digital oscilloscope 401, the GPIB-USB-HS interface card 402 and the computer 403, the accurate positioning of the blood vessel 202 of the blood in the blood vessel is achieved, and through the pulse excitation light spot falling into the blood vessel 202, ultrasonic mechanical waves are generated by using the blood in the excited blood vessel, the photoacoustic information in the blood vessel is really obtained, and then the accurate positioning of the blood vessel 203 in the tissue 201 is greatly improved in accuracy and reliability of the photoacoustic detection are achieved.
It is noted that relational terms such as first and second, and the like are 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. Moreover, 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. Without further limitation, an element defined by the phrase "comprising one … …" does not exclude the presence of other like elements in a process, method, article, or apparatus that comprises the element.
Although embodiments of the present invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made therein without departing from the principles and spirit of the invention, the scope of which is defined in the appended claims and their equivalents.
Claims (2)
1. The utility model provides a blood sugar optoacoustic accurate location detection device, includes light source unit (1), sample test unit (2), signal processing unit (3) and signal control unit (4), its characterized in that: the light source unit (1) comprises an OPO pulse laser (101), a diaphragm (102), a collimating lens (103), a first reflecting mirror (104), a second reflecting mirror (105), a third reflecting mirror (106) and a focusing lens (107), wherein the diaphragm (102), the collimating lens (103), the first reflecting mirror (104), the second reflecting mirror (105), the third reflecting mirror (106) and the focusing lens (107) are sequentially arranged on the right side of the OPO pulse laser (101) along the light propagation direction, the sample testing unit (2) comprises a tested tissue (201), a blood vessel (202), a medical coupling liquid (203), an ultrasonic detector (204), a sample bracket (205), a three-dimensional scanning translation stage (206) and a three-dimensional scanning controller (207), the tested tissue (201) is arranged on the front end face of the ultrasonic detector (204), the medical coupling liquid (203) is uniformly smeared between the tested tissue (201) and the ultrasonic detector (204), the ultrasonic detector (204) is arranged on the sample bracket (205), the sample bracket (205) is fixedly translated with the three-dimensional scanning stage (206) through the sample bracket (205) and the three-dimensional scanning stage (206), the three-dimensional scanning translation stage (206) moves a sample bracket (205) carrying an ultrasonic detector (204) and a tissue (201) to be tested in parallel along a three-dimensional direction through a three-dimensional scanning controller (207), a signal processing unit (3) is sequentially provided with a signal filter (301) and a signal amplifier (302) along a signal propagation direction, the signal control unit (4) comprises a digital oscilloscope (401), a GPIB-USB-HS interface card (402) and a computer (403), a trigger signal of the OPO pulse laser (101) is electrically connected with the digital oscilloscope (401) through a wire and is used for synchronously triggering signals of the digital oscilloscope acquisition signals, the GPIB-USB-HS interface card (402) transmits photoacoustic data acquired through the digital oscilloscope (401) to the computer (403) for subsequent analysis, and the computer (403) is electrically connected with the OPO pulse laser (101) through a data line;
the specific positioning detection steps of the detection device are as follows:
firstly, placing a tested tissue with the surface uniformly coated with a medical coupling liquid (203) on the front end surface of an ultrasonic detector (204), and resetting a three-dimensional scanning translation stage (206) to enable the tested sample to return to an initial position;
setting parameters of the OPO pulse laser (101), which specifically comprises the following steps: the three-dimensional scanning translation stage (206) X, Y and the three-dimensional scanning translation stage Z are set by the three-dimensional scanning controller (207) at the same time, and the moving step length ax, ay, az and the step number Nx, ny and Nz in the three directions of X, Y and Z are respectively as follows: lx=nx×ax, ly=ny×ay, lz=nz×az;
starting an OPO pulse laser (101), enabling the OPO pulse laser (101) to emit pulse laser beams with certain wavelength and energy, enabling the pulse laser beams to pass through a diaphragm (102), enabling the pulse laser beams to be collimated by a collimating lens (103), enabling the pulse laser beams to pass through a first reflecting mirror (104), a second reflecting mirror (105) and a third reflecting mirror (106) in sequence, enabling the laser beams with parallel angles to be converted into vertical angles to be incident, enabling the pulse laser beams to be focused and incident on the surface of a tested tissue through a focusing lens (107), and enabling the focal length of the focusing lens (107) to be exactly the distance between the focusing lens (107) and the surface of the tested tissue;
fourthly, opening a control program, and driving the tested tissue (201) and the ultrasonic detector (204) to translate along X, Y and Z directions according to the moving step length and the step number set by the three-dimensional scanning controller (207) in the second step by the three-dimensional scanning translation stage (206); the tissue under test (201) is in an initial plane in the depth direction, namely: the three-dimensional scanning translation stage (206) drives the tested tissue (201) to scan line by line in the X and Y directions, continuous uninterrupted scanning is carried out between the lines according to an arc shape, and each time a scanning point is completed, ix and iy are respectively added with 1, and two-dimensional scanning on an initial plane of the iz=1 is finished until the ix and iy reach Nx and Ny respectively;
fifthly, capturing photoacoustic voltage signals generated by excitation of each focus spot of a focus spot on an initial plane by an ultrasonic detector (204) while scanning in two dimensions, filtering by a signal filter (301) and amplifying by a signal amplifier (302), acquiring and displaying by a digital oscilloscope (401), transmitting the photoacoustic voltage signals to a computer (403) for storage by a GPIB-USB-HS interface card (402), and synchronously acquiring and storing the photoacoustic amplitude of the photoacoustic signals generated by each focus spot according to a software program;
sixthly, after two-dimensional scanning of an initial plane iz=1 is completed, a three-dimensional scanning translation stage (206) translates by one step distance in the Z direction, namely iz=2, a focusing light spot enters a second depth position, and then the three-dimensional scanning translation stage (206) drives a tested tissue (201) to scan line by line along X and Y directions on a new depth plane according to the moving step length and the step number set by a three-dimensional scanning controller (207) in the second step, wherein the method is the same as that of the fourth step; on the second depth plane, after ix and iy reach Nx and Ny respectively, the two-dimensional scanning of the second depth plane is finished, and meanwhile, the photoacoustic amplitude generated by excitation at each focusing light spot on the second depth plane is obtained in the same way as in the fifth step;
seventh, after two-dimensional scanning of plane iz=2 is completed, the three-dimensional scanning translation stage (206) translates in Z direction by one step distance, namely iz=3, the focusing light spot enters into a third depth position, then the operations from the fourth step to the sixth step are repeated, finally, when ix, iy and iz all reach respective step numbers Nx, ny and Nz simultaneously, the whole three-dimensional scanning is finished, and at the moment, the photoacoustic amplitude of the measured tissue (201) on all depth planes is obtained, namely: a three-dimensional photoacoustic amplitude data matrix;
eighth, obtaining a three-dimensional photoacoustic image of the tissue (201) to be tested or a photoacoustic two-dimensional image on a certain depth plane through a three-dimensional and two-dimensional image reconstruction algorithm, simultaneously obtaining a blood vessel image of the tissue (201) to be tested, and obtaining a specific position of a blood vessel in the tissue to be tested;
a ninth step of calculating the steps and steps of the three-dimensional scanning translation stage (206) which need to move in X, Y and Z directions according to the blood vessel position obtained in the eighth step, and then driving the tested tissue (201) to move to accurately drop the focusing light spot into the blood vessel of the tested tissue (201) through the three-dimensional scanning translation stage (206);
tenth, the focused light spot in the blood vessel excites blood to generate a photoacoustic signal comprising blood sugar concentration, the photoacoustic signal of blood sugar is captured by the ultrasonic detector (204), then the photoacoustic amplitude of blood sugar in the blood vessel is obtained as in the fifth step, the photoacoustic amplitude of blood sugar in the blood vessel of the tested tissue (201) can be accurately obtained according to the steps aiming at tested samples containing different blood sugar concentrations, then a relation model between concentration gradient and the photoacoustic amplitude of blood sugar in the blood vessel is established by utilizing a statistical modeling algorithm, and finally accurate prediction of the tested tissue (201) with unknown blood sugar concentration is realized.
2. The positioning detection method of the photoacoustic accurate positioning detection device for blood sugar according to claim 1, wherein the method comprises the steps of:
firstly, placing a tested tissue with the surface uniformly coated with a medical coupling liquid (203) on the front end surface of an ultrasonic detector (204), and resetting a three-dimensional scanning translation stage (206) to enable the tested sample to return to an initial position;
setting parameters of the OPO pulse laser (101), which specifically comprises the following steps: the three-dimensional scanning translation stage (206) X, Y and the three-dimensional scanning translation stage Z are set by the three-dimensional scanning controller (207) at the same time, and the moving step length ax, ay, az and the step number Nx, ny and Nz in the three directions of X, Y and Z are respectively as follows: lx=nx×ax, ly=ny×ay, lz=nz×az;
starting an OPO pulse laser (101), enabling the OPO pulse laser (101) to emit pulse laser beams with certain wavelength and energy, enabling the pulse laser beams to pass through a diaphragm (102), enabling the pulse laser beams to be collimated by a collimating lens (103), enabling the pulse laser beams to pass through a first reflecting mirror (104), a second reflecting mirror (105) and a third reflecting mirror (106) in sequence, enabling the laser beams with parallel angles to be converted into vertical angles to be incident, enabling the pulse laser beams to be focused and incident on the surface of a tested tissue through a focusing lens (107), and enabling the focal length of the focusing lens (107) to be exactly the distance between the focusing lens (107) and the surface of the tested tissue;
fourthly, opening a control program, and driving the tested tissue (201) and the ultrasonic detector (204) to translate along X, Y and Z directions according to the moving step length and the step number set by the three-dimensional scanning controller (207) in the second step by the three-dimensional scanning translation stage (206); the tissue under test (201) is in an initial plane in the depth direction, namely: the three-dimensional scanning translation stage (206) drives the tested tissue (201) to scan line by line in the X and Y directions, continuous uninterrupted scanning is carried out between the lines according to an arc shape, and each time a scanning point is completed, ix and iy are respectively added with 1, and two-dimensional scanning on an initial plane of the iz=1 is finished until the ix and iy reach Nx and Ny respectively;
fifthly, capturing photoacoustic voltage signals generated by excitation of each focus spot of a focus spot on an initial plane by an ultrasonic detector (204) while scanning in two dimensions, filtering by a signal filter (301) and amplifying by a signal amplifier (302), acquiring and displaying by a digital oscilloscope (401), transmitting the photoacoustic voltage signals to a computer (403) for storage by a GPIB-USB-HS interface card (402), and synchronously acquiring and storing the photoacoustic amplitude of the photoacoustic signals generated by each focus spot according to a software program;
sixthly, after two-dimensional scanning of an initial plane iz=1 is completed, a three-dimensional scanning translation stage (206) translates by one step distance in the Z direction, namely iz=2, a focusing light spot enters a second depth position, and then the three-dimensional scanning translation stage (206) drives a tested tissue (201) to scan line by line along X and Y directions on a new depth plane according to the moving step length and the step number set by a three-dimensional scanning controller (207) in the second step, wherein the method is the same as that of the fourth step; on the second depth plane, after ix and iy reach Nx and Ny respectively, the two-dimensional scanning of the second depth plane is finished, and meanwhile, the photoacoustic amplitude generated by excitation at each focusing light spot on the second depth plane is obtained in the same way as in the fifth step;
seventh, after two-dimensional scanning of plane iz=2 is completed, the three-dimensional scanning translation stage (206) translates in Z direction by one step distance, namely iz=3, the focusing light spot enters into a third depth position, then the operations from the fourth step to the sixth step are repeated, finally, when ix, iy and iz all reach respective step numbers Nx, ny and Nz simultaneously, the whole three-dimensional scanning is finished, and at the moment, the photoacoustic amplitude of the measured tissue (201) on all depth planes is obtained, namely: a three-dimensional photoacoustic amplitude data matrix;
eighth, obtaining a three-dimensional photoacoustic image of the tissue (201) to be tested or a photoacoustic two-dimensional image on a certain depth plane through a three-dimensional and two-dimensional image reconstruction algorithm, simultaneously obtaining a blood vessel image of the tissue (201) to be tested, and obtaining a specific position of a blood vessel in the tissue to be tested;
a ninth step of calculating the steps and steps of the three-dimensional scanning translation stage (206) which need to move in X, Y and Z directions according to the blood vessel position obtained in the eighth step, and then driving the tested tissue (201) to move to accurately drop the focusing light spot into the blood vessel of the tested tissue (201) through the three-dimensional scanning translation stage (206);
tenth, the focused light spot in the blood vessel excites blood to generate a photoacoustic signal comprising blood sugar concentration, the photoacoustic signal of blood sugar is captured by the ultrasonic detector (204), then the photoacoustic amplitude of blood sugar in the blood vessel is obtained as in the fifth step, the photoacoustic amplitude of blood sugar in the blood vessel of the tested tissue (201) can be accurately obtained according to the steps aiming at tested samples containing different blood sugar concentrations, then a relation model between concentration gradient and the photoacoustic amplitude of blood sugar in the blood vessel is established by utilizing a statistical modeling algorithm, and finally accurate prediction of the tested tissue (201) with unknown blood sugar concentration is realized.
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Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2007097654A (en) * | 2005-09-30 | 2007-04-19 | Fujifilm Corp | Blood information measuring device |
| CN107157491A (en) * | 2017-07-21 | 2017-09-15 | 江西科技师范大学 | Light sound blood sugar detection means and method that a kind of blood vessel is automatically positioned |
| CN107228904A (en) * | 2017-07-21 | 2017-10-03 | 江西科技师范大学 | A kind of photic ultrasonic non-invasive glucose monitoring device and method |
| CN206945622U (en) * | 2017-07-21 | 2018-01-30 | 江西科技师范大学 | A kind of non-invasive glucose monitoring device based on photoacoustic technique |
| CN108209940A (en) * | 2016-12-14 | 2018-06-29 | 现代自动车株式会社 | Optoacoustic, noninvasive and continuous blood glucose measuring device |
| CN109363645A (en) * | 2018-10-29 | 2019-02-22 | 中国科学院上海技术物理研究所 | A kind of human vas detection method based on Laser Photoacoustic Spectroscopy |
| CN210170053U (en) * | 2019-04-23 | 2020-03-24 | 江西科技师范大学 | Accurate location detection device of blood glucose optoacoustic |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP6587385B2 (en) * | 2014-11-27 | 2019-10-09 | キヤノン株式会社 | Subject information acquisition apparatus and subject information acquisition method |
-
2019
- 2019-04-23 CN CN201910329062.XA patent/CN110037711B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2007097654A (en) * | 2005-09-30 | 2007-04-19 | Fujifilm Corp | Blood information measuring device |
| CN108209940A (en) * | 2016-12-14 | 2018-06-29 | 现代自动车株式会社 | Optoacoustic, noninvasive and continuous blood glucose measuring device |
| CN107157491A (en) * | 2017-07-21 | 2017-09-15 | 江西科技师范大学 | Light sound blood sugar detection means and method that a kind of blood vessel is automatically positioned |
| CN107228904A (en) * | 2017-07-21 | 2017-10-03 | 江西科技师范大学 | A kind of photic ultrasonic non-invasive glucose monitoring device and method |
| CN206945622U (en) * | 2017-07-21 | 2018-01-30 | 江西科技师范大学 | A kind of non-invasive glucose monitoring device based on photoacoustic technique |
| CN109363645A (en) * | 2018-10-29 | 2019-02-22 | 中国科学院上海技术物理研究所 | A kind of human vas detection method based on Laser Photoacoustic Spectroscopy |
| CN210170053U (en) * | 2019-04-23 | 2020-03-24 | 江西科技师范大学 | Accurate location detection device of blood glucose optoacoustic |
Non-Patent Citations (1)
| Title |
|---|
| 任重等.基于OPO脉冲激发的血糖光声检测影响因素研究.光谱学与光谱分析.2018,第38卷(第10期),3023-3029. * |
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