CN119586994B - Blood flow velocity measuring device and method - Google Patents
Blood flow velocity measuring device and methodInfo
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- CN119586994B CN119586994B CN202411927824.3A CN202411927824A CN119586994B CN 119586994 B CN119586994 B CN 119586994B CN 202411927824 A CN202411927824 A CN 202411927824A CN 119586994 B CN119586994 B CN 119586994B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
- A61B5/026—Measuring blood flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
- A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
- A61B5/026—Measuring blood flow
- A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
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Abstract
The embodiment of the application discloses a blood flow velocity measuring device and a method, wherein the device comprises 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 with the control unit, the input unit is also connected with the measuring unit, the measuring unit is also connected with the analyzing unit, the analyzing unit is used for receiving an electric signal sent by an 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 measuring instruction to the input unit, receiving the digital signal sent by the analyzing unit and analyzing the digital signal to obtain a blood flow velocity result. The application integrates the input unit, the measuring unit, the analyzing unit, the control unit and the like through reasonable unit design, so that the whole structure is easier to realize miniaturization.
Description
Technical Field
The application relates to the technical field of information processing, in particular to a blood flow velocity measuring device and a method.
Background
Accurate measurement of blood flow velocity is of great importance for assessing vascular health and diagnosing related diseases. In the prior art, the photoacoustic imaging technology is used as an emerging nondestructive detection means, combines the advantages of optics and ultrasonic waves, and can provide tissue internal information at a higher resolution. However, most of the existing photoacoustic imaging devices are large in volume, complex in structure, not portable, and limited in practical application in clinical environments.
Therefore, how to ensure portability of the blood flow velocity measuring device and improve applicability of the blood flow velocity measuring device is a problem to be solved urgently.
Disclosure of Invention
Therefore, the blood flow velocity measuring device and the blood flow velocity measuring method provided by the embodiment of the application can miniaturize the device structure and improve the applicability of the blood flow velocity measuring device. The blood flow velocity measuring device provided by the embodiment of the application is realized by the following steps:
the embodiment of the application provides a blood flow velocity measuring device, which comprises:
The input unit, the measurement unit, parse unit and control unit, the input unit the parse unit and the measurement unit respectively with control unit connects, the input unit still with the measurement unit connects, the measurement unit still with parse unit connects, 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 for receiving the optical signals input by the input unit, carrying out convergence processing on the optical signals, and sending the optical signals to the first condensing lens after the size of the processed optical signals meets the preset size requirement;
the first condensing lens is configured to receive an optical signal sent by the objective lens, perform condensing processing on the optical signal, and send the optical signal to the first right-angle prism;
The first right-angle prism is used for adjusting the sending direction of the optical signal and sending the optical signal to the hexagonal prism;
The second right-angle prism is used for adjusting the sending direction of the optical signal, which is refracted after the sending direction of the optical signal is adjusted by the first right-angle prism, and sending the optical signal to the hexagonal prism;
The hexagonal prism is used for adjusting the angles of the optical signals sent by the first right-angle prism and the second right-angle prism, so that the optical signals irradiate on a sample, receiving sound wave signals generated by the sample after the optical signals irradiate, adjusting the sending direction of the sound wave signals and sending the sound wave signals to the acoustic lens;
The sound lens is used for focusing the sound wave signals and sending the sound wave signals to the ultrasonic probe through the first right-angle prism and the second right-angle prism;
the ultrasonic probe is used for converting the sound wave signal into an electric signal and sending the electric signal to the analysis unit;
The input unit is used for receiving the measurement instruction sent by the control unit, generating an optical signal and sending the optical signal to the objective lens;
The analysis unit is used for receiving the electric signals sent by the ultrasonic probe, analyzing the electric signals to obtain digital signals, and sending the digital signals to the control unit;
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.
In some embodiments, the input unit comprises a laser, an aperture, a second condenser lens, a pinhole, a astigmatic lens, a fiber coupler, and an optical fiber, wherein:
the laser is used for generating an optical signal after receiving the measurement instruction sent by the control unit and sending the optical signal to the diaphragm;
The diaphragm is used for receiving the optical signal sent by the laser, adjusting the intensity of the optical signal and sending the adjusted optical signal to the second focusing lens;
the second focusing lens is configured to receive the optical signal sent by the diaphragm, perform focusing processing on the optical signal, and send the optical signal to the pinhole;
The pinhole is configured to receive the optical signal sent by the second optical focusing lens, filter the optical signal to obtain a filtered optical signal, and send the optical signal to the astigmatic lens;
the light scattering lens is used for receiving the optical signals sent by the pinholes, performing divergent light convergence processing on the optical signals, and sending the optical signals subjected to the divergent light convergence processing to the optical fiber coupler;
the optical fiber coupler receives the optical signal sent by the astigmatic 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 for receiving the optical signal sent by the optical fiber coupler and transmitting the optical signal to the objective lens.
In some embodiments, the parsing unit includes a low noise amplifier and a signal acquisition card, wherein:
The low-noise amplifier is used for receiving the electric signal sent by the ultrasonic probe, amplifying the electric signal and sending the amplified electric signal to the signal acquisition card;
The signal acquisition card is used for receiving the electric signal sent by the low-noise amplifier, converting the electric signal into a digital signal and then sending the digital signal to the control unit.
In some embodiments, the control unit comprises a function generator and a processing module, wherein:
The function generator is used for receiving the control instruction sent by the processing module and controlling the hexagonal prism to rotate according to the control instruction;
the processing module is used for sending a control instruction to the function generator, sending a measurement instruction to the laser, receiving a digital signal sent by the signal acquisition card, and analyzing and processing the digital signal to obtain a blood flow velocity result.
In some embodiments, the laser is a pulsed laser.
In some embodiments, the measurement unit is of sealed design.
In some embodiments, the internal filling liquid of the measuring unit is purified water.
In some embodiments, the internal coating of the first right angle prism is a highly reflective coating.
In some embodiments, the ultrasound probe is fixed to the second right angle prism.
The embodiment of the application provides a blood flow velocity measuring method, which comprises the following steps:
the method comprises the steps that an input unit is controlled to respectively send a first optical signal and a second optical signal at preset intervals, and the intensity of the first optical signal is consistent with that 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;
acquiring an intensity value of the first electric signal, and obtaining a green elsen parameter of the first electric signal according to a formula (1);
p1＝Γ1(T1)ηhμaF1(1)
In formula (1), p 1 is the intensity value of the first electrical signal, Γ 1 is the green eastern parameter of the first electrical signal, T 1 is the sample temperature value corresponding to the first electrical signal, η h is the thermal conversion efficiency, μ a is the absorption coefficient, and F 1 is the intensity value of the first optical signal;
acquiring an intensity value of the second electric signal, and obtaining a green elsen parameter of the second electric signal according to a formula (2);
p2＝Γ2(T2)ηhμaF2(2)
In formula (2), p 2 is the intensity value of the second electrical signal, Γ 2 is the green eastern parameter of the second electrical signal, T 2 is the sample temperature value corresponding to the second electrical signal, η h is the thermal conversion efficiency, μ a is the absorption coefficient, and F 2 is the intensity value of the second optical signal;
Obtaining a blood flow velocity result through a formula (3) according to the green elsen parameter of the first electric signal and the green elsen parameter of the second electric signal;
In formula (3), ΔΓ is the difference between the green eastern parameter of the first electrical signal and the green eastern parameter of the second electrical signal, μ a is the absorption coefficient, F 1 is the intensity of the first optical 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 constants, and v is the blood flow velocity result.
The embodiment of the application provides a blood flow velocity measuring device and a method, wherein the device comprises 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 with the control unit, the input unit is also connected with the measuring unit, the measuring unit is also connected with the analyzing unit, the analyzing unit is used for receiving an electric signal sent by an 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 measuring instruction to the input unit, receiving the digital signal sent by the analyzing unit and analyzing the digital signal to obtain a blood flow velocity result. Like this, through reasonable unit design to blood velocity of flow measuring device, with input unit, measuring unit, analytic unit and control unit etc. integrate for overall structure is easier to realize miniaturization, solves the technical problem that proposes among the background art.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following description will briefly explain the embodiments of the present application or the drawings used in the description of the prior art, and it is obvious that the drawings in the following description are some embodiments of the present application, and other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
Fig. 1 is a schematic structural diagram of a blood flow velocity measuring device according to an embodiment of the present application;
FIG. 2 is a schematic diagram of another blood flow velocity measuring device according to an embodiment of the present application;
FIG. 3 is a schematic diagram of another blood flow velocity measuring device according to an embodiment of the present application;
FIG. 4 is a schematic diagram of another blood flow velocity measurement device according to an embodiment of the present application;
fig. 5 is a schematic flow chart of a blood flow velocity measurement method according to an embodiment of the present application.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present application more apparent, the specific technical solutions of the present application will be described in further detail below with reference to the accompanying drawings in the embodiments of the present application. The following examples are illustrative of the application and are not intended to limit the scope of the application.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing embodiments of the application only and is not intended to be limiting of the application.
In the following description, reference is made to "some embodiments" which describe a subset of all possible embodiments, but it is to be understood that "some embodiments" can be the same subset or different subsets of all possible embodiments and can be combined with one another without conflict.
It should be noted that the term "first/second/third" in relation to embodiments of the present application is used to distinguish between similar or different objects, and does not represent a particular ordering of the objects, it being understood that the "first/second/third" may be interchanged with a particular order or sequencing, as permitted, to enable embodiments of the present application described herein to be implemented in an order other than that illustrated or described herein.
Fig. 1 is a schematic structural diagram of a blood flow velocity measuring device according to an embodiment of the present application, which includes 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 with the control unit, the input unit is further connected with the measuring unit, and the measuring unit is further connected with the analyzing unit.
The measuring unit comprises an objective lens 1, a first condenser 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:
The objective lens 1 is configured 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 a preset size requirement.
In an embodiment of the application, the objective lens 1 focuses the optical signal 8 from the input unit to the subsequent optical element.
The application uses a single lens to accomplish focusing. By the curvature and focal length design of the objective lens 1, the focusing of the optical signal 8 can be precisely controlled.
Good light transmittance and refractive index can be ensured by selecting common optical glass materials, so that focusing effect is ensured.
The first condenser lens 2 is configured to receive the optical signal 8 sent from the objective lens 1, perform condensing processing on the optical signal 8, and send the optical signal 8 to the first right angle prism 3.
In the embodiment of the present application, the first condensing lens 2 is used to further focus the optical signal 8 and provide a proper incident angle for the subsequent right angle prism and hexagonal prism 6.
The lens material can be optical glass with high refractive index, so that the focusing performance of the optical glass is optimized. The focal length of the lens is designed to ensure that the focused beam diameter meets the experimental requirements.
The propagation direction of the light beam can be precisely controlled by adjusting the inclination angle of the lens, so that the angle adjustment of the subsequent optical element can be smoothly performed.
The first right angle prism 3 adjusts the transmission direction of the optical signal 8, and transmits the optical signal 8 to the hexagonal prism 6. The second right angle prism 4 is used for adjusting the transmitting direction of the optical signal 8, generating the transmitting direction of the refracted optical signal 8 after the transmitting direction of the optical signal 8 is adjusted by the first right angle prism 3, and transmitting the optical signal 8 to the hexagonal prism 6.
In the embodiment of the application, the primary function of the prism is to precisely adjust the angle of the light rays in order to properly transmit the light signal 8 to the hexagonal prism 6.
The right angle prism may be made of high refractive index optical glass to ensure minimal loss of the optical signal 8 during refraction and accurate reflection.
The accurate positioning and angle adjustment of the prism are very critical, and the position of the prism can be finely adjusted through a fine adjustment knob or an electric driving mechanism, so that the accurate control of the light beam direction is realized.
The hexagonal prism 6 is configured to adjust angles of the optical signals 8 sent by the first right-angle prism 3 and the second right-angle prism 4, so that the optical signals 8 irradiate the sample, receive the acoustic wave signals 9 generated by the sample irradiated by the optical signals 8, adjust a sending direction of the acoustic wave signals 9, and send the acoustic wave signals 9 to the acoustic lens 5;
In the embodiment of the application, the primary task of the hexagonal prism 6 is to guide the optical signal 8, which has been adjusted by two refractions, further to the sample and reflect the returned acoustic signal 9.
The geometry and optical characteristics of the hexaprism 6 need to be accurately calculated from the characteristics of the light source and the measurement target. The face angle and size of the prism directly affects the reflection angle of the optical signal 8.
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 increase the reflection efficiency.
An acoustic lens 5 for focusing the acoustic wave signal 9 and transmitting the acoustic wave signal 9 to the ultrasonic probe 7 via the first right angle prism 3 and the second right angle prism 4.
In the embodiment of the application, the acoustic lens 5 is used to focus the acoustic wave signal 9 reflected from the blood sample and to ensure the direction of propagation and the intensity of the signal.
The acoustic lens 5 of the present application employs a material having a high acoustic transmittance, such as a polymer or hydrogel, or the like. The structural design of the lens needs to ensure that the sound wave can be effectively focused and avoid attenuation of the signal.
The acoustic lens 5 concentrates the scattered acoustic wave signal 9 to a specific area by its curved or concave design, thereby improving the detection accuracy.
The ultrasonic probe 7 is used for converting the acoustic wave signal 9 into an electric signal and sending the electric signal to the analysis unit.
In an embodiment of the application, the ultrasound probe 7 converts the acoustic wave signal 9 into an electrical signal, providing the input required for subsequent signal processing.
The piezoelectric element in the ultrasonic probe 7 is a core component thereof, and is capable of converting the acoustic wave signal 9 into an electrical signal. Common piezoelectric materials include lead titanate and the like.
The operating frequency of the ultrasound probe 7 determines its sensitivity to different flow rate ranges. Generally, high frequency probes are suitable for finer blood flow measurements, while low frequency probes are suitable for deeper tissue detection.
As an example, the measuring unit is of sealed design.
In particular, the structure of the measuring unit is designed as a completely closed environment, in order to prevent interference or influence of external environmental factors (such as dust, moisture, temperature fluctuations, etc.) on the measuring process. The measuring unit may employ an integrated sealed housing to prevent the ingress of foreign matter. Inside the measuring unit, important components like the objective lens 1, the optical lens, the ultrasonic probe 7 and the like usually need to work in a clean and stable environment, and the sealing design can reduce the influence of external light and gas and ensure the accuracy of the measuring result.
And the input unit is used for receiving the measurement instruction sent by the control unit, generating an optical signal 8 and sending the optical signal 8 to the objective lens 1.
The application can effectively prevent the influence of external environment (such as dust, moisture, pollutants and the like) on the optical element and the electronic element in the measuring unit through the sealing design, and ensure the long-term stable operation of the equipment. By 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 not to be influenced by external factors, so that the accuracy of blood flow velocity measurement is improved.
As an example, the internal filling liquid of the measuring unit is purified water.
In particular, the filling of purified water inside the measuring unit is intended to provide a stable and transparent medium. The purified water has good sound wave conduction performance and can not introduce other impurities, so that noise interference can be reduced, and the transmission efficiency of sound waves is improved.
The purpose of the filling with purified water is to ensure that the optical signal 8 and the acoustic wave signal 9 can propagate efficiently and stably during the measurement.
The pure water is used as the filling liquid in the measuring unit, so that the performance, the stability and the service life of the whole blood flow velocity measuring system can be effectively improved.
As an example, the inner coating of the first right angle prism 3 in the measuring unit is a highly reflective coating.
Specifically, the internal coating of the first right angle prism 3 is a highly reflective coating. The effect of this coating is to enhance the reflection efficiency of the optical signal 8, so that the optical signal 8 maintains its intensity to the greatest extent during the reflection and refraction processes inside the prism, reduces the attenuation of the optical signal 8, and ensures that the signal can be smoothly transmitted to the subsequent optical element and irradiated onto the sample.
The high-reflection coating can obviously improve the reflection efficiency of the optical signal 8 in the prism, and reduce the loss of the optical signal 8, so that more optical signals 8 can be ensured to be effectively transmitted to a sample or other optical elements, and the overall performance and sensitivity of the measuring system are improved.
As an example, the ultrasonic probe 7 in the measuring unit is fixed to the second right angle prism 4.
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 refractive element of the optical signal 8, but also serves as a position component for supporting the ultrasonic probe 7.
When the ultrasonic probe 7 is fixed on the second right angle prism 4, it is possible to connect the ultrasonic probe 7 with the second right angle prism 4 by a mechanical fixing means such as a screw or an adhesive. In this way, the second right angle 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 accurate transmission of the ultrasonic signal during measurement.
The ultrasonic probe 7 is fixed on the second right-angle prism 4, so that the ultrasonic probe 7 can be ensured to be in a stable position in the measuring process, and errors caused by vibration of the device or external factors are reduced. The fixed design can effectively avoid the position of the ultrasonic probe 7 from shifting, ensure that the detection area is consistent during each measurement, and further improve the measurement accuracy.
In the embodiment of the present application, the function of the input unit is to generate a stable and accurate optical signal 8 and control the emitting direction and intensity of the optical signal 8.
Lasers or LED light sources having wavelengths in the near infrared or visible range are typically chosen for their ability to penetrate skin tissue and interact with red blood cells in the blood. A common choice is a light source with a wavelength of 650-900 nm.
By modulating the light source (e.g., modulating the output frequency or intensity of the laser), the input unit may provide the optical signal 8 with a specific frequency or time characteristic, facilitating subsequent signal processing.
And the analysis unit is used for receiving the electric signals sent by the ultrasonic probe 7, analyzing the electric signals to obtain digital signals, and sending the digital signals to the control unit.
In the embodiment of the application, the analysis unit is used for converting the electric signal into a digital signal, filtering noise and enhancing the signal-to-noise ratio of the signal. The analysis unit needs to be capable of processing the transmission signal in real time so as to ensure timely feedback of the blood flow velocity data.
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.
The control unit is responsible for coordinating the operation of the various parts in the overall device, including issuing measurement instructions, receiving processing results, and monitoring the measurement process.
The control unit can adopt an embedded processor or a microcontroller (such as ARM, raspberry Pi, etc.) or a computer, etc., so as to ensure the normal operation of the data processing, storing and displaying functions.
The control unit may be provided with a Graphical User Interface (GUI) allowing the user to view the real-time blood flow rate data and make the necessary operational settings.
The embodiment of the application can accurately focus and adjust the transmission paths of the light waves and the sound waves by using a plurality of optical elements and acoustic elements, and ensure the measurement accuracy of the blood flow velocity. By converting and processing the optical and acoustic signals for multiple times, the stability and accuracy of the signals are improved. The reasonable combination and compact integration of the optical and acoustic elements allows the device to achieve a good balance between volume and performance. The multifunctional operation can be realized in a smaller volume, and the convenience and the application range are improved.
On the basis of fig. 1, the present application also provides a schematic structural diagram of a blood flow velocity measuring device, as shown in fig. 2, the input unit includes a laser 10, a diaphragm 11, a second condenser lens 12, a pinhole 13, a light-diffusing lens 14, an optical fiber coupler 15, and an optical fiber 18, wherein:
the laser 10 is configured to generate an optical signal 8 after receiving a measurement instruction sent by the control unit, and send the optical signal 8 to the diaphragm 11.
In the embodiment of the present application, the laser 10 starts to generate the optical signal 8 after receiving the measurement command sent by the control unit. The output optical signal 8 of the laser 10 is typically a monochromatic laser beam with a strong focusing power.
As an example, a pulsed laser is selected. Pulsed lasers emit short, high intensity laser pulses rather than a continuous beam of laser light. By means of laser pulses, a high-energy optical signal 8 can be generated in a short time, and the pulsed laser can provide accurate optical pulses, facilitating the measurement of blood flow velocity by the photoacoustic effect. Because of the short time scale of the pulse, the interference caused by the interaction between the light, the tissue and the blood can be effectively reduced, and thus, a more accurate measurement result is obtained.
The blood flow velocity measuring device using the pulse laser can improve the measuring precision, response speed and sensitivity, so that the measuring result is more accurate and reliable, and the device is suitable for more complex or fine blood flow velocity analysis.
The diaphragm 11 is configured 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 condenser lens 12.
In the embodiment of the application, the optical signal 8 emitted by the laser 10 enters the diaphragm 11. The purpose of the diaphragm 11 is to adjust the intensity of the light signal 8 (i.e. to adjust the brightness of the light) so as to avoid that the light signal 8 is too strong or too weak to affect the operation of the subsequent optical elements. The adjusted optical signal 8 is transmitted to a second condenser lens 12.
The second condenser lens 12 is configured to receive the optical signal 8 transmitted from the diaphragm 11, perform condensing processing on the optical signal 8, and transmit the optical signal 8 to the pinhole 13.
In the embodiment of the application, the second focusing lens 12 performs further focusing processing on the optical signal 8 adjusted by the diaphragm 11. After passing the lens, the optical signal 8 becomes more concentrated, forming a beam suitable for the subsequent optical path. The focused optical signal 8 is transmitted to the pinhole 13.
And a pinhole 13 for receiving the optical signal 8 sent by the second condenser lens 12, filtering the optical signal 8 to obtain a filtered optical signal 8, and sending the optical signal 8 to the astigmatic lens 14.
In the present embodiment, a pinhole 13 is located in the optical path for filtering out some unwanted stray light or undesirable optical signals 8. The pinhole 13 will screen out the light beam that is satisfactory and the light signal 8 that is allowed to pass will continue to pass downwards. The optical signal 8 after passing through the pinhole 13 will be transmitted to the astigmatic lens 14.
And a light-diffusing lens 14 for receiving the optical signal 8 sent from the pinhole 13, performing divergent light converging processing on the optical signal 8, and sending the optical signal 8 after the divergent light converging processing to the optical fiber coupler 15.
In an embodiment of the present application, the light beam passing through the pinhole 13 is appropriately scattered or diverged by the light-dispersing lens 14 to ensure that the light beam can propagate at an appropriate angle or shape, adapting the receiving conditions of the subsequent fiber coupler 15. After passing through the astigmatic lens 14, the beam becomes more suitable for transmission through the optical fiber 18.
The optical fiber coupler 15 receives the optical signal 8 sent from the astigmatic 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.
In the embodiment of the present application, the optical fiber coupler 15 is responsible for converting the optical signal 8 adjusted by the astigmatic lens 14 from the free space transmission mode to the optical fiber 18 transmission mode. The optical fiber coupler 15 may introduce the optical signal 8 into the optical fiber 18 through a physical structure or optical element, thereby enabling the guiding and transmission of the optical signal 8.
An optical fiber 18 for receiving the optical signal 8 sent by the optical fiber coupler 15 and transmitting the optical signal 8 to the objective lens 1.
In the embodiment of the application, the optical fiber 18 receives the optical signal 8 from the fiber coupler 15 and transmits it efficiently to the objective lens 1 of the measuring unit. The main function of the optical fiber 18 is to ensure that the loss of the optical signal 8 is minimized during the transmission of the signal from the input unit to the objective lens 1.
The embodiment of the application can precisely control and adjust the intensity and the focusing degree of the optical signal 8 through the cooperative work of the series of optical elements, so as to ensure that the optical signal 8 entering the objective lens 1 has proper optical characteristics. The quality and stability of the optical signal 8 are improved, and the accuracy of the measurement result is further improved. Furthermore, the use of optical fibers 18 reduces reliance on complex optical path alignment, making the overall system more reliable and easy to maintain.
On the basis of fig. 1, the present application also provides a schematic structural diagram of a blood flow velocity measurement device, as shown in fig. 3, the analysis unit includes a low noise amplifier 17 and a signal acquisition card 16, wherein:
The low noise amplifier 17 is configured to receive the electrical signal sent by the ultrasonic probe 7, amplify the electrical signal, and send the amplified electrical signal to the signal acquisition card 16.
In the embodiment of the application, the low-noise amplifier 17 is used for amplifying the weak electric signal received by the ultrasonic probe 7, suppressing noise and ensuring the definition and quality of the signal.
The input of the low noise amplifier 17 is connected to the ultrasound 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 as to select an appropriate gain according to the required signal strength. For example, during blood flow measurement, it may be desirable to adjust the gain to optimize the signal strength and prevent signal distortion due to excessive amplification.
The low noise amplifier 17 minimizes interference of external noise sources by employing a low noise amplifying circuit (e.g., using a high quality operational amplifier), and maintains the definition of signals. In order to reduce noise, appropriate power supply filters and shielding measures are often used.
The amplified electrical signal is output to the input of the signal acquisition card 16. At this stage, the electrical signal has been increased enough for further digitization.
The signal acquisition card 16 is configured to receive the electrical signal sent by the low noise amplifier 17, convert the electrical signal into a digital signal, and send the digital signal to the control unit.
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.
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 to a digital signal for subsequent processing. The present application uses a high resolution digital-to-analog converter (e.g., 12 bits or 16 bits) to ensure signal accuracy during blood flow rate measurements.
The sampling rate determines the accuracy and real-time of signal acquisition. For blood flow measurement, the change in signal needs to be captured quickly, so the sampling rate can be set higher. The sampling rate is selected depending on the measured frequency range and the accuracy requirements.
After analog-to-digital conversion, the digital signal is transmitted to the control unit via an appropriate interface (e.g., USB, PCIe, etc.).
The embodiment of the application can greatly improve the signal processing capacity of the measuring device through the design of the low noise amplifier 17 and the signal acquisition card 16, and ensure that the system can measure the blood flow rate more accurately and stably.
On the basis of the above fig. 2 and 3, the present application further provides a schematic structural diagram of a blood flow velocity measurement device, as shown in fig. 4, the control unit includes a function generator 20 and a processing module 19, wherein:
The function generator 20 is configured to receive the control instruction sent by the processing module 19, and control the hexagonal prism 6 to rotate according to the control instruction.
In the embodiment of the present application, the function generator 20 is one of the core components of the control unit, and is responsible for generating and outputting accurate control signals. These signals are used to adjust the operating parameters of other devices to ensure that the optical and acoustic paths are able to operate in a predetermined manner.
The function generator 20 receives control instructions from the processing module 19, generates periodic signals (such as sine waves, square waves, triangular waves, etc.), and transmits these signals to the rotation control motor of the hexagonal prism 6.
The rotation of the hexagonal prism 6 is precisely regulated by the signal generated by the control function generator 20. By varying the rotation angle of the hexagonal prism 6, the function generator 20 can influence the propagation direction of the optical signal 8 or the acoustic signal 9. The rotation angle of the hexagonal prism 6 is typically adjusted by the frequency, amplitude of the control signal.
The processing module 19 is configured to send a control instruction to the function generator 20, send a measurement instruction to the laser 10, receive a digital signal sent by the signal acquisition card 16, and perform analysis processing on the digital signal to obtain a blood flow velocity result.
In the embodiment of the present application, the processing module 19 is responsible for processing and analyzing the acquired data. The workflow of the system is controlled through interactions with other components. The processing module 19 sends instructions to the laser 10 and other devices via a communication interface (e.g., serial, parallel, or higher level bus interface) to control signal path adjustment during emission and collection of the optical signal 8.
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, outputting digitized signals.
The digital signals received by the processing module 19 are processed by a built-in algorithm, and finally the flow rate of the blood is calculated.
The processing module 19 feeds back the final calculated blood flow rate to the user via a display screen, console or other output device. The user can view the real-time blood flow rate data on the screen.
According to the embodiment of the application, the optical system and the ultrasonic system work more cooperatively by the design of the control unit, so that the whole measurement process is optimized. The application of the function generator 20 enables the optical system to be flexibly adjusted according to the requirements, ensures the adaptability under different measurement conditions, and the processing module 19 performs data processing and analysis efficiently.
The embodiment of the application also provides a blood flow velocity measuring method, as shown in fig. 5, comprising steps 501 to 505:
in step 501, the control input unit sends a first optical signal and a second optical signal at preset intervals, and the intensity of the first optical signal is consistent with that of the second optical signal.
In the embodiment of the application, a suitable laser is selected as a light source, and a helium-neon laser (with a wavelength of about 632.8 nm) or a diode laser is used as a common laser. The light source is selected in consideration of the stability and blood absorption characteristics of the light source.
The laser should be capable of emitting a stable, tunable optical signal and the laser intensity and frequency can be adjusted by the control unit.
The control unit precisely controls the output power of the laser through a dimming technology. Each emitted light signal should have the same intensity and frequency.
The optical signals output by the laser are modulated into the required waveforms and intensities by the modulating optical element, and the two optical signals are ensured to have the same light intensity.
The control unit will send two different light signals according to a preset time interval. For example, the first optical signal may be used as a reference signal and the second optical signal used for dynamic measurement, the precise control of the time interval may be achieved by a clock or frequency generator.
Step 502, obtaining a first electrical signal according to the first optical signal, and obtaining a second electrical signal according to the second optical signal.
In the embodiment of the application, the electric signal is obtained after the interaction of the sample and the optical signal. The intensity of the reflected light is closely related to the blood flow state, the absorption characteristics of blood, and the structure of blood vessels.
The resulting electrical signal is analog/digital converted into a digital signal that can be processed. A high precision a/D converter (analog to digital converter) can be used to ensure accurate acquisition of the signal.
The first electrical signal is obtained by the first optical signal in the same way as the second electrical signal is obtained by the second optical signal.
Step 503, obtaining an intensity value of the first electric signal, and obtaining a green elsen parameter of the first electric signal according to formula (1);
p1＝Γ1(T1)ηhμaF1(1)
In formula (1), p 1 is the intensity value of the first electrical signal, Γ 1 is the green eastern parameter of the first electrical signal, T 1 is the sample temperature value corresponding to the first electrical signal, η h is the thermal conversion efficiency, μ a is the absorption coefficient, and F 1 is the intensity value of the first optical signal.
Step 504, obtaining the intensity value of the second electric signal, and obtaining the green elsen parameter of the second electric signal according to formula (2);
p2＝Γ2(T2)ηhμaF2(2)
In formula (2), p 2 is the intensity value of the second electrical signal, Γ 2 is the green eastern parameter of the second electrical signal, T 2 is the sample temperature value corresponding to the second electrical signal, η h is the thermal conversion efficiency, μ a is the absorption coefficient, and F 2 is the intensity value of the second optical signal.
Step 505, obtaining a blood flow velocity result through a formula (3) according to the green elsen parameter of the first electric signal and the green elsen parameter of the second electric signal;
In formula (3), ΔΓ is the difference between the green's elsen parameter of the first electrical signal and the green's elsen parameter of the second electrical signal, μ a is the absorption coefficient, F 1 is the intensity of the first optical 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 constants, and v is the blood flow velocity result.
In order to reduce measurement errors, multiple samplings may be performed over a period of time. By calculating the average of the multiple measurements, the accuracy of the blood flow rate measurement can be improved.
The embodiment of the application calculates the Greenness parameters (Green-EISEN PARAMETER) by using the first optical signal and the second optical signal and combining the respective electric signal intensities, and calculates the blood flow velocity according to the parameters. A more accurate blood flow measurement can be provided.
The description of the apparatus embodiments above is similar to that of the method embodiments above, with similar advantageous effects as the method embodiments. For technical details not disclosed in the embodiments of the apparatus of the present application, please refer to the description of the embodiments of the method of the present application.
It should be noted that, in the embodiment of the present application, if the method is implemented in the form of a software functional module, and sold or used as a separate product, the method may also be stored in a computer readable storage medium. Based on such understanding, the technical solutions of the embodiments of the present application may be essentially or partly contributing to the related art, embodied in the form of a software product stored in a storage medium, including several instructions for causing an electronic device to execute all or part of the methods described in the embodiments of the present application. The storage medium includes various media capable of storing program codes, such as a usb disk, a removable hard disk, a Read Only Memory (ROM), a magnetic disk, or an optical disk. Thus, embodiments of the application are not limited to any specific combination of hardware and software.
It should be appreciated that reference throughout this specification to "one embodiment" or "an embodiment" or "some embodiments" means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment of the present application. Thus, the appearances of the phrases "in one embodiment" or "in an embodiment" or "in some embodiments" in various places throughout this specification are not necessarily referring to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined in any suitable manner in one or more embodiments. It should be understood that, in various embodiments of the present application, the sequence numbers of the foregoing processes do not mean the order of execution, and the order of execution of the processes should be determined by the functions and internal logic thereof, and should not constitute any limitation on the implementation process of the embodiments of the present application. The foregoing embodiment numbers of the present application are merely for the purpose of description, and do not represent the advantages or disadvantages of the embodiments. The foregoing description of various embodiments is intended to highlight differences between the various embodiments, which may be the same or similar to each other by reference, and is not repeated herein for the sake of brevity.
The term "and/or" is used herein to describe only one association relationship that associates objects, meaning that there may be three relationships, e.g., object a and/or object B, and that there may be three cases where object a alone exists, object a and object B together, and object B alone.
It should be noted that, in this document, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one does not exclude the presence of other like elements in a process, method, article, or apparatus that comprises the element.
In the several embodiments provided by the present application, it should be understood that the disclosed apparatus and method may be implemented in other ways. The above-described embodiments are merely illustrative, e.g., the division of the modules is merely a logical division of functionality, and may be implemented in other manners, e.g., multiple modules or components may be combined or integrated into another system, or some features may be omitted, or not performed. In addition, the various components shown or discussed may be coupled or directly coupled or communicatively coupled to each other via some interface, whether indirectly coupled or communicatively coupled to devices or modules, whether electrically, mechanically, or otherwise.
The modules described as separate components may or may not be physically separate, and components displayed as modules may or may not be physical modules, may be located in one place or distributed on a plurality of network units, and may select some or all of the modules according to actual needs to achieve the purpose of the embodiment.
In addition, each functional module in each embodiment of the present application may be integrated in one processing unit, or each module may be separately used as a unit, or two or more modules may be integrated in one unit, where the integrated modules may be implemented in hardware or in a form of hardware plus a software functional unit.
It will be appreciated by those of ordinary skill in the art that implementing all or part of the steps of the above method embodiments may be implemented by hardware associated with program instructions, where the above program may be stored in a computer readable storage medium, where the program when executed performs the steps comprising the above method embodiments, where the above storage medium includes various media that may store program code, such as a removable storage device, a Read Only Memory (ROM), a magnetic disk, or an optical disk.
Or the above-described integrated units of the application may be stored in a computer-readable storage medium if implemented in the form of software functional modules and sold or used as separate products. Based on such understanding, the technical solutions of the embodiments of the present application may be essentially or partly contributing to the related art, embodied in the form of a software product stored in a storage medium, including several instructions for causing an electronic device to execute all or part of the methods described in the embodiments of the present application. The storage medium includes various media capable of storing program codes such as a removable storage device, a ROM, a magnetic disk, or an optical disk.
The methods disclosed in the method embodiments provided by the application can be arbitrarily combined under the condition of no conflict to obtain a new method embodiment.
The features disclosed in the several product embodiments provided by the application can be combined arbitrarily under the condition of no conflict to obtain new product embodiments.
The features disclosed in the embodiments of the method or the apparatus provided by the application can be arbitrarily combined without conflict to obtain new embodiments of the method or the apparatus.
The foregoing is merely an embodiment of the present application, but the scope of the present application is not limited thereto, and any person skilled in the art can easily think about changes or substitutions within the technical scope of the present application, and the changes and substitutions are intended to be covered by the scope of the present application. Therefore, the protection scope of the present application shall be subject to the protection scope of the claims.
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| AU2013204040A1 (en) * | 2001-02-23 | 2013-05-02 | Marcio Marc Aurelio Martins Abreu | Noninvasive measurements of chemical substances |
| CN111297346A (en) * | 2020-03-05 | 2020-06-19 | 深圳大学 | A photoacoustic Doppler blood flow velocity and blood oxygen content measurement system and its measurement method |
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| US20140142404A1 (en) * | 2008-10-23 | 2014-05-22 | The Washington University | Single-cell label-free photoacoustic flowoxigraphy in vivo |
| WO2009055705A2 (en) * | 2007-10-25 | 2009-04-30 | Washington University In St. Louis | Confocal photoacoustic microscopy with optical lateral resolution |
| KR101736113B1 (en) * | 2016-03-16 | 2017-05-17 | 한국광기술원 | Convergence catheter and imaging processing system for cardiovascular diagnosis |
| CN114217090B (en) * | 2021-12-07 | 2022-09-23 | 中国科学院大学 | Sensor control device, ultrasonic velocimeter and ultrasonic velocimetry system |
| DE102023118223A1 (en) * | 2022-07-11 | 2024-01-11 | Kardion Gmbh | LASER DOPPLER VELOCIMETERY FLOW MEASUREMENT |
| CN117679076A (en) * | 2023-12-13 | 2024-03-12 | 英诺激光科技股份有限公司 | Multi-wavelength photoacoustic ultrasound bimodal microscopic imaging system and method |
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| AU2013204040A1 (en) * | 2001-02-23 | 2013-05-02 | Marcio Marc Aurelio Martins Abreu | Noninvasive measurements of chemical substances |
| CN111297346A (en) * | 2020-03-05 | 2020-06-19 | 深圳大学 | A photoacoustic Doppler blood flow velocity and blood oxygen content measurement system and its measurement method |
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