Blood flow parameter measurement method, apparatus, device, and storage medium

Abstract

The embodiment of the application provides a blood flow parameter measurement method, device, equipment and storage medium, and belongs to the field of medical instruments. The method comprises the following steps: acquiring a first channel signal and a second channel signal through a receiver, and acquiring the flow rate of a to-be-detected blood vessel according to the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the to-be-detected blood vessel, and the second channel signal is a signal emitted by another transmitter and reflected by the to-be-detected blood vessel; acquiring a first Doppler angle of actual work of a probe according to the relationship between the flow rate, the Doppler angle and the flow rate; adjusting the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, and then acquiring the blood flow parameter of the to-be-detected blood vessel. The blood flow parameter measurement method, device, equipment and storage medium provided by the embodiment have smaller measurement error.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and in particular to a method, apparatus, equipment and storage medium for measuring blood flow parameters. Background Technology

[0002] With the development of technology, medical testing methods can be used to obtain relevant parameters of the human body to help doctors diagnose various diseases. For example, Doppler blood flow detection equipment can be used to detect blood flow parameters.

[0003] Currently, the use of Doppler blood flow detection equipment to measure blood flow parameters on the body surface is widely used in clinical practice, and the detection results and ease of operation have been greatly improved. However, in actual use, the measurement results often have a certain degree of error, especially when medical staff do not operate according to standard procedures, or when the patient moves during long-term monitoring. The error in the measurement results will be greater, which reduces the reliability of the blood flow velocity measurement results and may even lead to misdiagnosis of the patient's condition by medical staff in severe cases. Summary of the Invention

[0004] In view of this, the present application provides a blood flow parameter measurement method, apparatus, device, and storage medium to solve at least one problem existing in the background art.

[0005] In a first aspect, one embodiment of this application provides a method for measuring blood flow parameters, applied to a Doppler blood flow detection device. The Doppler blood flow detection device includes a probe, the probe comprising two transmitters fixed in position to each other and a receiver; the two transmitters are respectively located on both sides of the receiver in the direction of blood flow in the blood vessel to be detected; the method includes:

[0006] The receiver acquires a first channel signal and a second channel signal, and obtains the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by another transmitter and reflected by the blood vessel to be detected.

[0007] Based on the flow velocity and the relationship between the Doppler angle and the flow velocity, the first Doppler angle at which the probe actually operates is obtained;

[0008] Based on the first Doppler angle, the spectral envelopes of the first channel signal and the second channel signal are adjusted to obtain the blood flow parameters of the blood vessel to be detected.

[0009] Optionally, the step of acquiring the first channel signal and the second channel signal through the receiver, and acquiring the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal, includes:

[0010] Based on the first channel signal and the second channel signal, obtain the spectral envelopes of the first channel signal and the second channel signal;

[0011] The first flow velocity and the second flow velocity are obtained based on the spectral envelopes of the first channel signal and the second channel signal, respectively.

[0012] Optionally, determining the first Doppler angle at which the probe actually operates, based on the flow velocity and the relationship between the Doppler angle and the flow velocity, includes:

[0013] The first Doppler angle at which the probe actually operates is determined based on the flow velocity, the second Doppler angle preset by the probe, and the positional relationship between the transmitter and the receiver.

[0014] Optionally, obtaining the first flow velocity and the second flow velocity based on the spectral envelopes of the first channel signal and the second channel signal respectively includes:

[0015] Based on the spectral envelopes of the first channel signal and the second channel signal, the peak values ​​of multiple periods of the first channel signal and the second channel signal are obtained;

[0016] The Raida criterion was used to remove outliers from multiple of the aforementioned peak values;

[0017] Calculate the average value of the remaining peak values ​​after removing outliers;

[0018] The first flow rate and the second flow rate are obtained based on the average value.

[0019] Optionally, determining the first Doppler angle at which the probe actually operates based on the flow velocity, the second Doppler angle preset by the probe, and the positional relationship between the transmitter and the receiver includes:

[0020] Calculate β based on the following expression:

[0021]

[0022] Where θ is the preset second Doppler angle, β is the deviation angle of the Doppler angle, (θ-β) and (θ+β) are the first Doppler angles in which the two transmitters in the probe actually work, and γ is the angle between the receiver and the blood flow direction.

[0023] Optionally, the step of adjusting the spectral envelopes of the first channel signal and the second channel signal based on the first Doppler angle to obtain the blood flow parameters of the vessel to be detected includes:

[0024] Adjust the peak values ​​of the spectral envelopes of the first channel signal and the second channel signal according to the first Doppler angle;

[0025] The adjusted spectral envelopes of the first channel signal and the second channel signal are overlapped to obtain a new spectral envelope;

[0026] Based on the new spectral envelope, the blood flow parameters of the blood vessel to be detected are obtained.

[0027] Secondly, embodiments of this application provide a blood flow parameter measuring device applied to a Doppler blood flow detection device. The Doppler blood flow detection device includes a probe, which includes two transmitters fixed in position to each other and a receiver. The two transmitters are respectively located on both sides of the receiver in the direction of blood flow in the blood vessel to be detected. The blood flow parameter measuring device includes:

[0028] The first acquisition module is used to acquire a first channel signal and a second channel signal through the receiver, and to acquire the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by another transmitter and reflected by the blood vessel to be detected;

[0029] The second acquisition module is used to acquire the first Doppler angle of the probe when it is actually working, based on the flow velocity and the relationship between the Doppler angle and the flow velocity.

[0030] The third acquisition module is used to adjust the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, thereby acquiring the blood flow parameters of the blood vessel to be detected.

[0031] Thirdly, embodiments of this application provide a Doppler blood flow detection device, comprising:

[0032] The blood flow parameter measuring device described above;

[0033] The probe includes two transmitters fixed in position to each other and a receiver; the two transmitters are respectively located on both sides of the receiver in the direction of flow of the blood vessel to be detected.

[0034] Fourthly, embodiments of this application provide a computing device, the computing device comprising: a memory, a communication bus, and a processor, wherein:

[0035] The memory is used to store the blood flow parameter measurement method program;

[0036] The communication bus is used to realize the connection and communication between the memory and the processor;

[0037] The processor is used to execute a blood flow parameter measurement method program to implement the steps of any of the methods described above.

[0038] Fifthly, embodiments of this application provide a computer-readable storage medium storing an executable program, which, when executed by a processor, implements the steps of any of the methods described above.

[0039] The blood flow parameter measurement method, apparatus, device, and storage medium provided in this application embodiment include: acquiring a first channel signal and a second channel signal through the receiver, and acquiring the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by another transmitter and reflected by the blood vessel to be detected; acquiring a first Doppler angle of actual operation of the probe based on the flow velocity and the relationship between the Doppler angle and the flow velocity; adjusting the spectral envelope of the first channel signal and the second channel signal based on the first Doppler angle, thereby acquiring the blood flow parameters of the blood vessel to be detected. By placing the transmitter and receiver separately and positioning the receiver between the two transmitters, the receiving distance of the receiver can be reduced, thereby reducing measurement error. Therefore, the blood flow parameter measurement method, apparatus, device, and storage medium provided in this embodiment have a smaller measurement error.

[0040] Additional aspects and advantages of this application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of this application. Attached Figure Description

[0041] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0042] Figure 1 This is a structural block diagram of a Doppler blood flow detection device provided in an embodiment of this application;

[0043] Figure 2 Schematic diagram of the operating positions of the transmitter and receiver in a Doppler blood flow detection device provided in an embodiment of this application. Figure 1 ;

[0044] Figure 3 Schematic diagram of the operating positions of the transmitter and receiver in a Doppler blood flow detection device provided in an embodiment of this application. Figure 2 ;

[0045] Figure 4A schematic flowchart of a blood flow parameter measurement method provided in an embodiment of this application;

[0046] Figure 5 This is a flowchart of spectrum waveform processing in a specific application;

[0047] Figure 6 A detailed flowchart illustrating a blood flow parameter measurement method provided in an embodiment of this application;

[0048] Figure 7 This is a schematic diagram of the structure of a blood flow parameter measuring device provided in an embodiment of this application;

[0049] Figure 8 This is a schematic diagram of the structure of a computing device provided in an embodiment of this application.

[0050] Explanation of reference numerals in the attached figures:

[0051] 10. Probe; 11. First ultrasonic transmitting chip; 12. Second ultrasonic transmitting chip; 13. Ultrasonic receiving chip; 20. Main module of the device; 21. Ultrasonic transmitting circuit; 22. Ultrasonic receiving circuit; 23. Analog-to-digital converter; 24. Processing unit; 25. Display; 26. Communication interface; 27. Power supply system; 700. Blood flow parameter measuring device; 701. First acquisition module; 702. Second acquisition module; 703. Third acquisition module; 800. Computing device; 801. Memory; 802. Communication bus; 803. Processor; 804. Input device; 805. Output device; 806. External communication interface. Detailed Implementation

[0052] Exemplary embodiments of the present application will now be described in more detail with reference to the accompanying drawings. While exemplary embodiments of the present application are shown in the drawings, it should be understood that the present application may be implemented in various forms and should not be limited to the specific embodiments set forth herein. Rather, these embodiments are provided to enable a more thorough understanding of the present application and to fully convey the scope of the disclosure of the present application to those skilled in the art.

[0053] The following description provides numerous specific details to offer a more thorough understanding of this application. However, it will be apparent to those skilled in the art that this application can be practiced without one or more of these details. In other instances, to avoid confusion with this application, some technical features well-known in the art have not been described; that is, not all features of actual embodiments are described herein, nor are well-known functions and structures described in detail.

[0054] To fully understand this application, detailed steps and structures will be presented in the following description to illustrate the technical solution of this application. Preferred embodiments of this application are described in detail below; however, in addition to these detailed descriptions, this application may have other implementation methods.

[0055] Example 1

[0056] This application provides a method for measuring blood flow parameters, applied to a Doppler blood flow detection device. First, please refer to... Figure 1 , Figure 1 The structure of a Doppler blood flow detection device according to an embodiment of this application is shown. As shown, the Doppler blood flow detection device includes a probe 10 and a main device module 20. Specifically, the probe 10 may include two transmitters and one receiver. The main device module 20 may include an ultrasonic transmitting circuit 21, an ultrasonic receiving circuit 22, an analog-to-digital converter 23, and a processing unit 24. The transmitters are connected to the ultrasonic transmitting circuit 21 and then to the processing unit 24, and can transmit signals according to the instructions of the processing unit 24. The receivers are connected to the ultrasonic receiving circuit 22 and the analog-to-digital converter 23, thereby transmitting the received signals to the processing unit 24 for processing.

[0057] Specifically, the transmitter can be a first ultrasonic transmitting crystal 11 (abbreviated as T1) and a second ultrasonic transmitting crystal 12 (abbreviated as T2), and the receiver can be an ultrasonic receiving crystal 13 (abbreviated as R). The frequency range of the probe 10 can be 2MHz-8MHz.

[0058] Specifically, the ultrasonic receiving circuit 22 may include a filter and a signal demodulator (neither shown in the figure). The filter is used to filter the received signal, and the signal demodulator is used to demodulate the filtered signal.

[0059] Specifically, the main module 20 of the device may further include a display 25, a communication interface 26, and a power supply system 27. The display 25 is used to display graphics such as the received ultrasound signal spectrum and is an output component of the Doppler blood flow detection device. The communication interface 26 is used to share data with other devices or upload data to a server. Specifically, the communication interface 26 can be a commonly used communication hardware interface such as USB / UART / Ethernet / Bluetooth / WIFI / CAN, and this application does not impose specific limitations on it. The power supply system 27 is used to provide the electrical energy required for the device to operate.

[0060] Specifically, the device may also include a storage unit (not shown in the figure) connected to the processing unit 24 to store the received detection results, as well as intermediate quantities and algorithm programs during the calculation process.

[0061] Specifically, the device may also include an audio amplifier and a speaker connected to the audio amplifier. The speaker can be used to output audio of the results determined by the processing unit 24 and to output audio of information that needs to be reminded to the user.

[0062] Specifically, the device may further include an operation command input component, including, but not limited to, at least one of the following: a keyboard, buttons, a voice input component, and a touch screen. It is understood that other components capable of enabling command input are included within the aforementioned meaning of the operation command input component.

[0063] Specifically, the display 25 may be an LCD screen, which is understandable, or it may be other output components. Other devices that can realize signal output are also included in the meaning of this application.

[0064] The blood flow parameter measurement method provided in this application is applied to a Doppler blood flow detection device. The Doppler blood flow detection device includes a probe 10, see [link to relevant documentation]. Figure 2 and Figure 3 The probe 10 includes two transmitters and one receiver fixed in position to each other; the two transmitters are respectively located on opposite sides of the receiver in the direction of flow of the blood vessel to be detected. See also Figure 4 The method for measuring this blood flow parameter includes:

[0065] Step 401: Obtain the first channel signal and the second channel signal transmitted by the two transmitters received by the receiver, and obtain the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal;

[0066] Step 402: Based on the flow velocity and the relationship between the Doppler angle and the flow velocity, obtain the first Doppler angle of the probe 10 during actual operation;

[0067] Step 403: Adjust the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, and then obtain the blood flow parameters of the blood vessel to be detected.

[0068] Specifically, such as Figure 2 and Figure 3 As shown, the positions of the two transmitters and one receiver are fixed to each other, forming a trapezoid, with the receiver on the upper base and the two transmitters on the legs. This arrangement, with the receiver positioned between the two transmitters, ensures that both transmitters have Doppler information windows. The sound beams from both transmitters are refracted and scattered, and signals are transmitted to the receiver. More specifically, the two transmitters and one receiver can form an isosceles trapezoid, which simplifies calculations. Both transmitters use the same driving source, ensuring that the frequencies and phases of the transmissions from T1 and T2 are completely synchronized.

[0069] Specifically, the Doppler blood flow detection device is designed with the base angles of the isosceles trapezoid all at angle α, and the preset second Doppler angle is θ. However, in actual use, the degree of contact between the probe 10 and the human body, as well as the positional relationship between blood vessels and body surface tissues (referred to as tissues, such as skin), may cause deviations in the Doppler angle. For example... Figure 3 As shown, the blood vessels are tilted relative to the body surface tissue (the degree of tilt is exaggerated appropriately in the attached diagram for clarity), resulting in a Doppler deviation angle β, which leads to measurement errors. β is the deviation angle between the actual Doppler angle during detection and α, and can also be simply referred to as the tilt angle. To eliminate this error, we designed a dual-emitter co-source technology, using two co-source emitters and one receiver. Since the emission directions of T1 and T2 are opposite, according to the Doppler principle, the resulting frequency offsets are positive and negative, respectively. On the receiver R, there are positive and negative Doppler waveforms. The positive and negative Doppler waveforms can be calculated to obtain the corresponding blood flow parameters. Due to the existence of the deviation angle β, the calculated blood flow parameters have errors, but the error directions are opposite for the positive and negative directions, which can be used to reduce the error.

[0070] We conducted an error analysis based on the fact that the sensor could be installed correctly, but there was a deviation between the blood vessel position and the skin surface.

[0071] Design data:

[0072] The base angle of the isosceles trapezoid is α = 30°, and the preset Doppler angle is θ = 60°;

[0073] If the deviation angle β = 5°, then the Doppler angle of T1 is θ1 = 60° + 5° = 65°, and the Doppler angle of T2 is...

[0074] θ2 = 55°;

[0075] For simplicity in calculation, let Δf*c / 2f = A, where Δf represents the frequency difference obtained by measuring blood flow velocity using a Doppler blood flow detection device, c represents the propagation speed of the signal emitted by the transmitting chip, and f is the frequency of the signal emitted by the transmitting chip. Specifically, c can be the speed of sound propagation in human tissue, typically taken as 1570 m / s or 1540 m / s depending on the type of tissue.

[0076] The positive actual value V1 = Δf*c / (2f*cos(θ1)) = A / cos(θ1) = A / cos65° = 2.3663A;

[0077] The theoretical flow velocity measurement value V0 = Δf*c / (2f*cosθ) = A / cosθ = A / cos60° = A / 0.5 = 2A;

[0078] Error: (V1-V0) / V0=(2.3663A-2A) / 2A=18.3%.

[0079] Take the absolute value of the reversed value and then average it with the forward value.

[0080] Actual reverse flow velocity:

[0081] V2=Δf*c / (2f*cos(θ2))=A / cos(θ2)=A / cos55°=1.7434A;

[0082] (V1+V2) / 2=(2.3663A+1.7434A=) / 22.0548;

[0083] Error: (2.0548-2) / 2 = 2.74%;

[0084] The error decreased from 18.3% to 2.74%.

[0085] Therefore, the blood flow parameter measurement method of this application embodiment can effectively reduce the measurement error caused by the positional deviation of the probe 10 or the positional deviation between the blood vessel and the body surface tissue by setting two co-source transmitting chips on both sides of the flow direction of a receiving chip in the blood vessel to be detected.

[0086] The transmission path of the signals emitted by the two transmitters is as follows: Assume the emitted sound wave makes an angle θ with the direction of blood flow, i.e., the emission angle is θ. For the stationary transmitter T1, the red blood cell acts as a receiver moving at velocity v. When the red blood cell scatters the sound energy, and the receiver R receives it, the cell in the blood flow is equivalent to a secondary sound source moving at velocity v relative to the stationary receiver R. Assuming the angle between the axis of receiver R and the direction of blood flow is γ, the emission angle of the cell in the blood flow is γ. The signal emitted by the transmitter travels from the transmitter to the cell in the blood flow, and then to the receiver. This transmission path can be considered as constructing a sound wave transmission channel; since there are two transmitters, this is called the first channel and the second channel.

[0087] To distinguish between the actual working angle of probe 10 and the preset Doppler angle, the two are referred to as the first Doppler angle and the second Doppler angle, respectively.

[0088] Understandably, the flow velocity detected by a Doppler blood flow detection device is related to the Doppler angle. For example, the flow velocity obtained by detecting the Doppler frequency shift using the reflection method can be obtained through the following expression (1):

[0089]

[0090] Among them, f DLet f0 be the frequency of the sound wave emitted by the sound source, v be the blood flow velocity, θ be the angle between the emitted sound wave and the direction of blood flow, and γ be the angle between the receiver's R-axis and the direction of blood flow. From expression (1), it can be seen that the flow velocity v and the Doppler angle θ are correlated. Therefore, given the flow velocity, the first Doppler angle can be calculated.

[0091] In this embodiment, placing the receiver between the two transmitters reduces the receiver's receiving distance, further minimizing measurement errors. Furthermore, since the transmitter and receiver are separated, the probe 10 can be made narrower, shortening the distance between the probe 10 and the blood vessel during operation, further reducing errors. Additionally, because the receiver can receive signals from both transmitters, one receiver can be eliminated, reducing costs.

[0092] In some embodiments, acquiring a first channel signal and a second channel signal through the receiver, and acquiring the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal, includes:

[0093] Based on the first channel signal and the second channel signal, obtain the spectral envelopes of the first channel signal and the second channel signal;

[0094] The first flow velocity and the second flow velocity are obtained based on the spectral envelopes of the first channel signal and the second channel signal, respectively.

[0095] Specifically, the ultrasound spectra of the first channel signal and the second channel signal can be obtained respectively. Then, the power spectral density signal is obtained by fast Fourier transform (FFT). Next, the power spectral density signal is integrated to obtain the positive maximum frequency point and the negative maximum frequency point in the column signal of the ultrasound spectra corresponding to the power spectral density signal. The positive maximum frequency point and the negative maximum frequency point corresponding to each column signal in the ultrasound spectra are connected to obtain the waveform envelope corresponding to the ultrasound spectra, that is, the spectral envelope.

[0096] Based on the spectral envelope, the velocity-time integral (VTI) of each stroke is obtained, and then the flow velocity of the vessel to be detected is obtained.

[0097] In some embodiments, determining the first Doppler angle at which the probe 10 actually operates, based on the flow velocity and the relationship between the Doppler angle and the flow velocity, includes:

[0098] The first Doppler angle at which the probe 10 actually operates is determined based on the flow rate, the preset second Doppler angle of the probe 10, and the positional relationship between the transmitter and the receiver.

[0099] Understandably, during the measurement process, the presence of a deviation angle β will cause the actual operating first Doppler angle to differ from the preset second Doppler angle. Furthermore, since the receiver has transmitters on both sides of the flow direction of the blood vessel being detected, the first and second channel signals emitted by the two transmitters will react differently due to the deviation angle β; that is, the actual operating Doppler angles in the two channels will change in different directions, with one increasing and the other decreasing. Therefore, the actual operating first Doppler angle of the probe 10 can be determined based on this relationship.

[0100] Specifically, determining the first Doppler angle at which the probe 10 actually operates, based on the flow velocity, the preset second Doppler angle of the probe 10, and the positional relationship between the transmitter and the receiver, includes:

[0101] Calculate β according to the following expression (2):

[0102]

[0103] Where v1 is the flow velocity of the first channel and v2 is the flow velocity of the second channel, the flow velocities of the two channels can be obtained by the spectral envelope or frequency offset method. (θ-β) and (θ+β) are the first Doppler angles between the two transmitters in the probe 10 when they are actually operating.

[0104] In some embodiments, obtaining the first flow velocity and the second flow velocity based on the spectral envelopes of the first channel signal and the second channel signal respectively includes:

[0105] Based on the spectral envelopes of the first channel signal and the second channel signal, the peak values ​​of multiple periods of the first channel signal and the second channel signal are obtained;

[0106] The Raida criterion was used to remove outliers from multiple of the aforementioned peak values;

[0107] Calculate the average value of the remaining peak values ​​after removing outliers;

[0108] The first flow rate and the second flow rate are obtained based on the average value.

[0109] Specifically, such as Figure 5As shown, the method may include obtaining multiple peak values ​​of the first channel signal based on its spectral envelope and removing outliers using the Raida criterion. Then, an average value is calculated on the remaining peak values ​​after outlier removal to obtain a first average value, which is determined as the first peak value. Similarly, multiple peak values ​​of the second channel signal are obtained based on its spectral envelope and outliers are removed using the Raida criterion. Then, an average value is calculated on the remaining peak values ​​after outlier removal to obtain a second average value, which is determined as the second peak value. The first and second peak values ​​can be found in [reference needed]. Figure 5 (a).

[0110] Please continue to refer to this. Figure 5 In a specific application, the waveform of the first channel signal can be inverted first. The data of inverted channel 1 is as follows: Figure 5 As shown in (b).

[0111] To more accurately determine the peak values ​​of each spectral envelope, five periods can be selected, and the peak value of each of these five periods can be calculated, resulting in five peak values. Next, the Raida criterion is used to remove outliers from these five peak values. However, this step only means that the Raida criterion has been used to remove outliers; it does not necessarily mean that any outliers will be removed. In other words, if there are no outliers among the five peak values, all five peak values ​​are retained. Next, the average value of the remaining peak values ​​after outlier removal is calculated. Again, this step only means that the average value has been calculated; if only one peak value remains after outlier removal, then the average value represents that peak value.

[0112] Furthermore, the above steps can be performed on both the first channel signal and the second channel signal to obtain average values ​​respectively, and these average values ​​can be determined as the first peak value Vm1 and the second peak value Vm2. Since Vm1 and Vm2 are easier to obtain, the above expression (2) can be modified as follows:

[0113]

[0114] β can be calculated based on the above expression (3).

[0115] In some embodiments, adjusting the spectral envelopes of the first channel signal and the second channel signal based on the first Doppler angle to obtain the blood flow parameters of the vessel to be detected includes:

[0116] Adjust the peak values ​​of the spectral envelopes of the first channel signal and the second channel signal according to the first Doppler angle;

[0117] The adjusted spectral envelopes of the first channel signal and the second channel signal are overlapped to obtain a new spectral envelope;

[0118] Based on the new spectral envelope, the blood flow parameters of the blood vessel to be detected are obtained.

[0119] That is, the data of channel 1 and channel 2 can be adjusted accordingly based on β, and this step can also be called correction.

[0120] Specifically, adjusting the first channel signal and the second channel signal according to the determined relationship can include adjusting the first channel signal and the second channel signal according to the following formula:

[0121] Vm1'=Vm1*cosθ / cos(θ-β) (4)

[0122] Vm2'=Vm2*cosθcos(θ+β) (5)

[0123] Wherein, Vm1 is the first peak value, Vm2 is the second peak value, Vm1' is the peak value corresponding to the adjusted first channel signal, Vm2' is the peak value corresponding to the adjusted second channel signal, α is the set Doppler angle, r is the deviation angle between the actual Doppler angle during detection and α; (θ-β) and (θ+β) are the actual Doppler angles during detection in T1 and T2, respectively.

[0124] In practice, the first and second channel signals are scaled proportionally according to a defined relationship to obtain the corrected spectral envelope. Please refer to [reference needed]. Figure 5 (c) The two spectral waveforms after correction are highly similar.

[0125] Specifically, determining the blood flow parameter measurement value based on the adjusted first channel signal and the adjusted second channel signal may include: overlaying the adjusted first channel signal and the adjusted second channel signal to obtain the overlaid spectrum waveform; and determining the blood flow parameter measurement value based on the overlaid spectrum waveform.

[0126] The superimposed spectral waveform can be referenced. Figure 5 (d) The overlapped spectral waveform further fuses the detection results of T1 and T2, thereby neutralizing the angular errors between the two. Determining blood flow parameter measurements based on the overlapped spectral waveform can be performed using existing techniques in the field, and this application does not specifically limit this method.

[0127] Understandably, the blood flow parameter measurements obtained in this way are closer to the actual blood flow parameters, and the errors caused by the inconsistency between the angle between the probe 10 and the blood vessel to be detected in the actual measurement and the set Doppler angle are basically eliminated, thereby improving the accuracy of the blood flow parameter measurements.

[0128] To further understand the blood flow parameter measurement method of this application embodiment, a more specific embodiment is described below, such as... Figure 6 As shown, the method includes:

[0129] Step 601: Acquire the ultrasound waves from channel 1. That is, acquire them through a receiver. Channel 1 is the same as the first channel.

[0130] Step 602: Acquire the ultrasound waves from channel 2. This is done via a receiver. Since transmitter 1 and transmitter 2 use the same drive source, their emitted frequencies and phases are completely identical. Except for the emission angle, all other parameters are the same, allowing the calculation of the Doppler angle deviation. Channel 2 is the same as the second channel.

[0131] Step 603: Ultrasonic filtering of channel 1. This involves digital filtering using a filter to remove interfering signals.

[0132] Step 604: Ultrasonic filtering of channel 2. This involves digital filtering using a filter to remove interfering signals.

[0133] Step 605: Perform an FFT on the ultrasound signal from channel 1. This involves converting the spectrogram into a power spectral density signal.

[0134] Step 606: Perform an FFT on the ultrasound signal from channel 2. This involves converting the spectrogram into a power spectral density signal.

[0135] Step 607: Obtain the spectral envelope of the ultrasound waves from channel 1. Integrate the power spectral density signal to obtain the forward and reverse maximum frequency points in the column signals of the ultrasound spectrum corresponding to the power spectral density signal. Connect the forward and reverse maximum frequency points corresponding to each column signal in the ultrasound spectrum to obtain the waveform envelope corresponding to the ultrasound spectrum, i.e., the spectral envelope. Further, the flow velocity in the blood vessels measured by channel 1 can be obtained based on the spectral envelope.

[0136] Step 608: Obtain the spectral envelope of the ultrasound waves from channel 2. Integrate the power spectral density signal to obtain the forward and reverse maximum frequency points in the column signals of the ultrasound spectrum corresponding to the power spectral density signal. Connect the forward and reverse maximum frequency points corresponding to each column signal in the ultrasound spectrum to obtain the waveform envelope corresponding to the ultrasound spectrum, i.e., the spectral envelope. Further, the flow velocity in the blood vessels measured by channel 2 can be obtained based on the spectral envelope.

[0137] Step 609: Obtain the deviation angle β. Calculate the deviation angle β based on the flow velocities of the two channels.

[0138] Step 610: Correct the spectral envelope according to the deviation angle β, that is, correct the spectral envelopes of channel 1 and channel 2 respectively.

[0139] Step 611: Obtain blood flow parameters. Obtain blood flow parameters based on the corrected spectral envelope.

[0140] Example 2

[0141] This embodiment provides a blood flow parameter measuring device 700, which is applied to Doppler blood flow detection equipment, such as... Figure 7 As shown, the Doppler blood flow detection device includes a probe 10, which includes two transmitters and a receiver fixed in position to each other; the two transmitters are respectively located on both sides of the receiver in the direction of blood flow in the blood vessel to be detected; the blood flow parameter measuring device 700 includes:

[0142] The first acquisition module 701 is used to acquire a first channel signal and a second channel signal through the receiver, and to acquire the flow velocity of the blood vessel to be detected based on the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by another transmitter and reflected by the blood vessel to be detected;

[0143] The second acquisition module 702 is used to acquire the first Doppler angle of the probe 10 when it is actually working, based on the flow velocity and the relationship between the Doppler angle and the flow velocity.

[0144] The third acquisition module 703 is used to adjust the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, thereby acquiring the blood flow parameters of the blood vessel to be detected.

[0145] Specifically, such as Figure 2 and Figure 3 As shown, the positions of the two transmitters and one receiver are fixed to each other, forming a trapezoid, with the receiver on the upper base and the two transmitters on the legs. This arrangement, with the receiver positioned between the two transmitters, ensures that both transmitters have Doppler information windows. The sound beams from both transmitters are refracted and scattered, and signals are transmitted to the receiver. More specifically, the two transmitters and one receiver can form an isosceles trapezoid, which simplifies calculations. Both transmitters use the same driving source, ensuring that the frequencies and phases of the transmissions from T1 and T2 are completely synchronized.

[0146] Specifically, the Doppler blood flow detection device is designed with the base angles of the isosceles trapezoid all at angle α, and the preset second Doppler angle is θ. However, in actual use, the degree of contact between the probe 10 and the human body, as well as the positional relationship between the blood vessels and the body surface tissues (e.g., skin), may cause deviations in the Doppler angle. For example... Figure 3 As shown, the blood vessels are tilted relative to the body surface tissue (the degree of tilt is exaggerated appropriately in the attached diagram for clarity), resulting in a Doppler deviation angle β, which leads to measurement errors. β is the deviation angle between the actual Doppler angle during detection and α, and can also be simply referred to as the tilt angle. To eliminate this error, we designed a dual-emitter co-source technology, using two co-source emitters and one receiver. Since the emission directions of T1 and T2 are opposite, according to the Doppler principle, the resulting frequency offsets are positive and negative, respectively. On the receiver R, there are positive and negative Doppler waveforms. The positive and negative Doppler waveforms can be calculated to obtain the corresponding blood flow parameters. Due to the existence of the deviation angle β, the calculated blood flow parameters have errors, but the error directions are opposite for the positive and negative directions, which can be used to reduce the error.

[0147] We performed error analysis even when the sensor was installed correctly, but there was a deviation between the blood vessel position and the skin surface, as shown in the example above.

[0148] Therefore, the blood flow parameter measuring device 700 of this application embodiment can effectively reduce the measurement error caused by the positional deviation of the probe 10 or the positional deviation between the blood vessel and the body surface tissue by setting two co-source transmitting chips on both sides of the flow direction of the blood vessel to be detected.

[0149] The transmission path of the signals emitted by the two transmitters is as follows: Assume the emitted sound wave makes an angle θ with the direction of blood flow, i.e., the emission angle is θ. For the stationary transmitter T1, the red blood cell acts as a receiver moving at velocity v. When the red blood cell scatters the sound energy, and the receiver R receives it, the cell in the blood flow is equivalent to a secondary sound source moving at velocity v relative to the stationary receiver R. Assuming the angle between the axis of receiver R and the direction of blood flow is γ, the emission angle of the cell in the blood flow is γ. The signal emitted by the transmitter travels from the transmitter to the cell in the blood flow, and then to the receiver. This transmission path can be considered as constructing a sound wave transmission channel; since there are two transmitters, this is called the first channel and the second channel.

[0150] To distinguish between the actual working angle of probe 10 and the preset Doppler angle, the two are referred to as the first Doppler angle and the second Doppler angle, respectively.

[0151] Understandably, the flow velocity detected by a Doppler blood flow detection device is related to the Doppler angle. For example, the flow velocity can be obtained by using the principle of Doppler frequency shift detection through reflection, as shown in expression (1).

[0152] In this embodiment, placing the receiver between the two transmitters reduces the receiver's receiving distance, further minimizing measurement errors. Furthermore, since the transmitter and receiver are separated, the probe 10 can be made narrower, shortening the distance between the probe 10 and the blood vessel during operation, further reducing errors. Additionally, because the receiver can receive signals from both transmitters, one receiver can be eliminated, reducing costs.

[0153] In some embodiments, the first acquisition module 701 is specifically used for:

[0154] Based on the first channel signal and the second channel signal, obtain the spectral envelopes of the first channel signal and the second channel signal;

[0155] The first flow velocity and the second flow velocity are obtained based on the spectral envelopes of the first channel signal and the second channel signal, respectively.

[0156] Specifically, the ultrasound spectra of the first channel signal and the second channel signal can be obtained respectively. Then, the power spectral density signal is obtained by fast Fourier transform (FFT). Next, the power spectral density signal is integrated to obtain the positive maximum frequency point and the negative maximum frequency point in the column signal of the ultrasound spectra corresponding to the power spectral density signal. The positive maximum frequency point and the negative maximum frequency point corresponding to each column signal in the ultrasound spectra are connected to obtain the waveform envelope corresponding to the ultrasound spectra, that is, the spectral envelope.

[0157] Based on the spectral envelope, the velocity-time integral (VTI) of each stroke is obtained, and then the flow velocity of the vessel to be detected is obtained.

[0158] In some embodiments, the second acquisition module 702 is specifically used for:

[0159] The first Doppler angle at which the probe 10 actually operates is determined based on the flow rate, the preset second Doppler angle of the probe 10, and the positional relationship between the transmitter and the receiver.

[0160] Understandably, during the measurement process, the presence of a deviation angle β will cause the actual operating first Doppler angle to differ from the preset second Doppler angle. Furthermore, since the receiver has transmitters on both sides of the flow direction of the blood vessel being detected, the first and second channel signals emitted by the two transmitters will react differently due to the deviation angle β; that is, the actual operating Doppler angles in the two channels will change in different directions, with one increasing and the other decreasing. Therefore, the actual operating first Doppler angle of the probe 10 can be determined based on this relationship.

[0161] Specifically, the second acquisition module 702 can also be used for:

[0162] Calculate β according to expression (2).

[0163] In some embodiments, the first acquisition module 701 can also be used for:

[0164] Based on the spectral envelopes of the first channel signal and the second channel signal, the peak values ​​of multiple periods of the first channel signal and the second channel signal are obtained;

[0165] The Raida criterion was used to remove outliers from multiple of the aforementioned peak values;

[0166] Calculate the average value of the remaining peak values ​​after removing outliers;

[0167] The first flow rate and the second flow rate are obtained based on the average value.

[0168] Specifically, such as Figure 5 As shown, the method may include obtaining multiple peak values ​​of the first channel signal based on the spectral envelope of the first channel signal and removing outliers using the Laida criterion; then calculating the average value of the remaining peak values ​​after outlier removal to obtain a first average value, and determining the first average value as the first peak value. Similarly, obtaining multiple peak values ​​of the second channel signal based on the spectral envelope of the second channel signal and removing outliers using the Laida criterion; then calculating the average value of the remaining peak values ​​after outlier removal to obtain a second average value, and determining the second average value as the second peak value.

[0169] Please continue to refer to this. Figure 5 In a specific application, the waveform of the first channel signal can be inverted first. The data of inverted channel 1 is as follows: Figure 5 As shown in (b).

[0170] To more accurately determine the peak values ​​of each spectral envelope, five periods can be selected, and the peak value of each of these five periods can be calculated, resulting in five peak values. Next, the Raida criterion is used to remove outliers from these five peak values. However, this step only means that the Raida criterion has been used to remove outliers; it does not necessarily mean that any outliers will be removed. In other words, if there are no outliers among the five peak values, all five peak values ​​are retained. Next, the average value of the remaining peak values ​​after outlier removal is calculated. Again, this step only means that the average value has been calculated; if only one peak value remains after outlier removal, then the average value represents that peak value.

[0171] Furthermore, the above steps can be performed on both the first channel signal and the second channel signal to obtain average values ​​respectively, and the respective average values ​​can be determined as the first peak value Vm1 and the second peak value Vm2. Since Vm1 and Vm2 are easier to obtain, the above expression (2) can be modified into expression (3); β can be calculated according to the above expression (3).

[0172] In some embodiments, the third acquisition module 703 is specifically used for:

[0173] Adjust the peak values ​​of the spectral envelopes of the first channel signal and the second channel signal according to the first Doppler angle;

[0174] The adjusted spectral envelopes of the first channel signal and the second channel signal are overlapped to obtain a new spectral envelope;

[0175] Based on the new spectral envelope, the blood flow parameters of the blood vessel to be detected are obtained.

[0176] That is, the data of channel 1 and channel 2 can be adjusted accordingly based on β, and this step can also be called correction.

[0177] Specifically, adjusting the first channel signal and the second channel signal according to the determined relationship can include: adjusting the first channel signal and the second channel signal according to expressions (4) and (5):

[0178] In practice, the first and second channel signals are scaled proportionally according to a defined relationship to obtain the corrected spectral envelope. Please refer to [reference needed]. Figure 5 (c) The two spectral waveforms after correction are highly similar.

[0179] Specifically, determining the blood flow parameter measurement value based on the adjusted first channel signal and the adjusted second channel signal may include: overlaying the adjusted first channel signal and the adjusted second channel signal to obtain the overlaid spectrum waveform; and determining the blood flow parameter measurement value based on the overlaid spectrum waveform.

[0180] The superimposed spectral waveform can be referenced. Figure 5 (d) The overlapped spectral waveform further fuses the detection results of T1 and T2, thereby neutralizing the angular errors between the two. Determining blood flow parameter measurements based on the overlapped spectral waveform can be performed using existing techniques in the field, and this application does not specifically limit this method.

[0181] Understandably, the blood flow parameter measurements obtained in this way are closer to the actual blood flow parameters, and the errors caused by the inconsistency between the angle between the probe 10 and the blood vessel to be detected in the actual measurement and the set Doppler angle are basically eliminated, thereby improving the accuracy of the blood flow parameter measurements.

[0182] The modules included in this embodiment can be implemented using a processor in a computer; alternatively, they can be implemented using logic circuits in a computer. The processor can be a general-purpose processor, a digital signal processor (DSP), a field-programmable gate array (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor can be a central processing unit (CPU), a microprocessor (MPU), or any other conventional processor.

[0183] The description of the apparatus embodiments above is similar to that of the method embodiments above, and has similar beneficial effects. For technical details not disclosed in the apparatus of this embodiment, please refer to the description of the method embodiments in this invention for understanding.

[0184] Example 3

[0185] This embodiment provides a Doppler blood flow detection device, such as... Figure 1 As shown, the device includes:

[0186] The blood flow parameter measuring device 700 described in Example 2;

[0187] The probe 10 includes two transmitters fixed in position to each other and a receiver; the two transmitters are respectively located on both sides of the receiver in the direction of flow of the blood vessel to be detected. The probe 10 is the same as the probe 10 described in Embodiment 1; for its specific structure, please refer to [reference needed]. Figure 1

[0188] The description of the Doppler blood flow detection device embodiments above is similar to the description of the method embodiments above, and has similar beneficial effects. For technical details not disclosed in the Doppler blood flow detection device of this embodiment, please refer to the description of the method embodiments in this invention for understanding.

[0189] Example 4

[0190] This embodiment provides a computing device 800, such as... Figure 8 As shown, the computing device 800 includes: a memory 801, a communication bus 802, and a processor 803, wherein:

[0191] The memory 801 is used to store the blood flow parameter measurement method program;

[0192] The communication bus 802 is used to realize the connection and communication between the memory 801 and the processor 803;

[0193] The processor 803 is used to execute a blood flow parameter measurement method program to implement the steps of the method described in Embodiment 1.

[0194] The type or structure of the memory 801 can be found in the storage medium section below, and will not be repeated here.

[0195] The processor 803 can be a general-purpose processor, a digital signal processor (DSP), a field-programmable gate array (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor can be a central processing unit (CPU), a microprocessor (MPU), or any other conventional processor.

[0196] In some embodiments, the computing device 800 may further include an input device 804, an output device 805, and an external communication interface 806, which are interconnected via a bus system and / or other forms of connection mechanisms (not shown). In this embodiment, the input device may be a network connector, an analog-to-digital converter 23, etc., and the output device may be a display 25, a speaker, etc.

[0197] In some embodiments, the input device 804 may further include, for example, a keyboard, a mouse, a microphone, etc. The output device 805 can output various information to the outside, such as, in addition to the aforementioned display 25 and speakers, a printer, a projector, and a communication network and its connected remote output devices, etc. The external communication interface 806 can be wired, such as a standard serial port (RS232), a General-Purpose Interface Bus (GPIB) interface, an Ethernet interface, or a Universal Serial Bus (USB) interface, or it can be wireless, such as wireless network communication technology (WiFi), Bluetooth, etc.

[0198] The description of the computing device 800 embodiment above is similar to the description of the method embodiment above, and has similar beneficial effects. For technical details not disclosed in the computing device 800 of this embodiment, please refer to the description of the method embodiment in this invention for understanding.

[0199] Example 5

[0200] This embodiment provides a computer-readable storage medium on which an executable program is stored, and when the executable program is executed by a processor, it implements the steps of the method described in Embodiment 1.

[0201] Exemplary examples show that a computer-readable storage medium may be any combination of one or more readable media. A readable medium may be a readable signal medium or a readable storage medium. A computer-readable storage medium is a tangible device capable of holding and storing instructions for use by an instruction execution device. A readable storage medium may, for example, include, but is not limited to, electrical, magnetic, optical, electromagnetic, infrared, or semiconductor systems, apparatuses, or devices, or any combination thereof. More specific examples (a non-exhaustive list) of readable storage media include: portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), flash memory, compact disc read-only memory (CD-ROM), digital versatile disc (DVD), memory sticks, floppy disks, mechanical encoding devices, such as punch cards or recessed protrusions storing instructions thereon, and any suitable combinations thereof.

[0202] The RAM includes: Static Random Access Memory (SRAM), Synchronous Static Random Access Memory (SSRAM), Dynamic Random Access Memory (DRAM), Synchronous Dynamic Random Access Memory (SDRAM), Double Data Rate Synchronous Dynamic Random Access Memory (DDRSDRAM), Enhanced Synchronous Dynamic Random Access Memory (ESDRAM), SyncLink Dynamic Random Access Memory (SLDRAM), and Direct Rambus Random Access Memory (DRRAM).

[0203] The ROM includes: Programmable Read-Only Memory (PROM), Erasable Programmable Read-Only Memory (EPROM), and Electrically Erasable Programmable Read-Only Memory (EEPROM).

[0204] The computer-readable storage medium used herein is not to be construed as a transient signal itself, such as radio waves or other freely propagating electromagnetic waves, electromagnetic waves propagating through waveguides or other transmission media (e.g., light pulses through fiber optic cables), or electrical signals transmitted through wires.

[0205] The description of the above computer-readable storage medium embodiments is similar to the description of the above method embodiments, and has similar beneficial effects. For technical details not disclosed in the computer-readable storage medium of this embodiment, please refer to the description of the method embodiments in this invention for understanding.

[0206] It should be noted that the blood flow parameter measurement method, blood flow parameter measurement device, Doppler blood flow detection equipment, computing device, and computer-readable storage medium embodiments provided in this application belong to the same concept; the technical features in the technical solutions described in each embodiment can be arbitrarily combined without conflict.

[0207] Embodiments of this application may be systems, methods, and / or computer program products. A computer program product may include a computer-readable storage medium having computer-readable program instructions loaded thereon for causing a processor to implement various aspects of this application. The computer program product may be written in any combination of one or more programming languages ​​to perform operations of embodiments of this application. Programming languages ​​include object-oriented programming languages ​​such as Java, C++, etc., and conventional procedural programming languages ​​such as the "C" language or similar programming languages. The program code may be executed entirely on a user's computer, partially on a user's device, as a standalone software package, partially on a user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer may be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or may be connected to an external computer (e.g., via the Internet using an Internet service provider). In some embodiments, electronic circuits, such as programmable logic circuits, field-programmable gate arrays (FPGAs), or programmable logic arrays (PLAs), are personalized by utilizing state information of computer-readable program instructions. These electronic circuits can execute computer-readable program instructions to implement various aspects of this application.

[0208] The computer-readable program instructions described herein can be downloaded from computer-readable storage media to various computing / processing devices, or downloaded via a network, such as the Internet, local area network, wide area network, and / or wireless network, to an external computer or external storage device. The network may include copper transmission cables, fiber optic transmission, wireless transmission, routers, firewalls, switches, gateway computers, and / or edge servers. A network adapter card or network interface in each computing / processing device receives the computer-readable program instructions from the network and forwards them to the computer-readable storage media in the respective computing / processing device.

[0209] Various aspects of this application are described herein with reference to flowchart illustrations and / or block diagrams of methods, apparatus (systems), and computer program products according to embodiments of this application. It should be understood that each block of the flowchart illustrations and / or block diagrams, and combinations of blocks in the flowchart illustrations and / or block diagrams, can be implemented by computer-readable program instructions.

[0210] These computer-readable program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, or other programmable data processing apparatus to produce a machine such that, when executed by the processor of the computer or other programmable data processing apparatus, they create means for implementing the functions / actions specified in one or more blocks of the flowchart and / or block diagram. These computer-readable program instructions can also be stored in a computer-readable storage medium that causes a computer, programmable data processing apparatus, and / or other device to operate in a particular manner; thus, the computer-readable medium storing the instructions comprises an article of manufacture that includes instructions for implementing aspects of the functions / actions specified in one or more blocks of the flowchart and / or block diagram.

[0211] Computer-readable program instructions may also be loaded onto a computer, other programmable data processing apparatus, or other device to cause a series of operational steps to be performed on the computer, other programmable data processing apparatus, or other device to produce a computer-implemented process, thereby causing the instructions executed on the computer, other programmable data processing apparatus, or other device to perform the functions / actions specified in one or more boxes of a flowchart and / or block diagram.

[0212] In the following description, the terms “first, second, ...” are used only to distinguish similar objects and do not represent a specific ordering of objects. Understandably, “first, second, third” can be interchanged in a specific order or sequence where permitted.

[0213] The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the scope of this application. When used herein, the singular forms “a,” “an,” and “the” are also intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the terms “comprising” and / or “including,” when used in this specification, identify the presence of the stated features, integers, steps, operations, elements, and / or components, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups. When used herein, the term “and / or” includes any and all combinations of the associated listed items.

[0214] It should be understood that the phrases "an embodiment" or "some embodiments" mentioned throughout the specification mean that a specific feature, structure, or characteristic related to the embodiment is included in at least one embodiment of the invention. Therefore, "in an embodiment" or "in some embodiments" appearing throughout the specification do not necessarily refer to the same embodiment. Furthermore, these specific features, structures, or characteristics can be combined in any suitable manner in one or more embodiments. It should be understood that in the various embodiments of the invention, the sequence numbers of the above-described processes do not imply a sequential 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 invention. The sequence numbers of the above-described embodiments of the invention are merely descriptive and do not represent the superiority or inferiority of the embodiments.

[0215] 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 device embodiments described above are merely illustrative. For example, the division of modules is only a logical functional division, and in actual implementation, there may be other division methods, such as: multiple modules or components can be combined, or integrated into another system, or some features can be ignored or not executed. In addition, the coupling, direct coupling, or communication connection between the various components shown or discussed can be through some interfaces, and the indirect coupling or communication connection between devices or modules can be electrical, mechanical, or other forms.

[0216] The modules described above as separate components may or may not be physically separate. The components shown as modules may or may not be physical modules. They may be located in one place or distributed across multiple network modules. Some or all of the modules may be selected to achieve the purpose of this embodiment according to actual needs.

[0217] In addition, in the various embodiments of the present invention, each functional module can be integrated into one processing module, or each functional module can be a separate module, or two or more functional modules can be integrated into one module; the integrated module can be implemented in hardware or in the form of hardware plus software functional modules.

[0218] Those skilled in the art will understand that all or part of the steps of the above method embodiments can be implemented 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 performs the steps of the above method embodiments.

[0219] Alternatively, if the integrated modules of this invention are implemented as software functional modules and sold or used as independent products, they can also be stored in a computer-readable storage medium. Based on this understanding, the technical solutions of the embodiments of this invention, or the parts that contribute to the prior art, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause an electronic device (which may be a personal computer, server, or network device, etc.) to execute all or part of the methods described in the various embodiments of this invention. Thus, the embodiments of this invention are not limited to any specific hardware and software combination.

[0220] The methods disclosed in the several method embodiments provided in this application can be arbitrarily combined to obtain new method embodiments without conflict. Similarly, the features disclosed in the several product embodiments provided in this application can be arbitrarily combined to obtain new product embodiments without conflict.

[0221] It should be noted that, in this document, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Unless otherwise specified, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes that element.

[0222] It should be understood that the above embodiments are exemplary and are not intended to encompass all possible implementations included in the claims. Various modifications and changes can be made to the above embodiments without departing from the scope of this disclosure. Similarly, the various technical features of the above embodiments can be arbitrarily combined to form other embodiments of the present invention that may not be explicitly described. Therefore, the above embodiments only illustrate several implementations of the present invention and do not limit the scope of protection of this patent.

Claims

1. A method of measuring a blood flow parameter, applied to a Doppler blood flow detection device, characterized in that, The Doppler blood flow detection device comprises a probe, the probe comprising two transmitters and a receiver fixed in position; the two transmitters are respectively located on the two sides of the receiver in the flow direction of the blood vessel to be detected, and the two transmitters use the same driving source, so that the frequencies and phases of the two transmitters are consistent; the method comprises: acquiring a first channel signal and a second channel signal through the receiver, and acquiring the flow rate of the blood vessel to be detected according to the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by the other transmitter and reflected by the blood vessel to be detected; acquiring a first Doppler angle at which the probe actually works according to the relationship between the flow rate, a Doppler angle and the flow rate; adjusting the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, and further acquiring the blood flow parameter of the blood vessel to be detected; the acquiring of the first Doppler angle at which the probe actually works according to the relationship between the flow rate, a Doppler angle and the flow rate comprises: determining the first Doppler angle at which the probe actually works according to the flow rate, a second Doppler angle preset for the probe, and the positional relationship between the transmitters and the receiver; the determining of the first Doppler angle at which the probe actually works according to the flow rate, a second Doppler angle preset for the probe, and the positional relationship between the transmitters and the receiver comprises: calculating β according to the following expression: ； wherein θ is the preset second Doppler angle, β is the deviation angle of the Doppler angle, (θ-β) and (θ+β) are the first Doppler angles at which the two transmitters in the probe actually work, and γ is the angle between the receiver and the blood flow direction.

2. The method of measuring a blood flow parameter according to claim 1, wherein, the acquiring of the first channel signal and the second channel signal through the receiver, and the acquiring of the flow rate of the blood vessel to be detected according to the first channel signal and the second channel signal comprises: acquiring the spectral envelope of the first channel signal and the second channel signal according to the first channel signal and the second channel signal; acquiring a first flow rate and a second flow rate according to the spectral envelope of the first channel signal and the second channel signal.

3. The method of claim 2, wherein, the acquiring of the first flow rate and the second flow rate according to the spectral envelope of the first channel signal and the second channel signal comprises: acquiring the peak values of multiple periods of the first channel signal and the second channel signal according to the spectral envelope of the first channel signal and the second channel signal; eliminating outliers in the multiple peak values by using the Ralston criterion; calculating the average value of the peak values remaining after the outliers are eliminated; acquiring the first flow rate and the second flow rate according to the average value.

4. The method of measuring a blood flow parameter according to any one of claims 1 to 3, characterized in that, the adjusting of the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle, and the further acquiring of the blood flow parameter of the blood vessel to be detected comprises: adjusting the peak values of the spectral envelope of the first channel signal and the second channel signal according to the first Doppler angle. The frequency spectrum envelopes of the adjusted first channel signal and the second channel signal are overlapped to obtain a new frequency spectrum envelope; According to the new frequency spectrum envelope, a blood flow parameter of the blood vessel to be detected is obtained.

5. A blood flow parameter measuring device for use in a Doppler blood flow detection apparatus, characterized in that The Doppler blood flow detection device comprises a probe, the probe comprising two transmitters and a receiver fixed in position; the two transmitters are respectively located on the two sides of the receiver in the flow direction of the blood vessel to be detected, and the two transmitters use the same driving source, so that the frequencies and phases of the two transmitters are consistent; The blood flow parameter measurement device comprises: A first obtaining module is configured to obtain a first channel signal and a second channel signal through the receiver, and obtain a flow velocity of the blood vessel to be detected according to the first channel signal and the second channel signal; the first channel signal is a signal emitted by one transmitter and reflected by the blood vessel to be detected, and the second channel signal is a signal emitted by the other transmitter and reflected by the blood vessel to be detected; A second obtaining module is configured to obtain a first Doppler angle at which the probe actually works according to the flow velocity, and the relationship between the Doppler angle and the flow velocity; A third obtaining module is configured to adjust the frequency spectrum envelopes of the first channel signal and the second channel signal according to the first Doppler angle, and further obtain the blood flow parameter of the blood vessel to be detected; The second obtaining module is further configured to: determine the first Doppler angle at which the probe actually works according to the flow velocity, a second preset Doppler angle of the probe, and the positional relationship between the transmitters and the receiver; The second obtaining module is further configured to: calculate β according to the following expression: ； wherein θ is the second preset Doppler angle, β is a deviation angle of the Doppler angle, (θ-β) and (θ+β) are the first Doppler angles at which the two transmitters in the probe actually work, and γ is an angle between the receiver and the blood flow direction.

6. A Doppler blood flow detection device, characterized by The blood flow parameter measurement device of claim 5; The probe comprises two transmitters and a receiver fixed in position; the two transmitters are respectively located on the two sides of the receiver in the flow direction of the blood vessel to be detected. The computing device comprises a memory, a communication bus and a processor, wherein:

7. A computing device, comprising: The memory is configured to store a blood flow parameter measurement method program; The communication bus is configured to realize the connection and communication between the memory and the processor; The processor is configured to execute the blood flow parameter measurement method program to realize the steps of the method of any one of claims 1 to 4. The computer readable storage medium stores an executable program, and the executable program is executed by the processor to realize the steps of the method of any one of claims 1 to 4.

8. A computer-readable storage medium, characterized in that, The computer readable storage medium stores an executable program, and the executable program is executed by the processor to realize the steps of the method of any one of claims 1 to 4.

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