Blood flow velocity measuring device and method

Abstract

The embodiment of the invention discloses a blood flow velocity measuring device and method.The blood flow velocity measuring device comprises an input unit, a measuring unit, an analysis unit and a control unit, the input unit, the analysis unit and the measuring unit are connected with the control unit, the input unit is further connected with the measuring unit, the measuring unit is further connected with the analysis unit, and the analysis unit is connected with the control unit. The signal processing unit is used for receiving the electric signal sent by the ultrasonic probe, analyzing the electric signal to obtain a digital signal and sending the digital signal to the control unit; and the control unit is used for sending a measurement instruction to the input unit, receiving the digital signal sent by the analysis unit, and analyzing and processing the digital signal to obtain a blood flow velocity result. According to the blood flow velocity measurement device, through reasonable unit design, the input unit, the measurement unit, the analysis unit, the control unit and the like are integrated, so that the whole structure is easier to realize miniaturization.

Description

Technical Field

[0001] The present application relates to the field of information processing technology, and in particular to a blood flow velocity measurement device and method. Background Art

[0002] Accurate measurement of blood flow velocity is of great significance for evaluating vascular health and diagnosing related diseases. In the existing technology, photoacoustic imaging technology, as an emerging non-destructive testing method, combines the advantages of optics and ultrasound and can provide internal information of tissues at a higher resolution. However, most existing photoacoustic imaging devices are bulky, complex in structure, and not portable, which limits their practical application in clinical settings.

[0003] Therefore, how to ensure the portability of the blood flow velocity measuring device and improve the applicability of the blood flow velocity measuring device is an urgent problem to be solved. Summary of the invention

[0004] In view of this, a blood flow velocity measurement device and method provided in an embodiment of the present application can miniaturize the device structure and improve the applicability of the blood flow velocity measurement device. A blood flow velocity measurement device provided in an embodiment of the present application is implemented as follows:

[0005] A blood flow velocity measuring device provided in an embodiment of the present application includes:

[0006] An input unit, a measuring unit, an analyzing unit and a control unit, wherein the input unit, the analyzing unit and the measuring unit are respectively connected to the control unit, the input unit is also connected to the measuring unit, and the measuring unit is also connected to the analyzing unit, wherein:

[0007] The measuring unit comprises an objective lens, a first condensing lens, a first right-angle prism, a second right-angle prism, an acoustic lens, a hexagonal prism and an ultrasonic probe, wherein:

[0008] The objective lens is used to receive the optical signal input by the input unit, perform convergence processing on the optical signal, and send the optical signal to the first condensing lens after the size of the processed optical signal meets the preset size requirement;

[0009] The first condensing lens is used to receive the optical signal sent by the objective lens, and after condensing the optical signal, send the optical signal to the first right-angle prism;

[0010] The first right-angle prism is used to adjust the sending direction of the optical signal and send the optical signal to the hexagonal prism;

[0011] The second right-angle prism is used to adjust the sending direction of the light signal refracted after the light signal is adjusted in the sending direction by the first right-angle prism, and send the light signal to the hexagonal prism;

[0012] The hexagonal prism is used to adjust the angles of the light signals sent by the first right-angle prism and the second right-angle prism so that the light signals are irradiated onto the sample, receive the acoustic wave signals generated by the sample after being irradiated by the light signals, adjust the sending direction of the acoustic wave signals, and send the acoustic wave signals to the acoustic lens;

[0013] The acoustic lens is used to focus the acoustic wave signal and send the acoustic wave signal to the ultrasonic probe via the first right-angle prism and the second right-angle prism;

[0014] The ultrasonic probe is used to convert the sound wave signal into an electrical signal and send the electrical signal to the analysis unit;

[0015] The input unit is used to receive the measurement instruction issued by the control unit, generate an optical signal, and send the optical signal to the objective lens;

[0016] The analysis unit is used to receive the electrical signal sent by the ultrasound probe, analyze and process the electrical signal to obtain a digital signal, and send the digital signal to the control unit;

[0017] The control unit is used to send a measurement instruction to the input unit, receive a digital signal sent by the analysis unit, analyze and process the digital signal, and obtain a blood flow velocity result.

[0018] In some embodiments, the input unit includes a laser, an aperture, a second condensing lens, a pinhole, a diffraction lens, a fiber coupler, and an optical fiber, wherein:

[0019] The laser is used to generate a light signal after receiving a measurement instruction sent by the control unit, and send the light signal to the aperture;

[0020] The aperture is used to receive the optical signal sent by the laser, adjust the intensity of the optical signal, and send the adjusted optical signal to the second condensing lens;

[0021] The second condensing lens is used to receive the light signal sent by the aperture, perform condensing processing on the light signal, and send the light signal to the pinhole;

[0022] The pinhole is used to receive the optical signal sent by the second condensing lens, filter the optical signal to obtain a filtered optical signal, and send the optical signal to the astigmatism lens;

[0023] The astigmatism lens is used to receive the optical signal sent by the pinhole, perform divergent light convergence processing on the optical signal, and send the optical signal after the divergent light convergence processing to the optical fiber coupler;

[0024] The optical fiber coupler receives the optical signal sent by the light-scattering lens, converts the optical signal from a free-space optical transmission mode to an optical fiber transmission mode, and sends the optical signal in the optical fiber transmission mode to the optical fiber;

[0025] The optical fiber is used to receive the optical signal sent by the optical fiber coupler and transmit the optical signal to the objective lens.

[0026] In some embodiments, the analysis unit includes a low noise amplifier and a signal acquisition card, wherein:

[0027] The low noise amplifier is used to receive the electrical signal sent by the ultrasonic probe, amplify the electrical signal, and then send it to the signal acquisition card;

[0028] The signal acquisition card is used to receive the electrical signal sent by the low noise amplifier, convert the electrical signal into a digital signal, and then send it to the control unit.

[0029] In some embodiments, the control unit includes a function generator and a processing module, wherein:

[0030] The function generator is used to receive the control instruction sent by the processing module, and control the hexagonal prism to rotate according to the control instruction;

[0031] The processing module is used to send control instructions to the function generator, send measurement instructions to the laser, receive digital signals sent by the signal acquisition card, and analyze and process the digital signals to obtain blood flow velocity results.

[0032] In some embodiments, the laser is a pulsed laser.

[0033] In some embodiments, the measuring unit is of sealed design.

[0034] In some embodiments, the internal filling liquid of the measuring unit is pure water.

[0035] In some embodiments, the inner coating of the first right angle prism is a high reflective coating.

[0036] In some embodiments, the ultrasound probe is fixed on the second rectangular prism.

[0037] A blood flow velocity measurement method provided in an embodiment of the present application includes:

[0038] The control input unit sends a first optical signal and a second optical signal at a preset time interval, and the intensity of the first optical signal is consistent with the intensity of the second optical signal;

[0039] Obtaining a first electrical signal according to the first optical signal, and obtaining a second electrical signal according to the second optical signal;

[0040] Obtaining the strength value of the first electrical signal, and obtaining the Greeneson parameter of the first electrical signal according to formula (1);

[0041] p1=Γ1(T1)η h μ a F1(1)

[0042] Wherein, in formula (1), p1 is the intensity value of the first electrical signal, Γ1 is the Grüneisen parameter of the first electrical signal, T1 is the sample temperature value corresponding to the first electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, F1 is the intensity value of the first light signal;

[0043] Obtaining the strength value of the second electrical signal, and obtaining the Greeneson parameter of the second electrical signal according to formula (2);

[0044] p2=Γ2(T2)η h μ a F2(2)

[0045] Wherein, in formula (2), p2 is the intensity value of the second electrical signal, Γ2 is the Grüneisen parameter of the second electrical signal, T2 is the sample temperature value corresponding to the second electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, F2 is the intensity value of the second light signal;

[0046] According to the Grüneisen parameter of the first electrical signal and the Grüneisen parameter of the second electrical signal, a blood flow velocity result is obtained by formula (3);

[0047]

[0048] Wherein, in formula (3), ΔΓ is the difference between the Grüneisen parameter of the first electrical signal and the Grüneisen parameter of the second electrical signal, μ a is the absorption coefficient, F1 is the intensity of the first light signal, δt is the temperature difference between the sample temperature value corresponding to the first electrical signal and the sample temperature value corresponding to the second electrical signal, a, k1, k2 and e are all constants, and v is the blood flow velocity result.

[0049] A blood flow velocity measurement device and method provided in an embodiment of the present application includes an input unit, a measuring unit, an analyzing unit and a control unit. The input unit, the analyzing unit and the measuring unit are respectively connected to the control unit. The input unit is also connected to the measuring unit, and the measuring unit is also connected to the analyzing unit. The analyzing unit is used to receive the electrical signal sent by the ultrasonic probe, analyze and process the electrical signal to obtain a digital signal, and send the digital signal to the control unit; the control unit is used to send a measurement instruction to the input unit, receive the digital signal sent by the analyzing unit, analyze and process the digital signal, and obtain the blood flow velocity result. In this way, the blood flow velocity measurement device integrates the input unit, the measuring unit, the analyzing unit and the control unit through reasonable unit design, so that the overall structure is easier to achieve miniaturization, solving the technical problems raised in the background technology. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the embodiments of the present application or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0051] Figure 1 A schematic diagram of the structure of a blood flow velocity measurement device provided in an embodiment of the present application;

[0052] Figure 2 A schematic diagram of the structure of another blood flow velocity measurement device provided in an embodiment of the present application;

[0053] Figure 3 A schematic diagram of the structure of another blood flow velocity measurement device provided in an embodiment of the present application;

[0054] Figure 4 A schematic diagram of the structure of another blood flow velocity measurement device provided in an embodiment of the present application;

[0055] Figure 5 A flow chart of a blood flow velocity measurement method provided in an embodiment of the present application. DETAILED DESCRIPTION

[0056] In order to make the purpose, technical scheme and advantages of the embodiments of the present application clearer, the specific technical scheme of the present application will be further described in detail below in conjunction with the drawings in the embodiments of the present application. The following embodiments are used to illustrate the present application, but are not used to limit the scope of the present application.

[0057] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as those commonly understood by those skilled in the art to which this application belongs. The terms used herein are only for the purpose of describing the embodiments of this application and are not intended to limit this application.

[0058] In the following description, reference is made to “some embodiments”, which describe a subset of all possible embodiments, but it will be understood that “some embodiments” may be the same subset or different subsets of all possible embodiments and may be combined with each other without conflict.

[0059] It should be pointed out that the terms "first\second\third" involved in the embodiments of the present application are used to distinguish similar or different objects, and do not represent a specific ordering of the objects. It can be understood that "first\second\third" can be interchanged in a specific order or sequence where permitted, so that the embodiments of the present application described here can be implemented in an order other than that illustrated or described here.

[0060] Figure 1 It is a structural schematic diagram of a blood flow rate measuring device provided in an embodiment of the present application, including an input unit, a measuring unit, an analyzing unit and a control unit, wherein the input unit, the analyzing unit and the measuring unit are respectively connected to the control unit, the input unit is also connected to the measuring unit, and the measuring unit is also connected to the analyzing unit.

[0061] The measuring unit comprises an objective lens 1, a first condensing lens 2, a first right-angle prism 3, a second right-angle prism 4, an acoustic lens 5, a hexagonal prism 6 and an ultrasonic probe 7, wherein:

[0062] The objective lens 1 is used to receive the optical signal 8 input by the input unit, perform convergence processing on the optical signal 8, and send the optical signal 8 to the first condensing lens 2 after the size of the processed optical signal 8 meets the preset size requirement.

[0063] In the embodiment of the present application, the objective lens 1 focuses the optical signal 8 from the input unit to the subsequent optical element.

[0064] The present application uses a single lens to complete the focusing. The focusing of the optical signal 8 can be precisely controlled by designing the curvature and focal length of the objective lens 1 .

[0065] By selecting commonly used optical glass materials, good light transmittance and refractive index can be guaranteed, thereby ensuring the focusing effect.

[0066] The first condensing lens 2 is used for receiving the optical signal 8 sent by the objective lens 1 , and after condensing the optical signal 8 , sends the optical signal 8 to the first right-angle prism 3 .

[0067] In the embodiment of the present application, the first condensing lens 2 is used to further focus the optical signal 8 and provide a suitable incident angle for the subsequent right-angle prism and hexagonal prism 6 .

[0068] The lens material can be selected from optical glass with a high refractive index to optimize its focusing performance. The focal length design of the lens should ensure that the diameter of the focused beam meets the experimental requirements.

[0069] The propagation direction of the light beam can be precisely controlled by adjusting the tilt angle of the lens, ensuring that the angle adjustment of subsequent optical elements can proceed smoothly.

[0070] The first right angle prism 3 is used to adjust the sending direction of the optical signal 8 and send the optical signal 8 to the hexagonal prism 6. The second right angle prism 4 is used to adjust the sending direction of the optical signal 8 refracted by the first right angle prism 3 and send the optical signal 8 to the hexagonal prism 6.

[0071] In the embodiment of the present application, the main function of the prism is to accurately adjust the angle of the light so as to correctly transmit the optical signal 8 to the hexagonal prism 6.

[0072] The right-angle prism may be made of optical glass with a high refractive index to ensure that the optical signal 8 has minimal loss during the refraction process and is accurately reflected.

[0073] The precise positioning and angle adjustment of the prism are very critical. The present application can finely adjust the position of the prism through a fine-tuning knob or an electric drive mechanism to achieve precise control of the light beam direction.

[0074] The hexagonal prism 6 is used to adjust the angle of the light signal 8 sent by the first right-angle prism 3 and the second right-angle prism 4 so that the light signal 8 is irradiated onto the sample, and to receive the acoustic wave signal 9 generated by the sample after being irradiated by the light signal 8, and to adjust the sending direction of the acoustic wave signal 9 and send the acoustic wave signal 9 to the acoustic lens 5;

[0075] In the embodiment of the present application, the main task of the hexagonal prism 6 is to further guide the light signal 8 adjusted by two refractions to the sample and reflect the returned sound wave signal 9.

[0076] The geometric shape and optical properties of the hexagonal prism 6 need to be accurately calculated according to the properties of the light source and the measurement target. The face angle and size of the prism directly affect the reflection angle of the light signal 8.

[0077] The surface of the hexagonal prism 6 may be coated with a reflective or anti-reflective coating to reduce the loss of the optical signal 8 and improve the reflection efficiency.

[0078] The acoustic lens 5 is used to focus the acoustic wave signal 9 and send the acoustic wave signal 9 to the ultrasonic probe 7 via the first right-angle prism 3 and the second right-angle prism 4 .

[0079] In the embodiment of the present application, the acoustic lens 5 is used to focus the acoustic wave signal 9 reflected from the blood sample and ensure the propagation direction and intensity of the signal.

[0080] The acoustic lens 5 of the present application is made of a material with high acoustic transmittance, such as a polymer or a hydrogel, etc. The structural design of the lens needs to ensure that the sound waves can be effectively focused to avoid signal attenuation.

[0081] The acoustic lens 5 concentrates the scattered acoustic wave signal 9 in a specific area through its curved or concave design, thereby improving the detection accuracy.

[0082] The ultrasonic probe 7 is used to convert the sound wave signal 9 into an electrical signal and send the electrical signal to the analysis unit.

[0083] In the embodiment of the present application, the ultrasonic probe 7 converts the sound wave signal 9 into an electrical signal, providing the input required for subsequent signal processing.

[0084] The piezoelectric element in the ultrasonic probe 7 is its core component, which can convert the sound wave signal 9 into an electrical signal. Common piezoelectric materials include lead titanate and the like.

[0085] The working frequency of the ultrasonic probe 7 determines its sensitivity to different flow velocity ranges. Generally speaking, a high-frequency probe is suitable for more precise blood flow velocity measurement, while a low-frequency probe is suitable for detecting deeper tissues.

[0086] As an example, the measuring cell is of sealed design.

[0087] Specifically, the structure of the measuring unit is designed as a completely closed environment to prevent external environmental factors (such as dust, moisture, temperature fluctuations, etc.) from interfering with or affecting the measuring process. The measuring unit can adopt an integrated sealed housing to prevent external substances from entering. Inside the measuring unit, important components such as the objective lens 1, the optical lens, and the ultrasonic probe 7 usually need to work in a clean and stable environment. The sealing design can reduce the influence of external light and gas to ensure the accuracy of the measurement results.

[0088] The input unit is used to receive the measurement instruction sent by the control unit, generate the optical signal 8, and send the optical signal 8 to the objective lens 1.

[0089] The sealing design of the present application example can effectively prevent the external environment (such as dust, moisture, pollutants, etc.) from affecting the optical and electronic components inside the measuring unit, ensuring the long-term stable operation of the device. Through sealing, the stability of the internal environment of the measuring unit is improved, external interference is avoided, and the propagation of the optical signal and the acoustic signal 9 is ensured to be unaffected by external factors, thereby improving the accuracy of blood flow velocity measurement.

[0090] As an example, the internal filling liquid of the measuring cell is pure water.

[0091] Specifically, pure water is filled inside the measuring unit to provide a stable and transparent medium. Pure water has good sound wave conductivity and does not introduce other impurities, so it can reduce noise interference and improve the transmission efficiency of sound waves.

[0092] The purpose of filling with pure water is to ensure that the optical signal 8 and the acoustic wave signal 9 can be transmitted efficiently and stably during the measurement process.

[0093] The example of this application can effectively improve the performance, stability and service life of the entire blood flow rate measurement system by using pure water as the internal filling liquid of the measurement unit.

[0094] As an example, the inner coating of the first right angle prism 3 in the measuring unit is a high reflection coating.

[0095] Specifically, the inner coating of the first right-angle prism 3 is a high-reflection coating. The function of this coating is to enhance the reflection efficiency of the light signal 8, so that the light signal 8 can maintain its intensity to the greatest extent during the reflection and refraction process inside the prism, reduce the attenuation of the light signal 8, and ensure that the signal can be smoothly transmitted to the subsequent optical elements and irradiated onto the sample.

[0096] The example of the present application can significantly improve the reflection efficiency of the light signal 8 inside the prism through a high-reflection coating, reduce the loss of the light signal 8, thereby ensuring that more light signal 8 can be effectively transmitted to the sample or other optical elements, and improve the overall performance and sensitivity of the measurement system.

[0097] As an example, the ultrasonic probe 7 in the measuring unit is fixed on the second right-angle prism 4 .

[0098] Specifically, the ultrasonic probe 7 in the measuring unit is fixed on the second right-angle prism 4 , and the second right-angle prism 4 not only serves as a refraction element of the optical signal 8 , but also serves as a position component for supporting the ultrasonic probe 7 .

[0099] When the ultrasonic probe 7 is fixed on the second rectangular prism 4, the ultrasonic probe 7 may be connected to the second rectangular prism 4 by a mechanical fixing method (such as screws or bonding). In this way, the second rectangular prism 4 not only controls the propagation direction of the optical signal 8, but also provides a stable installation position for the ultrasonic probe 7, ensuring the accurate transmission of the ultrasonic signal during the measurement process.

[0100] The present application example can ensure that the ultrasonic probe 7 is in a stable position during the measurement process by fixing the ultrasonic probe 7 on the second right-angle prism 4, thereby reducing errors caused by device vibration or external factors. The fixed design can effectively prevent the position of the ultrasonic probe 7 from shifting, ensuring that the area detected by it is consistent each time it is measured, thereby improving the measurement accuracy.

[0101] In the embodiment of the present application, the function of the input unit is to generate a stable and accurate light signal 8 and control the emission direction and intensity of the light signal 8 .

[0102] Lasers or LEDs with wavelengths in the near-infrared or visible range are usually selected because they can penetrate skin tissue and interact with red blood cells in the blood. A common choice is a light source with a wavelength of 650-900nm.

[0103] By modulating the light source (eg, modulating the output frequency or intensity of a laser), the input unit can make the optical signal 8 have a specific frequency or time characteristic, which is convenient for subsequent signal processing.

[0104] The analyzing unit is used to receive the electrical signal sent by the ultrasonic probe 7, analyze and process the electrical signal to obtain a digital signal, and send the digital signal to the control unit.

[0105] In the embodiment of the present application, the analysis unit is used to convert the electrical signal into a digital signal, filter out noise, and enhance the signal-to-noise ratio of the signal. The analysis unit needs to be able to process the transmission signal in real time to ensure timely feedback of the blood flow rate data.

[0106] The control unit is used to send a measurement instruction to the input unit, receive the digital signal sent by the analysis unit, analyze and process the digital signal, and obtain the blood flow velocity result.

[0107] The control unit is responsible for coordinating the work of each part in the entire device, including issuing measurement instructions, receiving processing results, and monitoring the measurement process.

[0108] The control unit may adopt an embedded processor or microcontroller (such as ARM, Raspberry Pi, etc.) or a computer to ensure the normal operation of data processing, storage and display functions.

[0109] The control unit may be equipped with a graphical user interface (GUI) that allows the user to view real-time blood flow rate data and make necessary operation settings.

[0110] The embodiment of the present application can accurately focus and adjust the transmission path of light waves and sound waves by using multiple optical elements and acoustic elements to ensure the measurement accuracy of blood flow rate. The stability and accuracy of the signal are improved by multiple conversions and processing of optical and acoustic signals. The reasonable combination and compact integration of various optical elements and acoustic elements enable the device to achieve a good balance between volume and performance. It can achieve multifunctional operation in a smaller volume, improving convenience and application range.

[0111] In the above Figure 1 Based on this, the present application also provides a schematic diagram of the structure of a blood flow velocity measurement device, such as Figure 2 As shown, the input unit includes a laser 10, an aperture 11, a second condenser lens 12, a pinhole 13, a diffuser lens 14, a fiber coupler 15 and an optical fiber 18, wherein:

[0112] The laser 10 is used to generate a light signal 8 after receiving a measurement instruction sent by the control unit, and send the light signal 8 to the aperture 11.

[0113] In the embodiment of the present application, after receiving the measurement instruction issued by the control unit, the laser 10 starts to generate the optical signal 8. The output optical signal 8 of the laser 10 is usually a monochromatic laser beam with strong focusing ability.

[0114] As an example, a pulsed laser is selected. A pulsed laser emits short-duration, high-intensity laser pulses rather than a continuous laser beam. By means of laser pulses, a high-energy optical signal can be generated in a short time. The pulsed laser can provide precise optical pulses, which facilitates the measurement of blood flow velocity through the photoacoustic effect. Since the time scale of the pulse is short, it can effectively reduce the interference caused by the interaction between light and tissue and blood, thereby obtaining a more accurate measurement result.

[0115] The blood flow rate measurement device of the present application example can improve the measurement accuracy, response speed and sensitivity by using a pulsed laser, thereby making the measurement result more accurate and reliable, and suitable for more complex or sophisticated blood flow rate analysis.

[0116] The aperture 11 is used to receive the optical signal 8 sent by the laser 10 , adjust the intensity of the optical signal 8 , and send the adjusted optical signal 8 to the second condensing lens 12 .

[0117] In the embodiment of the present application, the optical signal 8 emitted by the laser 10 enters the aperture 11. The aperture 11 is used to adjust the intensity of the optical signal 8 (i.e., adjust the brightness of the light) to prevent the optical signal 8 from being too strong or too weak to affect the operation of subsequent optical elements. The adjusted optical signal 8 is transmitted to the second focusing lens 12.

[0118] The second condensing lens 12 is used for receiving the optical signal 8 sent by the aperture 11 , focusing the optical signal 8 , and sending the optical signal 8 to the pinhole 13 .

[0119] In the embodiment of the present application, the second condenser lens 12 further focuses the light signal 8 after being adjusted by the aperture 11. After passing through the lens, the light signal 8 becomes more concentrated and forms a light beam suitable for the subsequent optical path. The focused light signal 8 is transmitted to the pinhole 13.

[0120] The pinhole 13 is used to receive the optical signal 8 sent by the second condensing lens 12 , filter the optical signal 8 to obtain the filtered optical signal 8 , and send the optical signal 8 to the diffusing lens 14 .

[0121] In the embodiment of the present application, the pinhole 13 is located in the optical path to filter out some unnecessary stray light or unsatisfactory optical signals 8. The pinhole 13 will filter out the light beam that meets the requirements, and the optical signal 8 that is allowed to pass through will continue to be transmitted downward. The optical signal 8 after passing through the pinhole 13 will be transmitted to the astigmatism lens 14.

[0122] The astigmatism lens 14 is used to receive the optical signal 8 sent by the pinhole 13, perform divergent light convergence processing on the optical signal 8, and send the optical signal 8 after the divergent light convergence processing to the optical fiber coupler 15.

[0123] In the embodiment of the present application, the light-scattering lens 14 properly scatters or diverges the light beam passing through the pinhole 13 to ensure that the light beam can propagate at a proper angle or shape to adapt to the receiving conditions of the subsequent optical fiber coupler 15. After passing through the light-scattering lens 14, the light beam becomes more suitable for transmission through the optical fiber 18.

[0124] The optical fiber coupler 15 receives the optical signal 8 sent by the astigmatism lens 14 , converts the optical signal 8 from the free space optical transmission mode to the optical fiber 18 transmission mode, and sends the optical signal 8 in the optical fiber 18 transmission mode to the optical fiber 18 .

[0125] In the embodiment of the present application, the fiber coupler 15 is responsible for converting the optical signal 8 adjusted by the astigmatism lens 14 from the free space transmission mode to the optical fiber 18 transmission mode. The fiber coupler 15 can introduce the optical signal 8 into the optical fiber 18 through a physical structure or an optical element, thereby achieving the guidance and transmission of the optical signal 8.

[0126] The optical fiber 18 is used to receive the optical signal 8 sent by the optical fiber coupler 15 and transmit the optical signal 8 to the objective lens 1 .

[0127] In the embodiment of the present application, the optical fiber 18 receives the optical signal 8 from the optical fiber coupler 15 and efficiently transmits it to the objective lens 1 of the measurement unit. The main function of the optical fiber 18 is to minimize the loss of the optical signal 8 during the transmission of the signal from the input unit to the objective lens 1.

[0128] The embodiment of the present application can accurately control and adjust the intensity and focusing degree of the optical signal 8 through the coordinated work of the above series of optical elements, ensuring that the optical signal 8 entering the objective lens 1 has suitable optical properties. The quality and stability of the optical signal 8 are improved, thereby improving the accuracy of the measurement results. In addition, the application of the optical fiber 18 reduces the dependence on complex optical path alignment, making the overall system more reliable and easy to maintain.

[0129] In the above Figure 1 Based on this, the present application also provides a schematic diagram of the structure of a blood flow velocity measurement device, such as Figure 3 As shown, the analysis unit includes a low noise amplifier 17 and a signal acquisition card 16, wherein:

[0130] The low noise amplifier 17 is used to receive the electrical signal sent by the ultrasonic probe 7 , amplify the electrical signal, and then send it to the signal acquisition card 16 .

[0131] In the embodiment of the present application, the low noise amplifier 17 is used to amplify the weak electrical signal received by the ultrasound probe 7, while suppressing noise to ensure the clarity and quality of the signal.

[0132] The input end of the low noise amplifier 17 is connected to the ultrasonic probe 7. The ultrasonic probe 7 converts the acoustic wave signal 9 into an electrical signal, and the gain of the amplifier can be adjusted by the control unit so that an appropriate gain can be selected according to the required signal strength. For example, during the blood flow velocity measurement process, the gain may need to be adjusted to optimize the signal strength and prevent signal distortion caused by over-amplification.

[0133] The low noise amplifier 17 uses a low noise amplifier circuit (such as a high quality operational amplifier) ​​to minimize the interference of external noise sources and maintain the clarity of the signal. In order to reduce noise, appropriate power supply filters and shielding measures are usually used.

[0134] The amplified electrical signal is output to the input end of the signal acquisition card 16. At this stage, the electrical signal has been amplified enough to be further digitally processed.

[0135] The signal acquisition card 16 is used to receive the electrical signal sent by the low noise amplifier 17, convert the electrical signal into a digital signal, and then send it to the control unit.

[0136] In the embodiment of the present application, the signal acquisition card 16 is used to convert the analog electrical signal from the low noise amplifier 17 into a digital signal and send it to the control unit.

[0137] One of the core components of the signal acquisition card 16 is an analog-to-digital converter. The analog-to-digital converter converts the analog signal into a digital signal for subsequent processing. The present application uses a high-resolution digital-to-analog converter (e.g., 12-bit or 16-bit) to ensure the signal accuracy during the blood flow velocity measurement process.

[0138] The sampling rate determines the accuracy and real-time performance of signal acquisition. For blood flow measurement, signal changes need to be captured quickly, so the sampling rate can be set higher. The choice of sampling rate depends on the frequency range and accuracy requirements of the measurement.

[0139] After analog-to-digital conversion, the digital signal is transmitted to the control unit through an appropriate interface (such as USB, PCIe, etc.).

[0140] The embodiment of the present application can greatly improve the signal processing capability of the measuring device through the design of the low noise amplifier 17 and the signal acquisition card 16, ensuring that the system can measure the blood flow velocity more accurately and stably.

[0141] In the above Figure 2 and Figure 3 Based on this, the present application also provides a schematic diagram of the structure of a blood flow velocity measurement device, such as Figure 4 As shown, the control unit includes a function generator 20 and a processing module 19, wherein:

[0142] The function generator 20 is used to receive the control instruction sent by the processing module 19, and control the hexagonal prism 6 to rotate according to the control instruction.

[0143] In the embodiment of the present application, the function generator 20 is one of the core components of the control unit, responsible for generating and outputting precise control signals. These signals are used to adjust the working parameters of other devices to ensure that the optical path and the acoustic wave path can work in a predetermined manner.

[0144] The function generator 20 receives control instructions from the processing module 19 , generates periodic signals (such as sine waves, square waves, triangle waves, etc.), and transmits these signals to the rotation control motor of the hexagonal prism 6 .

[0145] The rotation of the hexagonal prism 6 is precisely adjusted by controlling the signal generated by the function generator 20. By changing the rotation angle of the hexagonal prism 6, the function generator 20 can affect the propagation direction of the optical signal 8 or the acoustic signal 9. The rotation angle of the hexagonal prism 6 is usually adjusted by controlling the frequency and amplitude of the signal.

[0146] The processing module 19 is used to send control instructions to the function generator 20, send measurement instructions to the laser 10, and receive digital signals sent by the signal acquisition card 16, and analyze and process the digital signals to obtain blood flow velocity results.

[0147] In the embodiment of the present application, the processing module 19 is responsible for processing the collected data and analyzing it. The system workflow is controlled by interacting with other components. The processing module 19 sends instructions to the laser 10 and other devices through a communication interface (such as a serial port, a parallel port, or a higher-level bus interface) to control the emission of the optical signal 8 and the signal path adjustment during collection.

[0148] The processing module 19 receives digital signals from the signal acquisition card 16, which are converted from electrical signals amplified by the low noise amplifier 17. The signal acquisition card 16 performs analog-to-digital conversion on these analog signals and outputs digital signals.

[0149] The digital signal received by the processing module 19 is processed by a built-in algorithm, and the blood flow rate is finally calculated.

[0150] The processing module 19 feeds back the finally calculated blood flow rate to the user through a display screen, a console or other output devices. The user can view the real-time blood flow rate data on the screen.

[0151] The embodiment of the present application makes the optical system and the ultrasonic system work more coordinated through the design of the control unit, optimizing the overall measurement process. The application of the function generator 20 allows the optical system to be flexibly adjusted according to needs, ensuring adaptability under different measurement conditions, and the processing module 19 efficiently performs data processing and analysis.

[0152] The present application also provides a blood flow velocity measurement method. Figure 5 As shown, it includes steps 501 to 505:

[0153] Step 501: Control the input unit to send a first optical signal and a second optical signal at a preset time interval, and the intensity of the first optical signal is consistent with the intensity of the second optical signal.

[0154] In the embodiment of the present application, a suitable laser is selected as the light source, and common lasers include helium-neon lasers (wavelength is about 632.8 nm) or diode lasers. The selection of the light source needs to take into account the stability of the light source and the blood absorption characteristics.

[0155] The laser should be able to emit a stable and adjustable light signal, and the laser intensity and frequency can be adjusted by a control unit.

[0156] The control unit uses dimming technology to precisely control the output power of the laser. The light signal emitted each time should have the same intensity and frequency.

[0157] The optical signal output by the laser is modulated into the required waveform and intensity through the modulation optical element, and it is ensured that the two optical signals have the same light intensity.

[0158] The control unit will send two different optical signals according to a preset time interval. For example, the first optical signal can be used as a reference signal, while the second optical signal is used for dynamic measurement. The precise control of the time interval can be achieved by a clock or frequency generator.

[0159] Step 502: Obtain a first electrical signal according to the first optical signal, and obtain a second electrical signal according to the second optical signal.

[0160] In the embodiment of the present application, after the sample interacts with the light signal, an electrical signal is obtained. The intensity of the reflected light is closely related to the blood flow state, the absorption characteristics of the blood, and the structure of the blood vessels.

[0161] The obtained electrical signal is converted into a digital signal that can be processed by analog / digital conversion. A high-precision A / D converter (analog-to-digital converter) can be used to ensure accurate signal acquisition.

[0162] The method of obtaining the first electrical signal through the first optical signal is the same as the method of obtaining the second electrical signal through the second optical signal.

[0163] Step 503 obtains the strength value of the first electrical signal, and obtains the Greeneson parameter of the first electrical signal according to formula (1);

[0164] p1=Γ1(T1)η h μ a F1(1)

[0165] Wherein, in formula (1), p1 is the intensity value of the first electrical signal, Γ1 is the Grüneisen parameter of the first electrical signal, T1 is the sample temperature value corresponding to the first electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, and F1 is the intensity value of the first light signal.

[0166] Step 504, obtaining the strength value of the second electrical signal, and obtaining the Grüneisen parameter of the second electrical signal according to formula (2);

[0167] p2=Γ2(T2)η h μ a F2(2)

[0168] Wherein, in formula (2), p2 is the intensity value of the second electrical signal, Γ2 is the Grüneisen parameter of the second electrical signal, T2 is the sample temperature value corresponding to the second electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, and F2 is the intensity value of the second light signal.

[0169] Step 505, obtaining a blood flow velocity result by formula (3) according to the Grüneisen parameter of the first electrical signal and the Grüneisen parameter of the second electrical signal;

[0170]

[0171] Wherein, in formula (3), ΔΓ is the difference between the Greenesen parameter of the first electrical signal and the Greenesen parameter of the second electrical signal, μ ais the absorption coefficient, F1 is the intensity of the first light signal, δt is the temperature difference between the sample temperature value corresponding to the first electrical signal and the sample temperature value corresponding to the second electrical signal, a, k1, k2 and e are all constants, and v is the blood flow rate result.

[0172] In order to reduce the measurement error, multiple sampling can be performed within a certain period of time. By calculating the average value of multiple measurements, the accuracy of blood flow velocity measurement can be improved.

[0173] The embodiment of the present application uses the first optical signal and the second optical signal, combined with their respective electrical signal strengths, to calculate Green-Eisen parameters, and uses these parameters to infer the blood flow rate, thereby providing more accurate blood flow rate measurement.

[0174] The description of the above device embodiment is similar to the description of the above method embodiment, and has similar beneficial effects as the method embodiment. For technical details not disclosed in the device embodiment of the present application, please refer to the description of the method embodiment of the present application for understanding.

[0175] It should be noted that in the embodiment of the present application, if the above method is implemented in the form of a software function module and sold or used as an independent product, it can also be stored in a computer-readable storage medium. Based on such an understanding, the technical solution of the embodiment of the present application can be essentially or partly embodied in the form of a software product that contributes to the relevant technology. The computer software product is stored in a storage medium, including several instructions to enable an electronic device to execute all or part of the methods described in each embodiment of the present application. The aforementioned storage medium includes: various media that can store program codes, such as a U disk, a mobile hard disk, a read-only memory (ROM), a magnetic disk or an optical disk. In this way, the embodiment of the present application is not limited to any specific combination of hardware and software.

[0176] It should be understood that "one embodiment" or "an embodiment" or "some embodiments" mentioned throughout the specification means that specific features, structures or characteristics related to the embodiment are included in at least one embodiment of the present application. Therefore, "in one embodiment" or "in one embodiment" or "in some embodiments" appearing throughout the specification may not necessarily refer to the same embodiment. In addition, these specific features, structures or characteristics can be combined in one or more embodiments in any suitable manner. It should be understood that in various embodiments of the present application, the size of the sequence number of the above-mentioned processes does not mean the order of execution, and the execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiment of the present application. The above-mentioned sequence numbers of the embodiments of the present application are only for description and do not represent the advantages and disadvantages of the embodiments. The above description of each embodiment tends to emphasize the differences between the various embodiments, and the same or similar aspects can be referenced to each other. For the sake of brevity, this article will not repeat them.

[0177] The term "and / or" in this article is only a description of the association relationship of associated objects, indicating that there may be three relationships. For example, object A and / or object B can represent three situations: object A exists alone, object A and object B exist at the same time, and object B exists alone.

[0178] It should be noted that, in this article, the terms "include", "comprises" or any other variations thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further restrictions, an element defined by the sentence "comprises a ..." does not exclude the existence of other identical elements in the process, method, article or device including the element.

[0179] In the several embodiments provided in the present application, it should be understood that the disclosed devices and methods can be implemented in other ways. The embodiments described above are only schematic. For example, the division of the modules is only a logical function division. There may be other division methods in actual implementation, such as: multiple modules or components can be combined, or can be integrated into another system, or some features can be ignored, or not executed. In addition, the coupling, direct coupling, or communication connection between the components shown or discussed can be through some interfaces, and the indirect coupling or communication connection of devices or modules can be electrical, mechanical or other forms.

[0180] The modules described above as separate components may or may not be physically separated, and the components displayed as modules may or may not be physical modules; they may be located in one place or distributed on multiple network units; some or all of the modules may be selected according to actual needs to achieve the purpose of the present embodiment.

[0181] In addition, all functional modules in the embodiments of the present application may be integrated into one processing unit, or each module may be a separate unit, or two or more modules may be integrated into one unit; the above-mentioned integrated modules may be implemented in the form of hardware or in the form of hardware plus software functional units.

[0182] A person skilled in the art can understand that all or part of the steps of implementing the above method embodiment can be completed by hardware related to program instructions, and the aforementioned program can be stored in a computer-readable storage medium. When the program is executed, it executes the steps of the above method embodiment; and the aforementioned storage medium includes: mobile storage devices, read-only memories (ROM), magnetic disks or optical disks, etc., various media that can store program codes.

[0183] Alternatively, if the above-mentioned integrated unit of the present application is implemented in the form of a software function module and sold or used as an independent product, it can also be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the embodiment of the present application can essentially or in other words, the part that contributes to the relevant technology can be embodied in the form of a software product, and the computer software product is stored in a storage medium, including a number of instructions for enabling an electronic device to execute all or part of the methods described in each embodiment of the present application. The aforementioned storage medium includes: various media that can store program codes, such as mobile storage devices, ROMs, magnetic disks, or optical disks.

[0184] The methods disclosed in several method embodiments provided in this application can be arbitrarily combined without conflict to obtain new method embodiments.

[0185] The features disclosed in several product embodiments provided in this application can be arbitrarily combined without conflict to obtain new product embodiments.

[0186] The features disclosed in several method or device embodiments provided in this application can be arbitrarily combined without conflict to obtain new method embodiments or device embodiments.

[0187] The above is only an implementation method of the present application, but the protection scope of the present application is not limited thereto. Any person skilled in the art who is familiar with the present technical field can easily think of changes or substitutions within the technical scope disclosed in the present application, which should be included in the protection scope of the present application. Therefore, the protection scope of the present application should be based on the protection scope of the claims.

Claims

1. A blood flow velocity measuring device, characterized in that: The device comprises an input unit, a measuring unit, a parsing unit and a control unit, wherein the input unit, the parsing unit and the measuring unit are respectively connected to the control unit, the input unit is also connected to the measuring unit, and the measuring unit is also connected to the parsing unit, wherein: The measuring unit comprises an objective lens, a first condensing lens, a first right-angle prism, a second right-angle prism, an acoustic lens, a hexagonal prism and an ultrasonic probe, wherein: The objective lens is used to receive the optical signal input by the input unit, perform convergence processing on the optical signal, and send the optical signal to the first condensing lens after the size of the processed optical signal meets the preset size requirement; The first condensing lens is used to receive the optical signal sent by the objective lens, and after condensing the optical signal, send the optical signal to the first right-angle prism; The first right-angle prism is used to adjust the sending direction of the optical signal and send the optical signal to the hexagonal prism; The second right-angle prism is used to adjust the sending direction of the light signal refracted after the light signal is adjusted in the sending direction by the first right-angle prism, and send the light signal to the hexagonal prism; The hexagonal prism is used to adjust the angles of the light signals sent by the first right-angle prism and the second right-angle prism so that the light signals are irradiated onto the sample, receive the acoustic wave signals generated by the sample after being irradiated by the light signals, adjust the sending direction of the acoustic wave signals, and send the acoustic wave signals to the acoustic lens; The acoustic lens is used to focus the acoustic wave signal and send the acoustic wave signal to the ultrasonic probe via the first right-angle prism and the second right-angle prism; The ultrasonic probe is used to convert the sound wave signal into an electrical signal and send the electrical signal to the analysis unit; The input unit is used to receive the measurement instruction issued by the control unit, generate an optical signal, and send the optical signal to the objective lens; The analysis unit is used to receive the electrical signal sent by the ultrasound probe, analyze and process the electrical signal to obtain a digital signal, and send the digital signal to the control unit; The control unit is used to send a measurement instruction to the input unit, receive a digital signal sent by the analysis unit, analyze and process the digital signal, and obtain a blood flow velocity result.

2. The blood flow velocity measuring device according to claim 1, characterized in that: The input unit includes a laser, an aperture, a second condensing lens, a pinhole, a diffraction lens, a fiber coupler and an optical fiber, wherein: The laser is used to generate a light signal after receiving a measurement instruction sent by the control unit, and send the light signal to the aperture; The aperture is used to receive the optical signal sent by the laser, adjust the intensity of the optical signal, and send the adjusted optical signal to the second condensing lens; The second condensing lens is used to receive the light signal sent by the aperture, perform condensing processing on the light signal, and send the light signal to the pinhole; The pinhole is used to receive the optical signal sent by the second condensing lens, filter the optical signal to obtain a filtered optical signal, and send the optical signal to the astigmatism lens; The astigmatism lens is used to receive the optical signal sent by the pinhole, perform divergent light convergence processing on the optical signal, and send the optical signal after the divergent light convergence processing to the optical fiber coupler; The optical fiber coupler receives the optical signal sent by the light-scattering lens, converts the optical signal from a free-space optical transmission mode to an optical fiber transmission mode, and sends the optical signal in the optical fiber transmission mode to the optical fiber; The optical fiber is used to receive the optical signal sent by the optical fiber coupler and transmit the optical signal to the objective lens.

3. The blood flow velocity measuring device according to claim 1, characterized in that: The analysis unit includes a low noise amplifier and a signal acquisition card, wherein: The low noise amplifier is used to receive the electrical signal sent by the ultrasonic probe, amplify the electrical signal, and then send it to the signal acquisition card; The signal acquisition card is used to receive the electrical signal sent by the low noise amplifier, convert the electrical signal into a digital signal, and then send it to the control unit.

4. The blood flow velocity measuring device according to any one of claims 2 or 3, characterized in that: The control unit comprises a function generator and a processing module, wherein: The function generator is used to receive the control instruction sent by the processing module, and control the hexagonal prism to rotate according to the control instruction; The processing module is used to send control instructions to the function generator, send measurement instructions to the laser, receive digital signals sent by the signal acquisition card, and analyze and process the digital signals to obtain blood flow velocity results.

5. The blood flow velocity measuring device according to claim 2, characterized in that: The laser is a pulse laser.

6. The blood flow velocity measuring device according to claim 1, characterized in that: The measuring unit is of sealed design.

7. The blood flow velocity measuring device according to claim 6, characterized in that: The internal filling liquid of the measuring unit is pure water.

8. The blood flow velocity measuring device according to claim 7, characterized in that: The inner coating of the first right-angle prism in the measuring unit is a high-reflection coating.

9. The blood flow velocity measuring device according to claim 8, characterized in that: The ultrasonic probe in the measuring unit is fixed on the second right-angle prism.

10. A blood flow velocity measurement method, applied to the blood flow velocity measurement device described in any one of claims 1 to 9, characterized in that: include: The control input unit sends a first optical signal and a second optical signal at a preset time interval, and the intensity of the first optical signal is consistent with the intensity of the second optical signal; Obtaining a first electrical signal according to the first optical signal, and obtaining a second electrical signal according to the second optical signal; Obtaining the strength value of the first electrical signal, and obtaining the Greeneson parameter of the first electrical signal according to formula (1); p1=Γ1(T1)η h m a F1(1) Wherein, in formula (1), p1 is the intensity value of the first electrical signal, Γ1 is the Grüneisen parameter of the first electrical signal, T1 is the sample temperature value corresponding to the first electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, F1 is the intensity value of the first light signal; Obtaining the strength value of the second electrical signal, and obtaining the Greeneson parameter of the second electrical signal according to formula (2); p2=Γ2(T2)η h m a F2(2) Wherein, in formula (2), p2 is the intensity value of the second electrical signal, Γ2 is the Grüneisen parameter of the second electrical signal, T2 is the sample temperature value corresponding to the second electrical signal, η h is the heat conversion efficiency, μ a is the absorption coefficient, F2 is the intensity value of the second light signal; According to the Grüneisen parameter of the first electrical signal and the Grüneisen parameter of the second electrical signal, a blood flow velocity result is obtained by formula (3); Wherein, in formula (3), ΔΓ is the difference between the Grüneisen parameter of the first electrical signal and the Grüneisen parameter of the second electrical signal, μ a is the absorption coefficient, F1 is the intensity of the first light signal, δt is the temperature difference between the sample temperature value corresponding to the first electrical signal and the sample temperature value corresponding to the second electrical signal, a, k1, k2 and e are all constants, and v is the blood flow velocity result.

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