Blood flow velocity measuring device and method

Abstract

The present application discloses a blood flow velocity measurement device and method, including an input unit, a measuring unit, a parsing unit, and a control unit. 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, which is also connected to the parsing unit. The parsing unit is used to receive an electrical signal sent by an ultrasonic probe, parse 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 parsing unit, analyze and process the digital signal, and obtain a blood flow velocity result. The present application integrates the input unit, the measuring unit, the parsing unit, and the control unit through a reasonable unit design, making the overall structure easier to miniaturize.

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] Accurately measuring blood flow velocity is crucial for assessing vascular health and diagnosing related diseases. Photoacoustic imaging, an emerging non-destructive testing method, combines the advantages of optics and ultrasound to provide high-resolution internal tissue information. However, existing photoacoustic imaging equipment is often bulky, complex, and lacks portability, limiting its 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, the embodiments of the present application provide a blood flow velocity measurement device and method, which can miniaturize the device structure and improve the applicability of the blood flow velocity measurement device. The blood flow velocity measurement device provided in the embodiments of the present application is implemented as follows:

[0005] An embodiment of the present application provides a blood flow velocity measurement device, comprising:

[0006] 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 further connected to the measuring unit, and the measuring unit is further connected to the parsing unit, wherein:

[0007] The measuring unit includes 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 configured 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 a preset size requirement;

[0009] The first condensing lens is used to receive the optical signal sent by the objective lens, perform focusing processing on the optical signal, and then 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 transmission direction of the light signal refracted after the light signal is adjusted in the transmission 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 transmission 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 acoustic wave signal into an electrical signal and send the electrical signal to the analyzing unit;

[0015] The input unit is configured to receive a measurement instruction from the control unit, generate an optical signal, and send the optical signal to the objective lens;

[0016] The analyzing unit is configured 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 the 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 configured 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 focusing 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 astigmatism 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 ultrasound 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 configured to receive a 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-reflection coating.

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

[0037] The present invention provides a method for measuring blood flow velocity, comprising:

[0038] The control input unit sends a first optical signal and a second optical signal at a preset time interval, wherein 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 intensity value of the first electrical signal, and obtaining the Greeness 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 Greeneisen 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 intensity value of the second electrical signal, and obtaining the Greenesen 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 Greeneisen 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 Greenesen parameter of the first electrical signal and the Greenesen 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 Greenesen parameter of the first electrical signal and the Greenesen 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] The embodiments of the present application provide a blood flow velocity measurement device and method, comprising an input unit, a measuring unit, an analysis unit, and a control unit. The input unit, the analysis unit, and the measuring unit are respectively connected to the control unit. The input unit is also connected to the measuring unit, which is also connected to the analysis unit. The analysis unit is used to receive an electrical signal sent by an 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 analysis unit, analyze and process the digital signal, and obtain a blood flow velocity result. In this way, the blood flow velocity measurement device integrates the input unit, the measuring unit, the analysis unit, and the control unit through reasonable unit design, making the overall structure easier to miniaturize and 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 following briefly introduces the drawings required for use in the embodiments of the present application or the description of the prior art. 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 structural diagram of a blood flow velocity measurement device provided in an embodiment of the present application;

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

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

[0054] Figure 4 A schematic structural diagram 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] To make the purpose, technical solutions and advantages of the embodiments of the present application clearer, the specific technical solutions 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 intended to limit the scope of the present application.

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

[0058] In the following description, reference is made to “some embodiments”, which describes 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 with 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 This is a structural schematic diagram of a blood flow rate measuring device provided in an embodiment of the present application, which includes an input unit, a measuring unit, an analysis unit and a control unit. The input unit, the analysis 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 analysis unit.

[0061] The measuring unit includes 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 elements.

[0064] This application uses a single lens to achieve focusing. By designing the curvature and focal length of the objective lens 1, the focusing of the light signal 8 can be precisely controlled.

[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 to receive the optical signal 8 sent by the objective lens 1 , perform focusing processing on the optical signal 8 , and then send 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 of the lens should be designed to 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 be carried out smoothly.

[0070] The first right-angle prism 3 is used to adjust the transmission 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 transmission direction of the optical signal 8 after the optical signal 8 is 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 can be made of optical glass with a high refractive index to ensure that the light 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 fine-tune the position of the prism through a fine-tuning knob or an electric drive mechanism, thereby achieving 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, receive the acoustic wave signal 9 generated by the sample after being irradiated by the light signal 8, adjust the transmission 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 based on the characteristics 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 hydrogel, etc. The structural design of the lens needs to ensure that it can effectively focus the sound waves and 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 acoustic 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 acoustic 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 acoustic wave signal 9 into an electrical signal. Common piezoelectric materials include lead titanate and the like.

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

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

[0087] Specifically, the measurement unit is designed to be a completely enclosed environment to prevent external environmental factors (such as dust, moisture, and temperature fluctuations) from interfering with or influencing the measurement process. The measurement unit can utilize an integrated sealed housing to prevent the ingress of foreign matter. Within the measurement unit, key components such as the objective lens 1, optical lens, and ultrasonic probe 7 typically require operation in a clean, stable environment. The sealed design can minimize the effects of external light and gases, ensuring the accuracy of measurement results.

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

[0089] The sealed design of this application example effectively prevents the external environment (such as dust, moisture, and contaminants) from affecting the optical and electronic components within the measurement unit, ensuring long-term stable operation of the device. The sealing improves the stability of the internal environment of the measurement unit, avoids external interference, and ensures that the propagation of the optical and acoustic signals 9 is not affected 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, the measurement cell is filled with pure water to provide a stable and transparent medium. Pure water has excellent sound wave conductivity and does not introduce other impurities, thereby reducing noise interference and improving 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] This application example uses pure water as the internal filling liquid of the measuring unit to effectively improve the performance, stability and service life of the entire blood flow rate measurement system.

[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 interior coating of the first right-angle prism 3 is a highly reflective coating. This coating enhances the reflection efficiency of the light signal 8, maximizing its intensity during reflection and refraction within the prism, minimizing signal attenuation, and ensuring smooth signal transmission to subsequent optical components and illumination of the sample.

[0096] The example of this application can significantly improve the reflection efficiency of the light signal 8 inside the prism through the high-reflective 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 rectangular 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 to the second rectangular prism 4, the ultrasonic probe 7 may be connected to the second rectangular prism 4 by mechanical fixing means (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 mounting position for the ultrasonic probe 7, ensuring accurate transmission of the ultrasonic signal during the measurement process.

[0100] By fixing the ultrasonic probe 7 to the second rectangular prism 4, the present example ensures that the ultrasonic probe 7 is in a stable position during the measurement process, reducing errors caused by device vibration or external factors. The fixed design effectively prevents the position of the ultrasonic probe 7 from shifting, ensuring that the area it detects is consistent during each measurement, thereby improving 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 typically chosen 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 specific frequency or time characteristics, which facilitates 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. The analysis unit must be able to process the transmission signal in real time to ensure timely feedback of blood flow velocity 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 can 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 perform necessary operation settings.

[0110] By utilizing multiple optical and acoustic components, the embodiments of this application are able to precisely focus and adjust the transmission paths of light and sound waves, ensuring accurate blood flow velocity measurements. Multiple conversions and processing of optical and acoustic signals improve signal stability and accuracy. The rational combination and compact integration of the various optical and acoustic components achieves a good balance between size and performance. This device enables multifunctional operation within a compact footprint, improving convenience and application scope.

[0111] In the above Figure 1 Based on this, the present application also provides a structural diagram of a blood flow velocity measuring 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 diffraction 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 from 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, consider a pulsed laser. A pulsed laser emits short, high-intensity laser pulses rather than a continuous laser beam. This method generates a high-energy optical signal in a short period of time. Pulsed lasers can provide precise optical pulses, facilitating blood flow velocity measurements using the photoacoustic effect. The short pulse timescale effectively minimizes interference caused by interactions between light, tissue, and blood, resulting in more accurate measurements.

[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 results 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 this embodiment, light signal 8 emitted by laser 10 enters aperture 11. Aperture 11 regulates the intensity of light signal 8 (i.e., adjusts the brightness of the light) to prevent excessive or insufficient light signal 8 from affecting the operation of subsequent optical components. The regulated light signal 8 is then transmitted to a second condenser 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 this embodiment of the present application, a second condenser lens 12 further focuses the light signal 8 after it has passed through the aperture 11. After passing through this lens, the light signal 8 becomes more concentrated, forming a beam suitable for the subsequent optical path. The focused light signal 8 is then 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 astigmatism lens 14 .

[0121] In this embodiment, a pinhole 13 is located in the optical path to filter out unnecessary stray light or substandard optical signals 8. Pinhole 13 selects the light beam that meets the requirements and allows the optical signals 8 to pass through and continue to transmit downward. After passing through pinhole 13, optical signals 8 are transmitted to 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 beam passing through the pinhole 13 is appropriately scattered or diverged by the light beam 14 to ensure that the light beam can propagate at an appropriate angle or shape to meet the reception conditions of the subsequent fiber coupler 15. After passing through the light beam 14, the light beam becomes more suitable for transmission through the optical fiber 18.

[0124] The fiber coupler 15 receives the optical signal 8 sent by the astigmatism lens 14 , converts the optical signal 8 from the free space light 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 this embodiment of the present application, fiber coupler 15 is responsible for converting optical signal 8, after being conditioned by astigmatism lens 14, from a free-space transmission mode to a transmission mode via optical fiber 18. Fiber coupler 15 can introduce optical signal 8 into optical fiber 18 through a physical structure or optical elements, thereby achieving guidance and transmission of 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 this embodiment of the present application, optical fiber 18 receives optical signal 8 from optical fiber coupler 15 and efficiently transmits it to objective lens 1 of the measurement unit. The main function of optical fiber 18 is to minimize the loss of optical signal 8 during the signal transmission from the input unit to objective lens 1.

[0128] Through the coordinated operation of the aforementioned series of optical components, the embodiment of the present application can precisely control and adjust the intensity and focus of light signal 8, ensuring that light signal 8 entering objective lens 1 possesses suitable optical properties. This improves the quality and stability of light signal 8, thereby enhancing the accuracy of measurement results. Furthermore, the use of optical fiber 18 reduces the reliance on complex optical path alignment, making the overall system more reliable and easier to maintain.

[0129] In the above Figure 1 Based on this, the present application also provides a structural diagram of a blood flow velocity measuring 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 of low-noise amplifier 17 is connected to ultrasound probe 7. Ultrasound probe 7 converts acoustic signal 9 into an electrical signal. The amplifier's gain can be adjusted by a control unit to select an appropriate gain based on the desired signal strength. For example, during blood flow measurement, gain adjustment may be necessary to optimize signal strength and prevent signal distortion caused by over-amplification.

[0133] The low noise amplifier 17 minimizes interference from external noise sources and maintains signal clarity by using a low noise amplifier circuit (such as a high-quality operational amplifier). 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 terminal 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 the analog-to-digital converter. The analog-to-digital converter converts the analog signal into a digital signal for subsequent processing. This application uses a high-resolution digital-to-analog converter (e.g., 12-bit or 16-bit) to ensure signal accuracy during blood flow velocity measurement.

[0138] The sampling rate determines the accuracy and real-time nature 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 required for 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 structural diagram of a blood flow velocity measuring 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 operating parameters of other devices to ensure that the optical path and acoustic path can operate in the 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 hexagonal prism 6 is precisely adjusted by controlling the signal generated by function generator 20. By varying the rotation angle of hexagonal prism 6, function generator 20 can influence the propagation direction of optical signal 8 or acoustic signal 9. The rotation angle of hexagonal prism 6 is typically 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 present embodiment, processing module 19 is responsible for processing and analyzing the collected data. It controls the system workflow by interacting with other components. Processing module 19 sends instructions to laser 10 and other devices via a communication interface (such as a serial port, parallel port, or a higher-level bus interface) to control the emission of optical signal 8 and adjust the signal path during acquisition.

[0148] The processing module 19 receives digital signals from the signal acquisition card 16. These signals 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 digitized 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 via a display screen, a console or other output device. The user can view the real-time blood flow rate data on the screen.

[0151] The control unit design in this embodiment of the present application further coordinates the operation of the optical and ultrasonic systems, optimizing the overall measurement process. The use of function generator 20 allows the optical system to be flexibly adjusted as needed, ensuring adaptability under different measurement conditions. Processing module 19 efficiently performs data processing and analysis.

[0152] The present application also provides a method for measuring blood flow rate. 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. Common lasers include helium-neon lasers (wavelength of about 632.8 nm) or diode lasers. The selection of the light source should 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, ensuring that each emitted light signal has 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 at preset time intervals. 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, the sample interacts with the light signal to generate an electrical signal. 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 from analog to digital to a processable digital signal. A high-precision A / D converter (analog-to-digital converter) can be used to ensure accurate signal acquisition.

[0162] The manner of obtaining the first electrical signal through the first optical signal is the same as the manner 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 Greenesen 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 Greeneisen 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 Greenesen 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 Greeneisen 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) based on the Greenesen parameter of the first electrical signal and the Greenesen 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 velocity result.

[0172] In order to reduce measurement errors, 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 calculates Green-Eisen parameters by using the first and second optical signals in combination with their respective electrical signal strengths, and infers blood flow velocity based on these parameters, thereby providing more accurate blood flow velocity 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 this application, please refer to the description of the method embodiment of this 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 this understanding, the technical solution of the embodiment of the present application is essentially or 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 method 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 the 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 an embodiment" or "in some embodiments" appearing throughout the specification do 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 the various embodiments of the present application, the size of the serial numbers of the above-mentioned processes does not mean the order of execution. 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 embodiments of the present application. The above-mentioned serial numbers of the embodiments of the present application are for description only and do not represent the advantages and disadvantages of the embodiments. The above description of the various embodiments tends to emphasize the differences between the various embodiments. The same or similar aspects can be referenced to each other. For the sake of brevity, they will not be repeated here.

[0177] The term "and / or" in this article is only a description of the association relationship between associated objects, indicating that there can be three relationships. For example, object A and / or object B can mean: 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 document, the terms "comprises," "includes," or any other variations thereof are intended to encompass non-exclusive inclusion, such that a process, method, article, or apparatus comprising a series of elements includes not only those elements but also other elements not explicitly listed, or elements inherent to such process, method, article, or apparatus. In the absence of further limitations, an element defined by the phrase "comprising a ..." does not exclude the presence of other identical elements in the process, method, article, or apparatus comprising the element.

[0179] In the several embodiments provided in this application, it should be understood that the disclosed devices and methods can be implemented in other ways. The embodiments described above are merely illustrative. For example, the division of the modules is merely a logical function division. In actual implementation, there may be other division methods, 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 across multiple network units; some or all of the modules may be selected according to actual needs to achieve the purpose of this embodiment.

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

[0182] Those skilled in the art will understand that all or part of the steps of implementing the above-mentioned 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-mentioned method embodiment; and the aforementioned storage medium includes: mobile storage devices, read-only memories (ROM), magnetic disks or optical disks, and other 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 functional 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, or the part that contributes to the relevant technology, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes 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 the several method embodiments provided in this application can be arbitrarily combined without conflict to obtain new method embodiments.

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

[0186] The features disclosed in the 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 merely an embodiment of the present application, but the scope of protection of the present application is not limited thereto. Any changes or substitutions that can be easily conceived by a person skilled in the art within the technical scope disclosed in this application should be included in the scope of protection of this application. Therefore, the scope of protection of this application should be based on the scope of protection of the claims.

Claims

1. A blood flow velocity measuring device, characterized in that: The device includes 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 further connected to the measuring unit, and the measuring unit is further connected to the parsing unit, wherein: The measuring unit includes 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 configured 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 a preset size requirement; The first condensing lens is used to receive the optical signal sent by the objective lens, perform focusing processing on the optical signal, and then 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 transmission direction of the light signal refracted after the light signal is adjusted in the transmission 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 transmission 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 acoustic wave signal into an electrical signal and send the electrical signal to the analyzing unit; The input unit is configured to receive a measurement instruction from the control unit, generate an optical signal, and send the optical signal to the objective lens; The analyzing unit is configured 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 the 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 configured 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 focusing 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 astigmatism 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 ultrasound 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 includes a function generator and a processing module, wherein: The function generator is configured to receive a 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 according to 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, wherein 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 intensity value of the first electrical signal, and obtaining the Greeness 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 Greeneisen 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 intensity value of the second electrical signal, and obtaining the Greenesen 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 Greeneisen 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 Greenesen parameter of the first electrical signal and the Greenesen 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 Greenesen parameter of the first electrical signal and the Greenesen 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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