A Photoacoustic Non-Destructive Glucose Localization Detection Device Based on Backward Mode and Its System Usage Method

Abstract

The present invention relates to a photoacoustic non-destructive blood glucose localization detection device based on a backward mode and a system usage method thereof. The device consists of a silica glass slide, a focusing lens, a micro ultrasonic sensor, a reflective objective lens, an optical fiber collimator, a fixture, a pre-signal amplifier, a displacement platform, a localization detection unit, a laser, and an optical fiber; the present invention also provides a method for vascular imaging localization and non-destructive blood glucose detection using the above device. The optical system adopted by the present invention uses a reflective objective lens to shape the light, making the entire optical system a backward structure. On the basis of sufficient beam energy intensity, the micro ultrasonic sensor is placed directly below the center of the reflective objective lens, which can improve the practicability of the device. Compared with similar detection devices and methods, it can not only achieve photoacoustic non-destructive blood glucose detection, but also achieve vascular imaging localization, blood glucose data processing, and the establishment of a prediction model, which can greatly improve the accuracy of blood glucose detection and the early warning of blood glucose concentration.

Description

Technical Field

[0001] The present invention relates to a photoacoustic non-destructive detection device, and particularly to a photoacoustic non-destructive blood glucose localization detection device based on a backward mode and a system usage method thereof. Background Art

[0002] Photoacoustic non-invasive blood glucose technology is a non-invasive detection technology based on the photoacoustic effect. By using the intensity (peak-to-peak value, integral value) and sound velocity of ultrasonic waves generated after blood absorbs light energy, a blood glucose prediction model is established, which has the characteristics of high resolution of light and high contrast of sound. In principle, it avoids the interference caused by strong light scattering in tissues and provides a highly sensitive measurement method for non-destructive blood glucose detection.

[0003] Diabetes is a common disease in the world. At present, the number of patients in our country has reached 5%. Due to the long-term disorder of metabolic function characterized by blood glucose concentration, a series of chronic complications such as diabetic nephropathy, diabetic eye complications, and diabetic cardiovascular complications will occur, seriously endangering the physical and mental health and even life of the affected population.

[0004] At present, science and technology and medical level are still unable to cure diabetes completely. Only by detecting blood glucose concentration and timely adjusting the dosage of drugs for conservative treatment. Blood glucose concentration is one of the important indicators for detecting diabetes. In order to avoid the occurrence of complications, patients need to self-detect blood glucose in real time. Traditional blood glucose detectors are invasive and cannot accurately select the detection site, causing multiple traumas. And the immune ability of diabetic patients is relatively poor. Using them will not only bring pain to patients but also cause secondary infections.

[0005] Photoacoustic non-invasive blood glucose detection technology has the characteristics of high resolution of light and high contrast of sound at the same time, and is widely used in biomedicine. By using the different ultrasonic velocities and intensities excited by blood glucose, blood glucose concentration information can be detected; the best detection site can be located according to photoacoustic imaging, improving the detection speed and accuracy. This technology can quickly locate the detection site and non-invasively detect blood glucose concentration with high precision, and will be one of the best blood glucose detection technologies. Summary of the Invention

[0006] To overcome the deficiencies in the accuracy of existing blood glucose detection, the present invention provides a photoacoustic non-destructive blood glucose localization and detection device based on a backward mode. This device avoids the drawbacks of the specificity of blood glucose at different positions and the drawbacks of blood glucose detection concentration. This device can perform photoacoustic imaging localization and blood glucose concentration detection on blood vessels in human body parts (such as fingers, arms, etc.). It can not only achieve blood vessel localization but also non-destructively detect blood glucose concentration, realizing the accuracy of biomedical detection technology. The reflective objective lens shapes the light, making the entire system a backward structure. On the basis of sufficient beam energy intensity, the micro ultrasonic sensor is placed at the light-shielding position in the exact middle of the light outlet of the reflective objective lens, making the penetration depth of the detected ultrasonic wave deeper, improving the practicality of the device and making the detected blood glucose signal more accurate. This system can detect the blood glucose concentration of the part to be measured, process the blood glucose data, and improve the accuracy of blood glucose detection.

[0007] To achieve the above object, the present invention adopts the following technical solutions:

[0008] A photoacoustic non-destructive blood glucose localization and detection device based on a backward mode, which includes a silica glass slide, a focusing lens, a micro ultrasonic sensor, a reflective objective lens, an optical fiber collimator, a fixture, a pre-signal amplifier, a displacement platform, a positioning and detection unit, a laser, and an optical fiber. The focusing lens, the reflective objective lens, and the optical fiber collimator are clamped by the fixture to form an optical system part, which is located directly below the silica glass slide. The micro ultrasonic sensor is located at the light-shielding position in the exact middle of the light outlet of the reflective objective lens. The data transmitted by the micro ultrasonic sensor is amplified by the pre-signal amplifier and transmitted to the positioning and detection unit for processing. The light source is provided by the laser and is coupled to the optical fiber collimator through the optical fiber.

[0009] In the optical system part, the light source from bottom to top is the optical fiber collimator, the reflective objective lens, and the focusing lens in sequence. The optical fiber collimator collimates the light beam transmitted by the optical fiber. The reflective objective lens shapes the collimated light and transmits and focuses it on both sides of the micro ultrasonic sensor directly below the micro ultrasonic sensor. The focusing lens performs secondary focusing on the light beam and focuses it on the skin surface to be measured directly above the silica glass slide.

[0010] Further, the laser is used to generate a light source to excite photoacoustic signals in blood vessels in the finger.

[0011] Further, the optical fiber is used to transmit the light beam generated by the laser, facilitating the application of the light beam.

[0012] Further, the optical fiber collimator collimates the light beam transmitted by the optical fiber.

[0013] Further, the reflective objective lens is used to adjust the collimated light, so that the parallel light is divided into two beams, left and right, and overlaps and focuses directly above the micro ultrasonic sensor. The adjusted light uniformity is better than 90%, and the diameter of the focal spot is about 20 um. The numerical aperture of the reflective objective lens is 0.5, and the light-shielding surface is 24%.

[0014] Further, the focusing lens is used for secondary focusing of light. The diameter of the focal spot is about 22 um, which improves the system resolution and unit energy density. The focal length of the focusing lens is 1000 mm.

[0015] Further, the fixture is placed on the displacement platform for C-scanning.

[0016] Further, the micro ultrasonic sensor is connected to a preamplifier. The preamplifier is connected to the positioning and detection unit through a data communication line with a BGC connector (Bayonet Nut Connector, hereinafter referred to as BNC line). The size of the micro ultrasonic sensor is 3.5 mm × 1.5 mm.

[0017] Further, the positioning and detection unit processes the photoacoustic signal, locates the blood vessel position, detects the blood glucose concentration, and issues an early warning.

[0018] The present invention also provides a method for using a photoacoustic non-destructive blood glucose positioning and detection system based on the backward mode. The specific method includes the following steps:

[0019] S1: Place the test part of the tested population on the silica glass slide, turn on the power supply, and start the operation of the laser, displacement platform, preamplifier and positioning and detection unit.

[0020] S2: Couple the light beam generated by the laser into the fiber collimator through the optical fiber, and then enter the reflective objective lens for shaping and focusing. The focused light is secondarily focused on the surface of the test part of the human body through the focusing lens.

[0021] S3: The micro ultrasonic sensor transmits the received photoacoustic signal to the preamplifier for amplification.

[0022] S4: The amplified signal is transmitted to the positioning and detection unit for signal processing. In the processing process, according to the amplitude and sound velocity of the signal, and integrating the relevant parameters of the human body part, the intensity of the photoacoustic signal is normalized to locate the blood vessel position and detect the blood glucose concentration.

[0023] S5: The positioning and detection unit controls the displacement platform to move to complete the imaging of the test area and the scanning of the blood glucose signal in the blood vessel.

[0024] S6: The positioning detection unit analyzes the ultrasonic signal intensity and sound velocity of the scanning points, analyzes the tissue characteristics of the scanning points, and extracts the information on the blood vessel positions and blood glucose concentrations in the detection area;

[0025] S7: Perform blood vessel positioning and blood glucose concentration detection based on the information on blood vessel positions and blood glucose concentrations.

[0026] Further, S6 and S7 specifically include: registering the results of blood vessel positioning and blood glucose concentration detection in a database, establishing a blood glucose concentration prediction model for the determined positions, and providing early warnings.

[0027] Further, the positioning detection information includes the information on blood vessel positions and blood glucose concentrations.

[0028] Further, the blood glucose concentration is trained using a convolutional neural network, and a regression prediction method, a combined prediction model, or a BP neural network prediction model is used to perform prediction calculations on the blood glucose concentration.

[0029] Compared with the prior art, the beneficial effects of the present invention are as follows: The present invention combines the photoacoustic blood glucose technology with the artificial intelligence recognition technology, and can perform non-invasive positioning detection of photoacoustic blood glucose; moreover, the present invention combines the two technologies of photoacoustic positioning and non-destructive blood glucose detection, effectively improving the accuracy and precision of blood glucose detection; compared with the traditional method, the reflective objective lens shapes the light, making the entire optical system a backward structure. On the basis of sufficient beam energy intensity, the micro ultrasonic sensor is placed at the light-shielding position of the reflective objective lens, so that the penetration depth of the detected ultrasonic wave is deeper, improving the practicability of the device and making the detected blood glucose signal more accurate. This system can detect the blood glucose concentration of the part to be measured, realize the processing of blood glucose data, and improve the accuracy of blood glucose detection. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] Figure 1 is a schematic structural diagram of the photoacoustic non-destructive blood glucose positioning detection device of the present invention;

[0031] Among them, 1, silica glass slide; 2, focusing lens; 3, micro ultrasonic sensor; 4, reflective objective lens; 5, fiber optic collimator; 6, fixture; 7, pre-signal amplifier; 8, displacement platform; 11, positioning detection unit; 9, laser; 10, optical fiber. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0032] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts shall fall within the protection scope of the present invention.

[0033] Example 1, as Figure 1 shown, a photoacoustic non-destructive blood glucose localization detection device based on the backward mode. The device consists of a silica glass slide 1, a focusing lens 2, a micro ultrasonic sensor 3, a reflective objective lens 4, an optical fiber collimator 5, a fixture 6, a pre-signal amplifier 7, a displacement platform 8, a localization detection unit 11, a laser 9, and an optical fiber 10. The focusing lens 2, the reflective objective lens 4, and the optical fiber collimator 5 are clamped by the fixture 6 to form an optical system part, which is located directly below the silica glass slide 1. The micro ultrasonic sensor 3 is located at the light-shielding position in the middle of the light outlet of the reflective objective lens 4. The data transmitted by the micro ultrasonic sensor 3 is amplified by the pre-signal amplifier 7 and then transmitted to the localization detection unit 11 for processing. The light source is provided by the laser 9 and is coupled to the optical fiber collimator through the optical fiber 10.

[0034] In the optical system part, the light source from bottom to top is the optical fiber collimator 5, the reflective objective lens 4, and the focusing lens 2 in sequence. The optical fiber collimator 5 collimates the light beam transmitted by the optical fiber 10. The reflective objective lens 4 shapes the collimated light and transmits and focuses it on both sides of the micro ultrasonic sensor 3 directly below the micro ultrasonic sensor 3. The focusing lens 2 performs secondary focusing on the light beam and focuses it on the surface of the skin to be measured directly above the silica glass slide 1.

[0035] The laser 9 is used to generate a light source to excite photoacoustic signals in blood vessels in the finger.

[0036] The optical fiber 10 is used to transmit the light beam generated by the laser, facilitating the application of the light beam.

[0037] The optical fiber collimator 5 collimates the light beam transmitted by the optical fiber.

[0038] The reflective objective lens 4 is used to adjust the collimated light, so that the parallel light is divided into two left and right beams and overlaps and focuses directly above the micro ultrasonic sensor 3. The uniformity of the adjusted light is better than 90%, and the diameter of the focal spot is about 20um. The numerical aperture of the reflective objective lens 4 is 0.5, and the light-shielding surface is 24%. The reflective objective lens 4 is preferably LMM-40X-UVV of THORLABS.

[0039] The focusing lens 2 is used for secondary focusing of the light, and the diameter of the focal spot is about 22um, improving the system resolution and the unit energy density. The focal length of the focusing lens 2 is 1000mm. The focusing lens 2 is preferably LA1464 of THORLABS.

[0040] The fixture 6 is placed on the displacement platform 8 for C-scanning.

[0041] The micro ultrasonic sensor 3 is connected to the preamplifier 7; the preamplifier 7 is connected to the positioning and detection unit 11 through a BNC cable; the micro ultrasonic sensor 7 is preferably an ultrasonic probe produced by the Institute of Medical Biology and Engineering, Chinese Academy of Sciences, with a size of 3.5 mm × 1.5 mm.

[0042] Further, the positioning and detection unit 11 processes the photoacoustic signal, locates the blood vessel position, detects the blood glucose concentration, and issues an alarm.

[0043] The present invention also provides a method for using a photoacoustic non-destructive blood glucose positioning and detection system based on the backward mode. The specific method includes the following steps:

[0044] S1: Place the part to be measured of the population to be measured on the silica glass slide 1, turn on the power supply, and start the laser 9, the displacement platform 8, the preamplifier 7, and the positioning and detection unit 11.

[0045] S2: Couple the light beam generated by the laser 9 into the fiber collimator 5 through the optical fiber 10, and then enter the reflective objective lens 4 for shaping and focusing. The focused light is secondarily focused on the surface of the part to be measured of the human body through the focusing lens 2.

[0046] S3: The micro ultrasonic sensor 3 transmits the received photoacoustic signal to the preamplifier 7 for amplification.

[0047] S4: The amplified signal is transmitted to the positioning and detection unit 11 for signal processing. In the processing process, according to the amplitude and sound velocity of the signal, and integrating the relevant parameters of the human body part, the intensity of the photoacoustic signal is normalized, the blood vessel position is located, and the blood glucose concentration is detected.

[0048] S5: The positioning and detection unit 11 controls the displacement platform 8 to move to complete the imaging of the area to be measured and the scanning of the blood glucose signal in the blood vessel.

[0049] S6: The positioning and detection unit 11 analyzes the ultrasonic signal intensity and sound velocity of the scanning points, analyzes the tissue characteristics of the scanning points, and extracts the information of the blood vessel position and blood glucose concentration in the detection area.

[0050] S7: Perform blood vessel positioning and blood glucose concentration detection according to the information of the blood vessel position and blood glucose concentration.

[0051] The specific steps of S6 and S7 include: registering the results of blood vessel positioning and blood glucose concentration detection in a database, establishing a blood glucose concentration prediction model for the determined position, and providing an alarm.

[0052] The positioning and detection information includes the information of the blood vessel position and the blood glucose concentration.

[0053] The blood glucose concentration is trained by a convolutional neural network, and a regression prediction method, a combined prediction model or a BP neural network prediction model is used to predict and calculate the blood glucose concentration.

[0054] The present invention is an optoacoustic imaging localization integrated with ultrasonic sound velocity for blood glucose concentration detection, which can perform non-invasive localization detection of blood glucose in human body parts, and integrate two technologies of optoacoustic imaging localization and non-invasive blood glucose detection, effectively improving the accuracy and precision of blood glucose detection; the present invention adopts a backward mode to shape the light, making the whole optical system a backward structure. On the basis of sufficient beam energy intensity, a micro ultrasonic sensor is placed at the light-shielding position of the reflective objective lens, improving the practicability of the device and the accuracy of the biomedical detection algorithm, enabling it to be widely applied in fields such as biometric identification.

[0055] As described above by way of example with reference to the drawings, the optoacoustic non-invasive blood glucose detection device based on the backward mode proposed according to the present invention. However, those skilled in the art should understand that various improvements can be made to the above-mentioned optoacoustic non-invasive blood glucose detection device proposed by the present invention without departing from the content of the present invention. Therefore, the protection scope of the present invention should be determined by the content of the appended claims.

Claims

1. A method for photoacoustic non-destructive blood glucose localization detection based on the backward mode, characterized in that , a photoacoustic non-destructive blood glucose localization detection device based on the backward mode is used to perform the following steps: Step S1: Place the test site of the population to be tested on the silica glass slide, start the power supply, and turn on the laser, displacement platform, pre-signal amplifier and localization detection unit to work; Step S2: Couple the light beam generated by the laser into the fiber collimator through the optical fiber, and then enter the reflective objective lens for shaping and focusing. The focused light passes through the focusing lens and is secondarily focused on the surface of the test site of the human body; Step S3: The micro ultrasonic sensor transmits the received photoacoustic signal to the pre-signal amplifier for amplification; Step S4: The amplified signal is transmitted to the localization detection unit for signal processing. In the processing process, according to the amplitude and sound velocity of the signal, combined with the relevant parameters of the human body part, the intensity of the photoacoustic signal is normalized to locate the blood vessel position and detect the blood glucose concentration; Step S5: The localization detection unit controls the displacement platform to move to complete the imaging of the test area and the scanning of the blood glucose signal in the blood vessel; Step S6: The localization detection unit analyzes the ultrasonic signal intensity and sound velocity of the scanning point, analyzes the tissue characteristics of the scanning point, and extracts the localization detection information of the detection area, where the localization detection information includes the information of the blood vessel position and blood glucose concentration; Step S7: Perform blood vessel localization and blood glucose concentration detection according to the localization detection information; wherein the device includes a silica glass slide, a focusing lens, a micro ultrasonic sensor, a reflective objective lens, a fiber collimator, a fixture, a pre-signal amplifier, a displacement platform, a localization detection unit, a laser, and an optical fiber; The focusing lens, reflective objective lens, and fiber collimator are clamped by the fixture to form the optical system part, which is located directly below the silica glass slide; The focusing lens is used for the secondary focusing of light, and the diameter of the focal spot is 22um, which improves the system resolution and unit energy density; The micro ultrasonic sensor is located at the light-shielding position in the middle of the light outlet of the reflective objective lens, and the micro ultrasonic sensor is connected to the pre-signal amplifier; The reflective objective lens is used to adjust the collimated light, so that the parallel light is divided into two beams on the left and right and overlaps and focuses directly above the micro ultrasonic sensor. The uniformity of the adjusted light is better than 90%, and the diameter of the focal spot is 20um; The fiber collimator is used to collimate the light beam transmitted by the optical fiber; The fixture is placed on the displacement platform for C-scanning; The pre-signal amplifier is connected to the localization detection unit through a BNC cable. The data transmitted by the micro ultrasonic sensor is amplified by the pre-signal amplifier and then transmitted to the localization detection unit for processing; The localization detection unit processes the photoacoustic signal, locates the blood vessel position, detects the blood glucose concentration, and gives an alarm; The laser is used to generate a light source, and the light source is coupled to the fiber collimator through the optical fiber; to excite the blood vessel to generate a photoacoustic signal; The optical fiber is used to transmit the light beam generated by the laser to facilitate the application of the light beam.

2. The method for photoacoustic non-destructive blood glucose localization detection based on the backward mode according to claim 1, characterized in that: In the optical system part, the light source from bottom to top is a fiber collimator, a reflective objective lens, and a focusing lens in sequence; the fiber collimator collimates the light transmitted by the optical fiber; the reflective objective lens shapes the collimated light and transmits it to both sides of the micro ultrasonic sensor and focuses it directly below the micro ultrasonic sensor; the focusing lens performs secondary focusing on the light beam and focuses it on the skin surface to be measured directly above the silica glass slide.

3. A non-invasive photoacoustic blood glucose localization detection method based on the backward mode according to claim 1 or 2, characterized in that: the focal length of the focusing lens is 1000 mm.

4. A non-invasive photoacoustic blood glucose localization detection method based on the backward mode according to claim 1 or 2, characterized in that: the size of the micro ultrasonic sensor is 3.5 mm × 1.5 mm.

5. A non-invasive photoacoustic blood glucose localization detection method based on the backward mode according to claim 1 or 2, characterized in that: the numerical aperture of the reflective objective lens is 0.5 and the light-shielding surface is 24%.

6. A non-invasive photoacoustic blood glucose localization detection method based on the backward mode according to claim 1, characterized in that: in step S6 and step S7, it includes registering the results of blood vessel localization and blood glucose concentration detection into a database, establishing a blood glucose concentration prediction model for the determined position, and providing an early warning.

7. A non-invasive photoacoustic blood glucose localization detection method based on the backward mode according to claim 6, characterized in that: the blood glucose concentration is trained by a convolutional neural network, and a regression prediction method, a combined prediction model or a BP neural network prediction model is used to predict and calculate the blood glucose concentration.

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