WO2024108872A1 - 利用双晶元组确定血流速度的方法和多普勒血流检测装置 - Google Patents

利用双晶元组确定血流速度的方法和多普勒血流检测装置 Download PDF

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Publication number
WO2024108872A1
WO2024108872A1 PCT/CN2023/087749 CN2023087749W WO2024108872A1 WO 2024108872 A1 WO2024108872 A1 WO 2024108872A1 CN 2023087749 W CN2023087749 W CN 2023087749W WO 2024108872 A1 WO2024108872 A1 WO 2024108872A1
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Prior art keywords
blood flow
angle
chip
flow velocity
spectrum waveform
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PCT/CN2023/087749
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English (en)
French (fr)
Inventor
丁衍
孙东军
何润宝
张跃春
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苏州晟智医疗科技有限公司
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Priority to EP23864118.7A priority Critical patent/EP4397247A1/en
Publication of WO2024108872A1 publication Critical patent/WO2024108872A1/zh
Priority to US18/753,524 priority patent/US20240341718A1/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/06—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0891—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4245—Details of probe positioning or probe attachment to the patient involving determining the position of the probe, e.g. with respect to an external reference frame or to the patient
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4494—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer characterised by the arrangement of the transducer elements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/488—Diagnostic techniques involving Doppler signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/54—Control of the diagnostic device

Definitions

  • the invention relates to the field of medical detection, in particular to a method for determining blood flow velocity by using a dual-crystal element group and a Doppler blood flow detection device.
  • the basic principle of using Doppler technology to detect blood flow velocity is that the ultrasonic probe emits ultrasonic waves of a certain intensity.
  • the ultrasonic waves encounter moving blood, since the wavelength of the ultrasonic waves is greater than the diameter of the red blood cells in the blood, the ultrasonic waves will scatter when encountering the red blood cells.
  • the red blood cells are moving, the scattered echo signals undergo Doppler frequency shift. The greater the speed, the greater the frequency shift.
  • the embodiments of the present application provide a method for determining blood flow velocity using a dual chip group and a Doppler blood flow detection device to solve at least one problem existing in the background technology.
  • an embodiment of the present application provides a method for determining blood flow velocity using a dual wafer group, which is applied to a Doppler blood flow detection device, wherein the Doppler blood flow detection device includes a first wafer group and a second wafer group for being placed at different positions of a blood vessel to be detected; the method includes:
  • a blood flow velocity measurement value is determined based on the adjusted first frequency spectrum waveform and the adjusted second frequency spectrum waveform.
  • the present application provides a Doppler blood flow detection device for implementing the above-mentioned first aspect.
  • the method for determining blood flow velocity using a dual-chip group and a Doppler blood flow detection device provided in an embodiment of the present application, wherein the Doppler blood flow detection device includes a first chip group and a second chip group for being placed at different positions of a blood vessel to be detected; the method includes: obtaining a first spectrum waveform obtained by detecting the blood vessel to be detected via the first chip group; obtaining a second spectrum waveform obtained by detecting the blood vessel to be detected via the second chip group; determining the relationship between the actual Doppler angle during detection and the Doppler angle set in the Doppler blood flow detection device according to the first spectrum waveform and the second spectrum waveform; adjusting the first spectrum waveform and the second spectrum waveform according to the determined relationship; determining the blood flow velocity measurement value according to the adjusted first spectrum waveform and the adjusted second spectrum waveform.
  • the Doppler blood flow detection device includes a first chip group and a second chip group for being placed at different positions of a blood vessel to be detected; the method includes: obtaining a
  • FIG1 is a structural block diagram of a Doppler blood flow detection device provided in an embodiment of the present application.
  • FIG2 is a schematic flow chart of a method for determining blood flow velocity using a dual chip assembly provided in an embodiment of the present application
  • FIG3 is a schematic diagram of the position of a Doppler blood flow detection device when detecting a blood vessel to be detected in a specific application
  • FIG4 is a flowchart of spectrum waveform processing in a specific application
  • FIG5 is a schematic diagram showing the positional relationship between the triaxial acceleration sensor and the blood vessel to be detected when the roll angle is not equal to 90°;
  • FIG6 is a schematic diagram of yaw angle, pitch angle and roll angle
  • FIG7 is a schematic diagram of the position of the blood vessel to be detected when there is a roll angle error and when there is no roll angle error;
  • FIG8 is a schematic diagram of a principle of determining a first distance using ultrasound provided in a specific example of the present application.
  • FIG9 is a circuit block diagram of determining a first distance using ultrasound provided in a specific example of the present application.
  • FIG10 is a schematic diagram of a process of determining a first distance using ultrasound provided in a specific example of the present application.
  • FIG. 11 is a schematic diagram of the positions of a first wafer group and/or a second wafer group including a first receiving wafer and a second receiving wafer when inspecting a blood vessel to be inspected, provided in a specific example of the present application.
  • Multiple involved in this application refers to two or more.
  • “And/or” describes the association relationship of associated objects, indicating that there can be three relationships, for example, "A and/or B” can represent: A exists alone, A and B exist at the same time, and B exists alone.
  • the terms “first”, “second”, “third”, etc. involved in this application are only used to distinguish similar objects, and do not represent a specific ordering of objects.
  • a patient refers to any person who is being or may be tested by a Doppler blood flow detection device, and the patient may also be referred to as a patient.
  • Medical personnel for example, include people who use a Doppler blood flow detection device to monitor patients, and therefore, are also considered as one of the users of the Doppler blood flow detection device; however, users may include not only medical personnel, but also other people who directly or indirectly use the Doppler blood flow detection device.
  • the Doppler blood flow detection device includes: a probe, a signal processing module, and a device main body module.
  • the probe may include a first chip group and a second chip group.
  • the first chip group and the second chip group are respectively connected to the signal processing module, so as to transmit the detected signal to the signal processing module; after receiving the signal transmitted by each chip group, the signal processing module processes the above signal.
  • the signal processing module includes a filtering circuit 1, a filtering circuit 2, a signal demodulation 1, a signal demodulation 2, ADC1, and ADC2;
  • the first wafer group is connected to the filtering circuit 1 in the signal processing module, and the second wafer group is connected to the filtering circuit 2 in the signal processing module, and the filtering circuit 1 and the filtering circuit 2 respectively filter the signals detected by the first wafer group and the second wafer group;
  • the filtering circuit 1 is connected to the signal demodulation 1, and the filtering circuit 2 is connected to the signal demodulation 2, and the signal demodulation 1 and the signal demodulation 2 respectively demodulate the signals after filtering by the filtering circuit 1 and the filtering circuit 2;
  • the signal demodulation 1 is connected to the ADC1, and the signal demodulation 2 is connected to the ADC2, and the ADC1 and the ADC2 respectively perform analog-to-digital conversion on the signals after demodulation by the signal demodulation 1 and the signal demodulation 2.
  • the device In order to store the received detection results, as well as the intermediate quantities and algorithm programs in the storage operation process, the device also includes a storage module connected to the processor, such as a memory, a storage device, etc. Of course, the device can also include a network port.
  • the communication interface provides an interface for communication with other smart devices to transmit data and realize feedback.
  • the communication interface can be a commonly used communication hardware interface such as USB/UART/network port/Bluetooth/WIFI/CAN, and this application does not make specific restrictions on it.
  • the device may also include an audio power amplifier and a speaker connected to the audio power amplifier.
  • the speaker may be used to The result determined by the processor is outputted in audio format, as well as the information that needs to be reminded to the user.
  • the device may also include an input device; wherein the input device includes but is not limited to at least one of the following: a keyboard, a button, a voice-controlled input device, and a touch screen. It is understandable that other devices capable of realizing signal input are included in the meaning of this application.
  • the device may also include an output device; wherein the output device includes but is not limited to an LCD display. Of course, other devices capable of realizing signal output are also included in the meaning of this application. In this way, the device can realize information interaction with the user.
  • the method for determining blood flow velocity using a dual wafer group is applied to a Doppler blood flow detection device, which includes a first wafer group and a second wafer group for being placed at different positions of a blood vessel to be detected.
  • the first wafer group and the second wafer group are arranged together in a probe.
  • the Doppler blood flow detection device is, for example, the Doppler blood flow detection device shown in FIG1.
  • the method for determining blood flow velocity using a dual-chip set includes:
  • Step 201 obtaining a first spectrum waveform obtained by detecting a blood vessel to be detected via a first chip group
  • Step 202 obtaining a second spectrum waveform obtained by detecting the blood vessel to be detected via the second chip group
  • Step 203 determining the relationship between the actual Doppler angle during detection and the Doppler angle set in the Doppler blood flow detection device according to the first spectrum waveform and the second spectrum waveform;
  • Step 204 adjusting the first spectrum waveform and the second spectrum waveform according to the determined relationship
  • Step 205 Determine a blood flow velocity measurement value according to the adjusted first frequency spectrum waveform and the adjusted second frequency spectrum waveform.
  • the first wafer group and the second wafer group are used to be placed at different positions of the blood vessel to be detected.
  • one of the first wafer group and the second wafer group is placed at the first position of the blood vessel to be detected, and the other is placed at the second position of the blood vessel to be detected.
  • the first position and the second position are respectively the front and rear positions of the blood vessel to be detected along the direction of blood flow movement, that is, the direction of blood flow movement is the direction from the first position to the second position.
  • the blood vessel to be detected is wrapped by the skin, and the first wafer group and the second wafer group are obviously not in direct contact with the blood vessel to be detected.
  • the first wafer group and the second wafer group described in this article are placed at different positions of the blood vessel to be detected, which means that the first wafer group and the second wafer group are placed at different positions corresponding to the blood vessel to be detected across the skin.
  • the first spectrum waveform and the second spectrum waveform are spectrum waveforms obtained by detecting the blood vessel to be detected through the first chip group and the second chip group, respectively, and the first chip group and the second chip group are used to be placed at different positions of the blood vessel to be detected.
  • Figure 3 is a schematic diagram of the position when a Doppler blood flow detection device is used to detect a blood vessel to be detected in a specific application. The figure simply shows the position of the blood vessel to be detected and the position of the first chip group and the second chip group transmitting signals.
  • the solid line in the figure indicates that the actual Doppler angle during detection is consistent with the Doppler angle set in the Doppler blood flow detection device, that is, the actual Doppler angle is equal to the set Doppler angle ⁇ (specifically the emission angle, so it may also be referred to as the emission angle ⁇ below).
  • the emission angle ⁇ specifically the emission angle, so it may also be referred to as the emission angle ⁇ below.
  • the dotted line in the figure shows the situation where the actual Doppler angle is inconsistent with the Doppler angle set in the Doppler blood flow detection device.
  • the Doppler blood flow detection device used in the embodiment of the present application includes the above-mentioned first chip group and the second chip group, and two Doppler channel acquisition is realized through the first chip group and the second chip group. Since the first chip group and the second chip group are placed at different positions on the blood vessel to be detected, the two Doppler channel acquisition has two Doppler angles, and two groups of acquisition data are obtained according to the two Doppler angles. Two spectrum waveforms can be obtained according to the two groups of acquisition data. Please refer to Figure 4, where the channel receiving the acquisition data of the first chip group is called “channel 1", and the channel receiving the acquisition data of the second chip group is called “channel 2”, and the spectrum waveform obtained through channel 1 and channel 2 is shown in Figure 4 (a).
  • the first wafer group includes at least one transmitting wafer and at least one receiving wafer
  • the second wafer group also includes at least one transmitting wafer and at least one receiving wafer.
  • the first wafer group and the second wafer group transmit and sample synchronously.
  • the measurement time corresponding to the first spectrum waveform and the second spectrum waveform is the same.
  • the difference between the two is caused by the difference in the actual Doppler angle of the first chip group and the second chip group. It can be understood that if in an ideal state (that is, the actual Doppler angle during detection is consistent with the Doppler angle set in the Doppler blood flow detection device), the actual Doppler angle during detection by the first chip group and the actual Doppler angle during detection by the second chip group should be the same, and both are equal to the set Doppler angle. In this way, the relationship between the actual Doppler angle during detection and the Doppler angle set in the Doppler blood flow detection device can be determined based on the first spectrum waveform and the second spectrum waveform.
  • the step of determining the first peak according to the first spectrum waveform, and/or the step of determining the second peak according to the second spectrum waveform may include: determining multiple peaks of multiple cycles according to the spectrum waveform; using the Laida criterion to eliminate outliers among the multiple peaks; and calculating the average value of the remaining peaks after eliminating the outliers.
  • the step of determining the first peak value according to the first spectrum waveform includes determining multiple peak values of multiple cycles according to the first spectrum waveform and removing outliers using the Laida criterion, then the average value of the remaining peak values after removing the outliers is calculated to obtain a first average value, and the first average value is determined as the first peak value.
  • the step of determining the second peak value from the second spectrum waveform includes determining multiple peaks of multiple cycles according to the second spectrum waveform and eliminating outliers using the Laida criterion, then calculating the average of the remaining peaks after eliminating the outliers to obtain a second average value, and determining the second average value as the second peak value.
  • the waveform of the first spectrum waveform may be flipped first.
  • the data of flipped channel 1 is shown in FIG4 ( b ).
  • 5 cycles can be selected, and the peak value of each cycle in the selected 5 cycles can be calculated to obtain 5 peak values.
  • this step only means that the Laida criterion is used to perform the operation of eliminating outliers, and does not mean that outliers must be eliminated. In other words, if there are no outliers among the 5 peaks, all 5 peaks are retained.
  • the average value of the peaks remaining after eliminating the outliers is calculated. Of course, this step only means that the operation of averaging is performed. If only one peak remains after eliminating the outliers, the result of the averaging is the peak value.
  • the above steps may be performed on both the first spectrum waveform and the second spectrum waveform to obtain average values respectively, and the respective average values are correspondingly determined as the first peak value Vm1 and the second peak value Vm2.
  • r is the deviation angle between the actual Doppler angle during detection and ⁇ , which can also be referred to as the tilt angle. Further, according to r, the data of channel 1 and channel 2 can be adjusted accordingly, and this step can also be called correction.
  • the first spectrum waveform and the second spectrum waveform are scaled by a corresponding ratio according to the determined relationship, so as to obtain a modified spectrum waveform, as shown in (c) of FIG4.
  • the two modified spectrum waveforms are highly similar.
  • determining the blood flow velocity measurement value based on the adjusted first spectrum waveform and the adjusted second spectrum waveform includes: spectrally overlapping the adjusted first spectrum waveform and the adjusted second spectrum waveform to obtain an overlapped spectrum waveform; and determining the blood flow velocity measurement value based on the overlapped spectrum waveform.
  • the overlapped spectrum waveform can be referred to in (d) of FIG4 .
  • the overlapped spectrum waveform further merges the detection results of the first wafer group with the detection results of the second wafer group, thereby neutralizing the angle error between the two. Determining the blood flow velocity measurement value based on the overlapped spectrum waveform can be performed using existing technical means in the art, and this application does not make specific limitations on this.
  • the blood flow velocity measurement value obtained in this way is closer to the actual blood flow velocity, and basically eliminates the inconsistency between the angle between the probe and the blood vessel to be detected in the actual measurement and the set Doppler angle. The error is reduced, thereby improving the accuracy of blood flow velocity measurement.
  • the frequencies of the signals emitted by the transmitting chips in the first chip group and the second chip group are different, so that the Doppler blood flow detection device is a dual-frequency dual-channel abnormal probe detection device.
  • the frequency of the signals emitted by the first wafer group and the second wafer group is in the range of 1 MHz-16 MHz to meet the requirements of dual-frequency dual-channel detection. Further, the frequency of the signals emitted by the first wafer group and the second wafer group is in the range of 2 MHz-8 MHz, and the accuracy of the detection result is better.
  • the frequency F1 of the signal emitted by the first wafer group and the frequency F2 of the signal emitted by the second wafer group satisfy the following relationship: 1. F1 ⁇ F2, 2. The remainder of F2 taken from F1 is greater than 0.5MHz, 3. F2 ⁇ 3F1.
  • F1 2.1 MHz - 2.7 MHz
  • F2 3.8 MHz - 4.3 MHz.
  • a limiting filter is used in the signal filtering of the first chip group and the second chip group, and the bandwidth of one of them ranges from F1-0.5MHz to F1+0.5MHz; the bandwidth of the other ranges from F2-0.5MHz to F2+0.5MHz.
  • different channels are set with different filter bandwidths.
  • the receiving chips on both sides can receive the signals of the two transmitting chips, that is, there will be interference with each other.
  • the filtering of the corresponding frequency band of the corresponding channel is selected, which can suppress the signal of another frequency band and achieve a better signal-to-noise ratio.
  • Ultrasonic interference in the two channels is removed through filtering and demodulation techniques.
  • the first wafer group and the second wafer group are arranged in the probe of the Doppler blood flow detection device, and the two can be arranged in the same probe.
  • the embodiment of the present application does not exclude the situation where the two are arranged in two probes respectively. If the two are arranged in two probes respectively, there is a mechanical connection relationship between the two probes, so that the positions of the two probes are related to each other to ensure that when a deviation angle occurs, the deviation angles of the two are respectively ⁇ r.
  • the method also includes: determining the roll angle of the probe in the detection state, the roll angle being the angle between the projection direction of the sound field emitted by the transmitting chip in the probe on the horizontal plane and the direction of blood flow movement in the blood vessel to be detected, and the transmitting chip is a transmitting chip in the first chip group and/or the second chip group; correcting the blood flow velocity measurement value according to the roll angle to obtain a corrected blood flow velocity measurement value.
  • the Doppler blood flow detection device also includes a posture sensor (not shown in FIG. 1 ) disposed in the probe; determining the roll angle of the probe in the detection state includes: using the posture sensor to determine the roll angle of the probe in the detection state.
  • the attitude sensor is a high-performance three-dimensional motion attitude measuring instrument.
  • the attitude sensor may include at least one of the following: a three-axis acceleration sensor, a gyroscope, a three-axis electronic compass, and other motion sensors.
  • the posture sensor includes a three-axis acceleration sensor; determining that the probe is detecting The method comprises: obtaining acceleration components of gravity acceleration in three mutually perpendicular coordinate axis directions in the detection state based on a three-axis acceleration sensor; and determining the roll angle according to the acceleration components.
  • the user when starting to measure the blood flow velocity, the user places the probe at the measurement position according to a predetermined usage method, wherein the predetermined usage method is, for example, to ensure that the projection direction of the sound field emitted by the transmitting element in the probe on the horizontal plane is perpendicular to the direction of blood flow movement in the blood vessel to be detected, and no discrete angle is generated, thereby reducing the measurement error.
  • the predetermined usage method is, for example, to ensure that the projection direction of the sound field emitted by the transmitting element in the probe on the horizontal plane is perpendicular to the direction of blood flow movement in the blood vessel to be detected, and no discrete angle is generated, thereby reducing the measurement error.
  • the patient can be considered to be stationary.
  • the initial output value of the three-axis acceleration sensor can be recorded as a reference for the roll angle calculated later.
  • FIG5 shows the positional relationship between the three-axis acceleration sensor and the blood vessel to be detected when the roll angle is not equal to 90°. Since the three-axis acceleration sensor is located in the probe, FIG5 also shows the positional relationship between the three-axis acceleration sensor and the blood vessel to be detected when the projection direction of the sound field emitted by the transmitting element in the probe on the horizontal plane is not perpendicular to the direction of blood flow in the blood vessel to be detected.
  • the component of gravity acceleration g in the X-axis direction is Ax
  • the angle between Ax and the blood vessel to be detected 101 is a1
  • the angle with gravity acceleration g is a
  • the component of gravity acceleration g in the Y-axis direction is Ay
  • the angle between Ay and the blood vessel to be detected 101 is b1
  • the angle with gravity acceleration g is b
  • the component of gravity acceleration g in the Z-axis direction Az
  • the angle between Az and the blood vessel to be detected 101 is ⁇ 1
  • the angle with gravity acceleration g is ⁇ .
  • sina1 Ax/g
  • cosa1 squr(g*g-Ax*Ax)/g
  • the relationship between the measured value of the triaxial acceleration sensor and a1, b1 and ⁇ 1 is obtained.
  • the values of a1, b1 and ⁇ 1 are equal to the corresponding radian values.
  • ⁇ is the angle value corresponding to the radian value b11
  • ⁇ is the angle value corresponding to the radian value ⁇ 11
  • ⁇ is the angle value corresponding to the radian value a11
  • ⁇ is the roll angle
  • the directions of the three mutually perpendicular coordinate axes are established according to the directions of the three-axis acceleration sensor in the measuring state.
  • the three-axis acceleration sensor and the transmitting chip are located together in the probe. Therefore, the direction of the three-axis acceleration sensor can represent the direction of the transmitting chip. Therefore, the angle between the projection direction of the sound field emitted by the transmitting chip on the horizontal plane and the direction of blood flow movement can be determined based on the acceleration component.
  • the attitude sensor includes a gyroscope; determining the roll angle of the probe in the detection state includes: obtaining the roll angle in the detection state based on the gyroscope.
  • Figure 6 is a schematic diagram of the yaw angle, pitch angle and roll angle; wherein (a) shows the yaw angle ⁇ , (b) shows the pitch angle ⁇ , and (c) shows the roll angle ⁇ .
  • the spatial trajectory of the moving object is decomposed into independent motions along the Z, Y, and X axes, and the component of the motion vector in each axis is represented by the cosine of the angle between the vector and each axis.
  • the moving object is, for example, a posture sensor.
  • the component format is as follows:
  • the three-fold Euler rotation of a moving object can be represented by three direction cosine matrices:
  • Cosine Matrix Product Used to express the transformation from the geographic coordinate system to the moving object coordinate system:
  • the angular rate data obtained by the attitude sensor can be converted into attitude angle data.
  • the inclination angle (roll angle ⁇ and pitch angle ⁇ ) can be obtained by using inverse trigonometric functions:
  • the relative angle between the Z-axis direction and the direction of the blood vessel to be detected is unchanged, that is, ⁇ and ⁇ 1 remain unchanged, that is, the pitch angle remains unchanged, and only the roll angle ⁇ needs to be used for angle correction.
  • the blood flow velocity measurement value has been determined based on the adjusted first spectrum waveform and the adjusted second spectrum waveform; next, the blood flow velocity measurement value is corrected to obtain a corrected blood flow velocity measurement value.
  • V1 V/sin ⁇ ; wherein V1 represents the blood flow velocity measurement value after correction, V represents the blood flow velocity measurement value before correction, and ⁇ represents the roll angle.
  • the roll angle ⁇ is equal to 90°, and the measurement result has no roll angle error.
  • This embodiment further improves the accuracy of the blood flow velocity measurement value to be output by correcting the blood flow velocity measurement value determined in step 205.
  • the corrected value of the blood flow velocity measurement value can be output as the output value.
  • step 201 and/or step 202 may include: obtaining an emission angle, which is the angle between the direction of the emission signal of the transmitting chip in the first chip group and/or the second chip group and the direction of blood flow movement in the blood vessel to be detected; obtaining the distance between the transmitting chip and the receiving chip in the same chip group in the Doppler blood flow detection device and the distance between the transmitting chip and the blood vessel to be detected; determining the receiving angle according to the emission angle, the distance between the transmitting chip and the receiving chip, and the distance between the transmitting chip and the blood vessel to be detected, which is the angle between the direction of the receiving signal of the receiving chip in the first chip group and/or the second chip group and the direction of blood flow movement; determining the first spectrum waveform and/or the second spectrum waveform according to the emission angle and the receiving angle.
  • the present embodiment can obtain a result closer to the actual situation.
  • obtaining the emission angle may specifically include: obtaining the emission angle ⁇ (i.e., the set Doppler angle) pre-stored in the Doppler blood flow detection device. It is understandable that the specific value of the emission angle ⁇ may be a fixed angle value determined when the Doppler blood flow detection device is designed.
  • Acquiring the distance D between the transmitting wafer T and the receiving wafer R in the same wafer group in the Doppler blood flow detection device may specifically include: acquiring the distance D between the transmitting wafer T and the receiving wafer R in the same wafer group pre-stored in the Doppler blood flow detection device.
  • the D value may also be a fixed value determined when the Doppler blood flow detection device is designed.
  • the distance between the transmitting chip T and the blood vessel 101 to be detected includes a first distance L, which is the distance from the transmitting chip T to the blood vessel 101 to be detected along the direction in which the transmitting chip T transmits the signal; the receiving angle ⁇ is determined according to the transmitting angle ⁇ , the distance D between the transmitting chip T and the receiving chip R, and the distance L between the transmitting chip T and the blood vessel 101 to be detected, including using the following formula to determine the receiving angle ⁇ :
  • arctan(D/L); wherein ⁇ is the receiving angle, ⁇ is the transmitting angle,
  • is the absolute value of the difference between the receiving angle and the transmitting angle, and D is the transmitting chip. and the distance between the receiving wafer, L is the first distance.
  • obtaining the distance between the transmitting chip T and the blood vessel 101 to be detected includes: obtaining the time t required for the transmitting chip T to transmit the signal to the receiving chip R to receive the signal; determining the distance the signal propagates within the required time according to the required time t and the propagation speed c of the signal; and determining the first distance L according to the propagation distance.
  • the distance between the transmitting crystal element T and the blood vessel 101 to be detected can be obtained by measuring with A-ultrasound, B-ultrasound and other technologies.
  • the transmitter T is, for example, an ultrasonic transmitter
  • the receiver R is, for example, an ultrasonic receiver
  • the obstacle is, for example, a blood vessel to be detected;
  • the transmitter T transmits a short segment of ultrasonic waves of a fixed frequency to the obstacle, and starts timing at the beginning of the transmission.
  • the ultrasonic wave has a propagation speed c and time in the object. After being reflected by the obstacle, it enters the receiver R.
  • the time from transmission to reception can be measured as t.
  • the propagation speed of the ultrasonic wave in the object is c, and the measured distance can be calculated.
  • the actual distance can be estimated based on the measured distance.
  • the original acquisition circuit and sensor can be used to acquire Doppler signals using a PW pulse wave Doppler method, and the time difference between transmission and reception can be recorded in each occurrence cycle to calculate the measured distance and angle.
  • This method uses time domain data for analysis and calculation.
  • the blood vessel depth of the neck is between 5mm-30mm (i.e. H is between 5mm-30mm), and the range of L is between 7mm-42mm.
  • the range of T is between 7/1570000 ⁇ 42/1570000s, 7/1570 ⁇ 42/1570ms, and 4.5 ⁇ s ⁇ 27 ⁇ s.
  • FIG9 is a circuit block diagram of a specific example of the present application for determining a first distance using ultrasound
  • FIG10 is a flow chart of a specific example of the present application for determining a first distance using ultrasound.
  • the circuit in the figure is a part of the signal conditioning part of the overall circuit, which is specifically used for distance testing.
  • the generation control circuit, signal demodulation and signal amplification parts are shared.
  • the generation control circuit controls the transmitting wafer to send a signal.
  • the signal demodulation and signal amplification respectively demodulate and amplify the signal; wherein, the received signal will be input into the ADC (not shown in the figure) for collection.
  • the signal enters the analog comparator for comparison, and the analog comparator outputs a digital signal, which is directly collected by the I/O pin of the processor.
  • the process of using ultrasound to determine the first distance includes: after starting the distance test, the transmitting chip transmits an ultrasonic signal, starts timing, and turns off the transmission; the ultrasonic signal is transmitted through the tissue to the blood, collides with the blood, and is reflected to the receiving chip after the Doppler effect occurs.
  • the receiving chip performs i/q demodulation on the ultrasonic signal, and the demodulated signal is output as a weak analog signal.
  • the signal amplification circuit amplifies the signal to a set range. The greater the blood flow velocity, the greater the signal. Set a comparison voltage V0, when the signal is greater than V0, the analog comparator output is 1; when the signal is less than V0, the analog comparator output is 0.
  • the method for determining each ranging cycle is as follows: the transmitting chip emits an ultrasonic signal and starts timing. If the analog comparator output changes from 0 to 1, it is considered to be the ultrasonic transmission time measured in this cycle. Specifically, the result of the comparator trigger is determined to be yes or no. If the result is yes, the time N is recorded; if the result is no, the waiting time is up until the total acquisition time is up.
  • a time period such as a measurement time of 2s-5s, preferably 3s, to ensure that the signal under the maximum blood flow state can be measured in one measurement time.
  • the pulse of the patient being measured is 20bpm, which can meet clinical requirements.
  • the recorded time is sorted from small to large, the abnormal points are removed, and the three smallest times are selected to take the average, and the distance test is completed.
  • the receiving angle is then calculated using the following formula:
  • arctan(D/L).
  • the second distance H is input into the Doppler blood flow detection device by medical personnel, for example.
  • the receiving wafers in the first wafer group and/or the second wafer group include a first receiving wafer R1 and a second receiving wafer R2, the first receiving wafer R1 and the second receiving wafer R2 receive a signal transmitted by the same transmitting wafer T, and the distance D1 between the transmitting wafer T and the first receiving wafer R1 is the same as the distance D2 between the transmitting wafer T and the second receiving wafer R2; determining the receiving angle according to the transmitting angle, the distance between the transmitting wafer and the receiving wafer, and the distance between the transmitting wafer and the blood vessel to be detected, including: determining a first receiving angle ⁇ 1 and a second receiving angle ⁇ 2; wherein , the first receiving angle ⁇ 1 is the angle between the direction in which the first receiving element R1 receives the signal and the direction in which the blood flows; the second receiving angle ⁇ 2 is the angle between the direction in which the second receiving element R2 receives the signal and the direction in which the blood
  • the distance D1 between the transmitting wafer T and the first receiving wafer R1 is the same as the distance D2 between the transmitting wafer T and the second receiving wafer R2, so ⁇ - ⁇ 2 ⁇ 1- ⁇ , and the angle difference is assumed to be ⁇ .
  • the transmitting wafer T transmits a signal
  • the first receiving wafer R1 and the second receiving wafer R2 can receive the signal at the same time.
  • an embodiment of the present application further provides a Doppler blood flow detection device, which is used to implement the method of determining blood flow velocity using a dual chip group in any one of the above embodiments.
  • Doppler blood flow detection device can be referred to the relevant description in the above-mentioned method embodiment of determining blood flow velocity using a dual-chip group, and will not be repeated here.

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Abstract

一种利用双晶元组确定血流速度的方法，应用于多普勒血流检测装置，多普勒血流检测装置包括用于放置在待检测血管不同位置处的第一晶元组和第二晶元组。方法包括：获取经由第一晶元组对待检测血管进行检测得到的第一频谱波形(201)；获取经由第二晶元组对待检测血管进行检测得到的第二频谱波形(202)；根据第一频谱波形和第二频谱波形确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系(203)；根据确定的关系对第一频谱波形和第二频谱波形进行调整(204)；根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值(205)。

Description

利用双晶元组确定血流速度的方法和多普勒血流检测装置
相关申请
本申请要求于2022年11月24日申请的，申请号为202211479824.2，名称为“利用双晶元组确定血流速度的方法和多普勒血流检测装置”的中国专利申请的优先权，在此将其全文引入作为参考。
技术领域
本发明涉及医疗检测领域，特别是涉及一种利用双晶元组确定血流速度的方法和多普勒血流检测装置。
背景技术
随着科技的发展，对于人体出现的各类疾病，可以通过医疗检测手段获取人体的相关参数来帮助医生进行诊断，其中血流速度是一项重要的生理参数，许多疾病都能在血流速度上得到反映。
利用多普勒技术进行血流速度的检测，其基本原理是超声探头发出一定强度的超声波，当超声波遇到运动的血液时，由于超声波的波长大于血液中的红细胞的直径，超声波遇到红细胞时将发生散射。同时由于红细胞在运动，所以散射的回波信号发生了多普勒频移，速度越大，频移也就越大。通过分析回波信号中的频移量，结合多普勒技术的数学公式推算出红细胞的移动速度。
目前，使用多普勒血流检测装置对患者进行血流速度检测在临床上已经得到了广泛应用，但是在实际使用中，测量结果往往存在着一定的误差，尤其是在医护人员操作不标准，或者患者在长时间监测过程中出现移动时，测量结果的误差会更大，这导致血流速度测量结果的可参考性被降低，严重时可能会造成医护人员对患者病情的误判。
发明内容
有鉴于此，本申请实施例为解决背景技术中存在的至少一个问题而提供一种利用双晶元组确定血流速度的方法和多普勒血流检测装置。
第一方面，本申请实施例提供了一种利用双晶元组确定血流速度的方法，应用于多普勒血流检测装置，多普勒血流检测装置包括用于放置在待检测血管不同位置处的第一晶元组和第二晶元组；方法包括：
获取经由第一晶元组对待检测血管进行检测得到的第一频谱波形；
获取经由第二晶元组对待检测血管进行检测得到的第二频谱波形；
根据第一频谱波形和第二频谱波形确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系；
根据确定的关系对第一频谱波形和第二频谱波形进行调整；
根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值。
第二方面，本申请实施例提供了一种多普勒血流检测装置，用于实现上述第一方 面中任意一项的利用双晶元组确定血流速度的方法。
本申请实施例所提供的利用双晶元组确定血流速度的方法和多普勒血流检测装置，其中，多普勒血流检测装置包括用于放置在待检测血管不同位置处的第一晶元组和第二晶元组；该方法包括：获取经由第一晶元组对待检测血管进行检测得到的第一频谱波形；获取经由第二晶元组对待检测血管进行检测得到的第二频谱波形；根据第一频谱波形和第二频谱波形确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系；根据确定的关系对第一频谱波形和第二频谱波形进行调整；根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值。如此，避免了由于实际测量中探头与待检测血管之间的夹角与装置中设定的多普勒夹角不一致的情况所带来的误差问题，提高了血流速度测量值的准确性。
本申请附加的方面和优点将在下面的描述中部分给出，部分将从下面的描述中变得明显，或通过本申请的实践了解到。
附图说明
此处所说明的附图用来提供对本申请的进一步理解，构成本申请的一部分，本申请的示意性实施例及其说明用于解释本申请，并不构成对本申请的不当限定。在附图中：
图1为本申请一实施例提供的多普勒血流检测装置的结构框图；
图2为本申请一实施例提供的利用双晶元组确定血流速度的方法的流程示意图；
图3为一具体应用中采用多普勒血流检测装置对待检测血管进行检测时的位置示意图；
图4为一具体应用中频谱波形处理流程图；
图5为滚转角不等于90°时三轴加速度传感器与待检测血管的位置关系示意图；
图6为偏航角、俯仰角和滚转角的示意图；
图7为在有滚转角误差时和在无滚转角误差时对待检测血管进行检测的位置示意图；
图8为本申请一具体示例提供的利用超声波确定第一距离的原理示意图；
图9为本申请一具体示例提供的利用超声波确定第一距离的电路框图；
图10为本申请一具体示例提供的利用超声波确定第一距离的流程示意图；
图11为本申请一具体示例提供的采用包括第一接收晶元和第二接收晶元的第一晶元组和/或第二晶元组对待检测血管进行检测时的位置示意图。
具体实施方式
为使本发明的技术方案和有益效果能够更加明显易懂，下面通过列举具体实施例的方式进行详细说明。其中，附图不一定是按比例绘制的，局部特征可以被放大或缩小，以更加清楚的显示局部特征的细节；除非另有定义，本文所使用的技术和科学术语与本申请所属的技术领域中的技术和科学术语的含义相同。
除另作定义外，本申请所涉及的技术术语或者科学术语应具有本申请所属技术领域具备一般技能的人所理解的一般含义。在本申请中的“一”、“一个”、“一种”、“该”、“这些”等类似的词并不表示数量上的限制，它们可以是单数或者复数。在本申请中所涉及的术语“包括”、“包含”、“具有”及其任何变体，其目的是涵盖不排他的包含；例如，包含一系列步骤或模块(单元)的过程、方法和系统、产品或设备并未限定于列出的步骤或模块(单元)，而可包括未列出的步骤或模块(单元)，或者可包括这些过程、方法、产品或设备固有的其他步骤或模块(单元)。在本申请中所涉及的“多个”是指两个或两个以上。“和/或”描述关联对象的关联关系，表示可以存在三种关系，例如，“A和/或B”可以表示：单独存在A，同时存在A和B，单独存在B这三种情况。在本申请中所涉及的术语“第一”、“第二”、“第三”等，只是对相似对象进行区分，并不代表针对对象的特定排序。
本申请中，患者指的是正在接受或者可能接受多普勒血流检测装置的检测的任何人，患者也可被称为病人。医护人员，例如包括使用多普勒血流检测装置对患者进行监测的人，因而，也作为使用多普勒血流检测装置的用户之一；但，用户不仅可以包括医护人员，还可以包括其他直接或间接使用多普勒血流检测装置的人员。
本申请实施例提供了一种利用双晶元组确定血流速度的方法，应用于多普勒血流检测装置。首先，请参考图1，图1示出了本申请一实施例提供的多普勒血流检测装置的结构。如图所示，多普勒血流检测装置，包括：探头，信号处理模块，以及装置主体模块。具体的，探头可以包括第一晶元组和第二晶元组。其中，第一晶元组和第二晶元组分别与信号处理模块连接，从而将探测到的信号传输至信号处理模块；信号处理模块在接收到由各晶元组传输的信号后，对上述信号进行处理。具体地，信号处理模块包括滤除电路1、滤除电路2、信号解调1、信号解调2、ADC1、以及ADC2；第一晶元组与信号处理模块中的滤除电路1连接，第二晶元组与信号处理模块中的滤除电路2连接，滤除电路1和滤除电路2分别对第一晶元组和第二晶元组探测到的信号进行滤波处理；滤除电路1与信号解调1连接，滤除电路2与信号解调2连接，信号解调1和信号解调2分别对经滤除电路1和滤除电路2滤波处理后的信号进行解调处理；信号解调1与ADC1连接，信号解调2与ADC2连接，ADC1和ADC2分别对经信号解调1和信号解调2解调处理后的信号进行模数转换处理。经信号处理模块处理后的信号传输至处理器。为了存储接收到的检测结果，以及存储运算过程中的中间量和算法程序，该装置中还包括与处理器连接的存储模块，如内存、存储器等。当然，该装置中还可以包括网络口。
通讯接口为和其它智能设备的通讯提供接口，以进行数据的传输，实现反馈。通讯接口可以是USB/UART/网口/蓝牙/WIFI/CAN等常用的通讯硬件接口，本申请对其不做具体限制。
此外，该装置还可以包括音频功放以及与音频功放连接的喇叭。喇叭可以用于对 处理器确定的结果进行音频输出以及对需要提醒用户的信息进行音频输出。
本具体示例中，该装置还可以包括输入设备；其中，输入设备包含但不限于以下至少之一：键盘、按键、声控输入装置、触摸屏。可以理解的是，其他能够实现信号输入的设备均包含在本申请的含义中。此外，该装置还可以包括输出设备；其中，输出设备包含但不限于LCD显示屏。当然，其他能够实现信号输出的设备也均包含在本申请的含义中。如此，该装置能够实现与用户的信息交互。
本申请实施例提供的利用双晶元组确定血流速度的方法，应用于多普勒血流检测装置，多普勒血流检测装置包括用于放置在待检测血管不同位置处的第一晶元组和第二晶元组。在实际应用中，第一晶元组和第二晶元组共同设置在探头内。其中，多普勒血流检测装置例如为图1所示的多普勒血流检测装置。
请参考图2，该利用双晶元组确定血流速度的方法包括：
步骤201、获取经由第一晶元组对待检测血管进行检测得到的第一频谱波形；
步骤202、获取经由第二晶元组对待检测血管进行检测得到的第二频谱波形；
步骤203、根据第一频谱波形和第二频谱波形确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系；
步骤204、根据确定的关系对第一频谱波形和第二频谱波形进行调整；
步骤205、根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值。
其中，第一晶元组和第二晶元组用于放置在待检测血管不同位置处，例如，第一晶元组和第二晶元组中的一者放置在待检测血管的第一位置处，而另一者放置在待检测血管的第二位置处，第一位置和第二位置分别为沿血流运动方向上待检测血管的前后两个位置，即血流运动方向为由第一位置至第二位置的方向。应当理解，待检测血管被皮肤包裹，第一晶元组和第二晶元组显然并不是直接与待检测血管接触，本文所述的第一晶元组和第二晶元组放置在待检测血管不同位置处，指的是第一晶元组和第二晶元组隔着皮肤放置在与待检测血管对应的不同位置处。
第一频谱波形和第二频谱波形分别为经由第一晶元组和第二晶元组对待检测血管进行检测得到的频谱波形，而第一晶元组和第二晶元组用于放置在待检测血管不同位置处。图3为一具体应用中采用多普勒血流检测装置对待检测血管进行检测时的位置示意图，图中简易示出了待检测血管的位置以及第一晶元组和第二晶元组发射信号的位置。图中实线表示检测时的实际多普勒夹角与多普勒血流检测装置中设定的多普勒夹角一致的情况，即实际多普勒夹角等于设定的多普勒夹角α(具体为发射角，因此下文也可能称为发射角α)。然而在实际测量中，往往难以保证实际多普勒夹角与设定的多普勒夹角完全一致，即会产生测量误差。图中虚线示出了实际多普勒夹角与多普勒血流检测装置中设定的多普勒夹角不一致的情况，设检测时的实际多普勒夹角与α之间的偏差角度为r；则此时，对于第一晶元组而言，实际多普勒夹角等于α+r；对于第 二晶元组而言，实际多普勒夹角等于α-r。可以理解的，如果仅采用第一晶元组或者仅采用第二晶元组，那么获得的血流速度测量值V是实际血流速度V0在相应的晶元组发射或接收信号的方向上的垂直分量，因此V＝V0/cosα。那么，如果偏差角度r为1°，则测量误差△V＝V0/cosα-V0/cos(α±1)。由此可见，设定的多普勒夹角越大，产生的误差就越大。
为了减小误差，本申请实施例所应用的多普勒血流检测装置包括上述第一晶元组和第二晶元组，通过第一晶元组和第二晶元组实现两路多普勒通道采集，由于第一晶元组和第二晶元组在待检测血管上的放置位置不同，从而两路多普勒通道采集具有两个多普勒夹角，根据两个多普勒夹角分别获得两组采集数据，根据两组采集数据可以得到两种频谱波形。请参考图4，这里将接收第一晶元组采集数据的通道称为“通道1”，将接收第二晶元组采集数据的通道称为“通道2”，通过通道1和通道2获得的频谱波形如图4中(a)所示。
其中，第一晶元组中包括至少一个发射晶元和至少一个接收晶元，第二晶元组中同样包括至少一个发射晶元和至少一个接收晶元。第一晶元组和第二晶元组同步发射和采样。第一频谱波形和第二频谱波形对应的测量时间相同。
由于第一频谱波形和第二频谱波形是对同一待检测血管在同一时刻进行测量得到的频谱波形，因此二者之间的差异是由于第一晶元组和第二晶元组的实际多普勒夹角不同所导致的。可以理解的，若在理想状态下(即检测时的实际多普勒夹角与多普勒血流检测装置中设定的多普勒夹角一致)，第一晶元组检测时的实际多普勒夹角和第二晶元组检测时的实际多普勒夹角应当是相同的，二者均等于设定的多普勒夹角。如此，根据第一频谱波形和第二频谱波形可以确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系。
作为一种可选的实施方式，根据第一频谱波形和第二频谱波形确定检测时的实际多普勒夹角和多普勒血流检测装置中设定的多普勒夹角之间的关系，包括：根据第一频谱波形确定第一峰值；根据第二频谱波形确定第二峰值；根据第一峰值和第二峰值确定检测时的实际多普勒夹角和设定的多普勒夹角之间满足如下关系：cos(α+r)/cos(α-r)＝Vm1/Vm2，其中，Vm1为第一峰值，Vm2为第二峰值，α为设定的多普勒夹角，r为检测时的实际多普勒夹角与α之间的偏差角度；α+r和α-r分别为第一晶元组和第二晶元组检测时的实际多普勒夹角。
进一步地，根据第一频谱波形确定第一峰值的步骤，和/或根据第二频谱波形确定第二峰值的步骤，可以包括：根据频谱波形确定多个周期的多个峰值；使用拉依达准则剔除多个峰值中的异常值；对于剔除异常值后剩余的峰值计算平均值。
容易理解的，若根据第一频谱波形确定第一峰值的步骤包括根据第一频谱波形确定多个周期的多个峰值并使用拉依达准则剔除异常值，那么对于剔除异常值后剩余的峰值计算平均值得到第一平均值，将该第一平均值确定为第一峰值。类似地，若根据 第二频谱波形确定第二峰值的步骤包括根据第二频谱波形确定多个周期的多个峰值并使用拉依达准则剔除异常值，那么对于剔除异常值后剩余的峰值计算平均值得到第二平均值，将该第二平均值确定为第二峰值。
请继续参考图4，在一具体应用中，可先将第一频谱波形的波形翻转。翻转通道1的数据如图4中(b)所示。
为了更为准确地确定各频谱波形的峰值，可以选择5个周期，并将选择的5个周期中各周期的峰值计算出来，得到5个峰值。接下来，使用拉依达准则剔除5个峰值中的异常值。当然，该步骤仅意味着使用拉依达准则执行了剔除异常值的操作，并不意味着必然有异常值被剔除。换言之，若5个峰值中没有异常值，则5个峰值全部被保留。接下来，对剔除异常值后剩余的峰值求取平均值。当然，该步骤仅意味着执行了求取平均值的操作，如果剔除异常值后仅剩余一个峰值，那么求取平均值的结果即为该峰值。
进一步的，可以针对第一频谱波形和第二频谱波形均执行上述步骤，从而分别获得平均值，并将各自的平均值对应确定为第一峰值Vm1和第二峰值Vm2。
接下来，根据关系式cos(α+r)/cos(α-r)＝Vm1/Vm2，可以计算出r。r为检测时的实际多普勒夹角与α之间的偏差角度，也可以简称为倾斜角。进一步地，根据r可以对通道1和通道2的数据进行相应的调整，该步骤也可以被称为修正。
具体地，根据确定的关系对第一频谱波形和第二频谱波形进行调整，可以包括：根据如下公式对第一频谱波形和第二频谱波形进行调整：Vm1’＝Vm1*cosα/cos(α+r)，Vm2’＝Vm2*cosα/cos(α-r)，其中，Vm1为第一峰值，Vm2为第二峰值，Vm1’为调整后的第一频谱波形对应的峰值，Vm2’为调整后的第二频谱波形对应的峰值，α为设定的多普勒夹角，r为检测时的实际多普勒夹角与α之间的偏差角度；α+r和α-r分别为第一晶元组和第二晶元组检测时的实际多普勒夹角。
在实际操作中，具体根据确定的关系对第一频谱波形和第二频谱波形进行相应比例的缩放，从而获得修正后的频谱波形，请参考图4中(c)。经过修正后的两个频谱波形高度近似。
作为一种可选的实施方式，根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值，包括：将调整后的第一频谱波形和调整后的第二频谱波形进行频谱重叠，得到重叠后的频谱波形；根据重叠后的频谱波形确定血流速度测量值。
其中，重叠后的频谱波形可参考图4中(d)。重叠后的频谱波形进一步将第一晶元组的检测结果与第二晶元组的检测结果融合，从而可以中和掉二者的角度误差。根据重叠后的频谱波形确定血流速度测量值可以采用本领域已有的技术手段执行，本申请对此不做具体限定。
可以理解的，如此获得的血流速度测量值更加贴近实际血流速度，基本去除了由于实际测量中探头与待检测血管之间的夹角与设定的多普勒夹角不一致的情况所带来 的误差，从而提高了血流速度测量值的准确性。
在具体应用中，第一晶元组和第二晶元组中发射晶元发射的信号的频率不同，从而多普勒血流检测装置为双频双通道异常探头检测装置。
可选的，第一晶元组和第二晶元组发射的信号的频率在1MHz-16MHz的范围内，以满足双频双通道检测的需求。进一步地，第一晶元组和第二晶元组发射的信号的频率在2MHz-8MHz的范围内，检测结果的准确性更好。
为了提高检测结果的准确性，第一晶元组发射的信号的频率F1和第二晶元组发射的信号的频率F2满足如下关系：1、F1<F2，2、F2取F1的余数大于0.5MHz，3、F2<3F1。
其中，F2取F1的余数大于0.5MHz，也可以表示成F2％F1>0.5MHz。取余数就是取出不能整除的多出来的部分；具体地，如果F2＝nF1+x，其中，n为正整数，x<F1，则F2取F1的余数等于x。
作为一种较佳的示例，F1＝2.1MHz-2.7MHz，F2＝3.8MHz-4.3MHz。
在一具体示例中，第一晶元组和第二晶元组的信号滤波中做限波滤波器，其中之一的带宽的范围为F1-0.5MHz～F1+0.5MHz；其中另一的带宽范围为F2-0.5MHz～F2+0.5MHz。如此，不同的通道设置不同的滤波带宽。在双通道同时发射时，两侧的接收晶元都能够接收到两个发射晶元的信号，也就是互相会有干扰，在本具体示例中，选择了对应通道对应频段的滤波，可以把另外一个频段的信号抑制，达到更好的信噪比。
通过滤波和解调技术去除两个通道中的超声波干扰。
可以理解地，第一晶元组和第二晶元组设置在多普勒血流检测装置的探头内，并且二者可以设置在同一探头内。但需要说明的是，本申请实施例也不排除二者分别设置在两个探头内的情况。如果二者分别设置在两个探头内，则两个探头之间存在机械连接关系，从而两个探头之间的位置相关联，以保证在出现偏差角度时，二者的偏差角度分别为±r。
作为一种可选的实施方式，该方法还包括：确定探头在检测状态下的滚转角，滚转角为探头中发射晶元发射的声场在水平面上的投影方向与待检测血管中血流运动方向之间的夹角，发射晶元为第一晶元组和/或第二晶元组中的发射晶元；根据滚转角对血流速度测量值进行修正，得到修正后的血流速度测量值。
在具体应用中，多普勒血流检测装置还包括设置在探头内的姿态传感器(图1中未示出)；确定探头在检测状态下的滚转角，包括：利用姿态传感器确定探头在检测状态下的滚转角。
姿态传感器是一种高性能的三维运动姿态测量仪器。姿态传感器可以包括以下至少之一：三轴加速度传感器、陀螺仪、三轴电子罗盘等运动传感器。
作为一种可选的实施方式，姿态传感器包括三轴加速度传感器；确定探头在检测 状态下的滚转角，包括：基于三轴加速度传感器获得在检测状态下重力加速度在相互垂直的三个坐标轴方向上的加速度分量；根据加速度分量确定滚转角。
在具体应用中，开始进行血流速度的测量时，用户将探头按照预先规定的使用方式放置在测量位置，其中，预先规定的使用方式例如为保证探头中发射晶元发射的声场在水平面上的投影方向与待检测血管中血流运动方向相垂直，不产生离散角，从而减小测量误差。在测量的过程中，可以认为病人是静止的。此时可以记录三轴加速度传感器的初始输出值，为后续计算得到的滚转角做参考。
可以理解的，以待检测血管位于水平面内为例，如果三轴加速度传感器的芯片是水平放置的，并且以三轴加速度传感器的方向建立包括XYZ三个坐标轴的直角坐标系，那么重力加速度g在X轴和Y轴方向的分量均为0，在Z轴方向的分量为g。
而在实际测量时，特别是长时间的监测中，很可能会出现由于病人移动导致探头中发射晶元发射的声场在水平面上的投影方向与待检测血管中血流运动方向不垂直的情况，从而造成测量误差。
图5示出了滚转角不等于90°时三轴加速度传感器与待检测血管的位置关系，由于三轴加速度传感器位于探头内，因此图5也即探头中发射晶元发射的声场在水平面上的投影方向与待检测血管中血流运动方向不垂直的情况三轴加速度传感器与待检测血管的位置关系。如图所示，重力加速度g在X轴方向的分量为Ax，Ax与待检测血管101之间的夹角为a1，与重力加速度g的夹角为a；重力加速度g在Y轴方向的分量为Ay，Ay与待检测血管101之间的夹角为b1，与重力加速度g的夹角为b；重力加速度g在Z轴方向的分量为Az，Az与待检测血管101之间的夹角为γ1，与重力加速度g的夹角为γ。其中，各个角度之间的关系为：a＝90°-a1，b＝90°-b1，γ＝90°-γ1。
重力加速度g在各轴方向上的分量为：Ax＝gcosa，Ay＝gcosb，Az＝gcosγ；或者：Ax＝gsina1，Ay＝gsinb1，Az＝gsinγ1。
进一步的：
g*g＝Ax*Ax+gcosa1*gcosa1；
gcosa1＝squr(g*g-Ax*Ax)；
同理可知，
gcosb1＝squr(g*g-Ay*Ay)；
gcosγ1＝squr(g*g-Az*Az)。
在立体几何中，g相当于立方体的对角线，Ax、Ay、Az相当于三条边，所以根据勾股定理：Ax*Ax+Ay*Ay+Az*Az＝g*g。
以X轴为例，sina1＝Ax/g，cosa1＝squr(g*g-Ax*Ax)/g；
tana1＝Ax/squr(g*g-Ax*Ax)＝Ax/squr(Ay*Ay+Az*Az)。
同理可知，
tanb1＝Ay/squr(Ax*Ax+Az*Az)；
tanγ1＝Az/squr(Ax*Ax+Ay*Ay)。
由此得出了三轴加速度传感器的测量值与a1、b1和γ1之间的关系。这里，a1、b1和γ1的值与对应的弧度值相等。
接下来，计算各轴与水平线(参考图中待检测血管101)之间的弧度值，其中，采用a11、b11、γ11分别代表X轴方向、Y轴方向、Z轴方向与水平线之间的弧度值；则：
a11＝arctan(Ax/squr(Ay*Ay+Az*Az))；
b11＝arctan(Ay/squr(Ax*Ax+Az*Az))；
γ11＝arctan(Az/squr(Ax*Ax+Ay*Ay))。
接下来使用以下公式进行计算：弧度＝角度值*πR/180；即，角度值＝弧度*180/πR，其中R取1。最后得到各轴的角度值分别为：
φ＝a11*180/π＝[arctan(Ax/squr(Ay*Ay+Az*Az))]*180/π；
ψ＝b11*180/π＝[arctan(Ay/squr(Ax*Ax+Az*Az))]*180/π；
θ＝γ11*180/π＝[arctan(Az/squr(Ax*Ax+Ay*Ay))]*180/π；
其中，ψ为弧度值b11对应的角度值，θ为弧度值γ11对应的角度值，φ为弧度值a11对应的角度值；φ即为滚转角。
可以理解的，相互垂直的三个坐标轴方向根据三轴加速度传感器在测量状态下的方向建立，三轴加速度传感器与发射晶元共同位于探头内，因此，三轴加速度传感器所处的方向可以代表发射晶元所处的方向；故，根据加速度分量能够确定出发射晶元发射的声场在水平面上的投影方向与血流运动方向之间的夹角。
作为另一种可选的实施方式，姿态传感器包括陀螺仪；确定探头在检测状态下的滚转角，包括：基于陀螺仪获得在检测状态下的滚转角。
图6为偏航角、俯仰角和滚转角的示意图；其中，(a)示出了偏航角ψ，(b)示出了俯仰角θ，(c)示出了滚转角φ。将运动物体的空间轨迹分解为沿Z、Y、X三轴的独立运动，运动矢量在每个轴向的分量由该矢量与各轴之间夹角的余弦表示。其中，运动物体例如为姿态传感器。方向余弦共九个参数，可以用一个3阶方向余弦矩阵来表示。分量形式如下：
运动物体的3次的欧拉旋转可以用三个方向余弦矩阵表示：


余弦矩阵的乘积用来表示从地理坐标系到运动物体坐标系的变换：


在得到运动物体坐标系相对于地理坐标系的姿态更新矩阵后，就可以将姿态传感器获取的角速率数据转换为姿态角数据。
表示加速度计在各轴方向上感测的重力分量，[0 0 1]表示地理坐标系下在加速度计各轴测量重力场的分量。
利用反三角函数可以得到倾斜角(滚转角φ和俯仰角θ)：

在实际使用中，根据人体的特性，可认为Z轴方向和待检测血管方向的相对角度是不变化的，即γ和γ1保持不变，即俯仰角不变，只需要利用滚转角φ进行角度修正。
可以理解的，当人体变化位置时，姿态传感器和待检测血管的位置是同步变化的。在多普勒效应中，起作用的是和待检测血液中血流运动方向所在的平面平行的夹角。
在本实施例中，已经根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值；接下来对血流速度测量值进行修正，得到修正后的血流速度测量值。 具体地，采用以下公式进行修正：V1＝V/sinφ；其中，V1表示修正后的血流速度测量值，V表示修正前的血流速度测量值，φ表示滚转角。
请参考图7，在按照预先规定的使用方式将探头放置在测量位置时，滚转角φ等于90°，此时测量结果无滚转角误差。而在有滚转角误差时，即探头发生转动后，按照速度分量的原理，此时获得的血流速度测量值是无滚转角误差应时应当获得的血流速度测量值在转动后方向上的速度分量，因此通过公式V1＝V/sinφ可以获得修正后的血流速度，即或者理论上等于无滚转角误差应时应当获得的血流速度测量值的修正值。
可以理解的，在滚转角φ等于90°时，根据上述公式V1＝V/sinφ，计算可得V1＝V，进一步说明此时测量结果无滚转角误差。
本实施例通过对步骤205确定的血流速度测量值进行修正，进一步提高了待输出的血流速度测量值的准确性。可选的，可以将血流速度测量值的修正值作为输出值而输出。
作为一种可选的实施方式，步骤201和/或步骤202可以包括：获取发射角，发射角为第一晶元组和/或第二晶元组中发射晶元发射信号的方向与待检测血管中血流运动方向之间的夹角；获取多普勒血流检测装置中位于同一晶元组中的发射晶元和接收晶元之间的距离以及发射晶元与待检测血管之间的距离；根据发射角、发射晶元和接收晶元之间的距离、以及发射晶元与待检测血管之间的距离确定接收角，接收角为第一晶元组和/或第二晶元组中接收晶元接收信号的方向与血流运动方向之间的夹角；根据发射角和接收角确定第一频谱波形和/或第二频谱波形。
如此，通过先根据发射角、发射晶元和接收晶元之间的距离、以及发射晶元与待检测血管之间的距离确定接收角，再利用发射角和接收角确定频谱波形，可以获得更为准确的频谱波形。尤其针对待检测血管为浅表的血管，比如人体颈动脉等情形，采用本实施方式可以获得更贴近真实情况的结果。
其中，获取发射角具体可以包括：获取多普勒血流检测装置中预先存储的发射角α(即设定的多普勒夹角)。可以理解的，发射角α的具体数值可以是多普勒血流检测装置在设计时就确定下来的固定角度值。
获取多普勒血流检测装置中位于同一晶元组中的发射晶元T和接收晶元R之间的距离D，具体可以包括：获取多普勒血流检测装置中预先存储的位于同一晶元组中的发射晶元T和接收晶元R之间的距离D。该D值也可以是多普勒血流检测装置在设计时就确定下来的固定值。
发射晶元T与待检测血管101之间的距离包括第一距离L，第一距离L为沿发射晶元T发射信号的方向上发射晶元T到待检测血管101的距离；根据发射角α、发射晶元T和接收晶元R之间的距离D、以及发射晶元T与待检测血管101之间的距离L确定接收角β，包括采用以下公式确定接收角β：|β-α|＝arctan(D/L)；其中，β为接收角，α为发射角，|β-α|为接收角与发射角之间的差值的绝对值，D为发射晶元 和接收晶元之间的距离，L为第一距离。
请参考图8，示例性的，获取发射晶元T与待检测血管101之间的距离，包括：获取发射晶元T发射信号至接收晶元R接收信号所需的时长t；根据所需的时长t以及信号的传播速度c确定信号在所需的时长内传播的距离；根据传播的距离确定第一距离L。
实际应用中，获取发射晶元T与待检测血管101之间的距离可以通过A超、B超等技术测量实现。请继续参考图8，发射器T例如为超声发射器，接收器R例如为超声接收器，障碍物例如为待检测血管；发射器T向障碍物发射一小段固定频率的超声波，并在开始发射时进行计时，超声波在物体中有传播的速度c和时间，被障碍物反射后进入到接收器R，从发射到接收的时间可测得为t，超声波在物体中的传播速度为c，则可以计算得到测量距离，根据测量距离可以估算出实际距离。可以通过以下公式确定第一距离：L＝c*t/2。
具体的，可以使用原采集电路和传感器的组成，采用PW脉冲波多普勒的方式进行多普勒的采集，并在每个发生周期记录发射到接收的时间差，从而计算测量距离和角度。此方法使用时域数据进行分析计算。
由于超声波在人体组织中的传播速度c＝1570m/s＝1570000mm/s，颈部的血管深度在5mm-30mm之间(即H在5mm-30mm之间)，L的范围在7mm-42mm之间。T的范围在7/1570000～42/1570000s，7/1570～42/1570ms，4.5μs～27μs之间。使用的超声频率可以在2MHz～8MHz，具体地，超声频率为4MHz。以超声频率为4MHz为例，每个发射周期的时长为1/4MHz＝0.25μs；那么，发射5个超声周期，总计发射时长为1.25μs，这能够满足采样间隔时间。
图9为本申请一具体示例提供的利用超声波确定第一距离的电路框图；图10为本申请一具体示例提供的利用超声波确定第一距离的流程示意图。
首先，请参考图9。图中电路为总体电路中信号调理部分中的一部分，专门用来进行距离测试。其中，发生控制电路、信号解调和信号放大部分共用。在进行距离测试时，发生控制电路控制发射晶元发出信号，接收晶元接收到信号后，由信号解调和信号放大分别对信号进行解调和放大处理；其中，接收到信号会被输入到ADC(图中未示出)中进行采集。在进行距离测试时，信号进入模拟比较器进行比较，模拟比较器输出为数字信号，直接由处理器的I/O管脚采集。
接下来，请参考图10。利用超声波确定第一距离的流程包括：在开始距离测试后，发射晶元发射超声波信号，并且开始计时，关闭发射；超声波信号通过组织传输到血液相撞，发生多普勒效应后反射至接收晶元，接收晶元对超声波信号进行i/q解调，解调信号输出为微弱的模拟信号，信号放大电路把信号放大至设定的范围。当血流速度越大时，信号会越大。设定一个比较电压V0，当信号大于V0时，模拟比较器输出为1；当信号小于V0时，模拟比较器输出为0。
确定每一个测距周期的方法为：从发射晶元发射超声波信号并开始计时，如果模拟比较器输出从0转为1，则认为是该周期测得的超声传输时间。具体地，判断比较器触发的结果为是还是否，如果结果为是，则记录时间N；如果结果为否，则等待时间到，直至总采集时间到。
由于在一个脉动周期中，动态血流的速度是从小到大再转小，从设计电路中，血流速度越大，信号越大，会越早的触发模拟比较器，这种情况下测得的时间越准确。所以，可选的，设定一个时间段，如，2s-5s的测量时间，优选为3s，保证在一次测量时间中能够测得最大的血流状态下的信号。3s的情况下，被测患者的脉搏是20bpm，能够满足到临床的要求。
如图10所示，从发射超声波到总采集时间到，记录的时间从小到大排序，去除异常点，选择三个最小的时间取平均，距离测试结束。
根据公式L＝c*t/2，确定第一距离。再通过如下公式计算得到接收角：|β-α|＝arctan(D/L)。
作为另一种可选的实施方式，获取发射晶元T与待检测血管101之间的距离，包括：获取由用户基于输入设备输入的第二距离H，第二距离H为沿垂直于皮肤表面的方向上发射晶元T到待检测血管101的距离；根据第二距离H确定第一距离L，其中采用以下公式确定第一距离L：L＝H/sinα；其中，H为第二距离。
其中，第二距离H例如由医护人员输入至多普勒血流检测装置中。
接下来，请参考图11。可选的，位于第一晶元组和/或第二晶元组中的接收晶元包括第一接收晶元R1和第二接收晶元R2，第一接收晶元R1和第二接收晶元R2接收同一发射晶元T发射的信号，发射晶元T和第一接收晶元R1之间的距离D1与发射晶元T和第二接收晶元R2之间的距离D2相同；根据发射角、发射晶元和接收晶元之间的距离、以及发射晶元与待检测血管之间的距离确定接收角，包括：确定第一接收角β1和第二接收角β2；其中，第一接收角β1为第一接收晶元R1接收信号的方向与血流运动方向之间的夹角，第二接收角β2为第二接收晶元R2接收信号的方向与血流运动方向之间的夹角；根据发射角和接收角确定血流速度测量值，包括：根据发射角α和第一接收角β1确定第一血流速度测量值V10；根据发射角α和第二接收角β2确定第二血流速度测量值V20；根据第一血流速度测量值V10和第二血流速度测量值V20确定血流速度测量值V。
其中，发射晶元T和第一接收晶元R1之间的距离D1与发射晶元T和第二接收晶元R2之间的距离D2相同，所以α-β2≈β1-α，设此角度差值为ε。发射晶元T发射信号时，第一接收晶元R1和第二接收晶元R2能够同时接收到信号。那么，第一接收晶元R1和第二接收晶元R2对应的速度分量相等，Δf1＝Δf2＝Δf*cosε。
假设α＝60°，通过ε＝9.823°，因此β1＝α+ε＝69.823°，β2＝α-ε＝50.177°。
令△f*c/2f＝A；
则如果不考虑发射角和接收角之间的差异，实际应当检测得到的血流速度V11＝△f*c/(2f*cosα)＝A/cosα＝A/0.5＝2A；
而在本方法中，根据第一血流速度测量值V10和第二血流速度测量值V20确定血流速度测量值V。具体地，例如将第一血流速度测量值V10和第二血流速度测量值V20的平均值确定为血流速度测量值V。那么，
V10＝△f*c/(f*(cosα+cosβ1))＝2A/(cos60°+cos69.823°)＝2.332A；
V20＝△f*c/(f*(cosα+cosβ2))＝2A/(cos60°+cos50.177°)＝1.748A；
则V＝(V1+V2)/2＝2.04A。
如此，使用本方法可以减小误差。且β越小时，误差越小。
在此基础上，本申请实施例还提供了一种多普勒血流检测装置，用于实现上述实施例中任意一项的利用双晶元组确定血流速度的方法。
应当理解，关于多普勒血流检测装置的各细节技术特征可以参考上述利用双晶元组确定血流速度的方法实施例中的相关描述，此处不再赘述。
应该理解，虽然本申请各流程图中的各个步骤按照箭头的指示依次显示，但是这些步骤并不是必然按照箭头指示的顺序依次执行。除非本文中有明确的说明，这些步骤的执行并没有严格的顺序限制，这些步骤可以以其它的顺序执行。而且，图中的至少一部分步骤可以包括多个步骤或者多个阶段，这些步骤或者阶段并不必然是在同一时刻执行完成，而是可以在不同的时刻执行，这些步骤或者阶段的执行顺序也不必然是依次进行，而是可以与其它步骤或者其它步骤中的步骤或者阶段的至少一部分轮流或者交替地执行。
应当理解，以上实施例均为示例性的，不用于包含权利要求所包含的所有可能的实施方式。在不脱离本公开的范围的情况下，还可以在以上实施例的基础上做出各种变形和改变。同样的，也可以对以上实施例的各个技术特征进行任意组合，以形成可能没有被明确描述的本发明的另外的实施例。因此，上述实施例仅表达了本发明的几种实施方式，不对本发明专利的保护范围进行限制。

Claims (17)

  1. 一种利用双晶元组确定血流速度的方法，应用于多普勒血流检测装置，所述多普勒血流检测装置包括用于放置在待检测血管不同位置处的第一晶元组和第二晶元组；所述方法包括：
    获取经由所述第一晶元组对所述待检测血管进行检测得到的第一频谱波形；
    获取经由所述第二晶元组对所述待检测血管进行检测得到的第二频谱波形；
    根据所述第一频谱波形和所述第二频谱波形确定检测时的实际多普勒夹角和所述多普勒血流检测装置中设定的多普勒夹角之间的关系；
    根据确定的所述关系对所述第一频谱波形和所述第二频谱波形进行调整；
    根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值。
  2. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述根据所述第一频谱波形和所述第二频谱波形确定检测时的实际多普勒夹角和所述多普勒血流检测装置中设定的多普勒夹角之间的关系，包括：
    根据所述第一频谱波形确定第一峰值；
    根据所述第二频谱波形确定第二峰值；
    根据所述第一峰值和所述第二峰值确定检测时的实际多普勒夹角和所述设定的多普勒夹角之间满足如下关系：
    cos(α+r)/cos(α-r)＝Vm1/Vm2，
    其中，Vm1为第一峰值，Vm2为第二峰值，α为设定的多普勒夹角，r为检测时的实际多普勒夹角与α之间的偏差角度；α+r和α-r分别为所述第一晶元组和所述第二晶元组检测时的实际多普勒夹角。
  3. 根据权利要求2所述的利用双晶元组确定血流速度的方法，其中，所述根据所述第一频谱波形确定第一峰值的步骤，和/或所述根据所述第二频谱波形确定第二峰值的步骤，包括：
    根据频谱波形确定多个周期的多个峰值；
    使用拉依达准则剔除多个所述峰值中的异常值；
    对于剔除异常值后剩余的峰值计算平均值。
  4. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述根据确定的所述关系对所述第一频谱波形和所述第二频谱波形进行调整，包括：
    根据如下公式对所述第一频谱波形和所述第二频谱波形进行调整：
    Vm1’＝Vm1*cosα/cos(α+r)，
    Vm2’＝Vm2*cosα/cos(α-r)，
    其中，Vm1为第一峰值，Vm2为第二峰值，Vm1’为调整后的第一频谱波形对应的峰值，Vm2’为调整后的第二频谱波形对应的峰值，α为设定的多普勒夹角，r为检测时的实际多普勒夹角与α之间的偏差角度；α+r和α-r分别为所述第一晶元组和所述第二晶元组检测时的实际多普勒夹角。
  5. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述根据调整后的第一频谱波形和调整后的第二频谱波形确定血流速度测量值，包括：
    将调整后的第一频谱波形和调整后的第二频谱波形进行频谱重叠，得到重叠后的频谱波形；
    根据所述重叠后的频谱波形确定血流速度测量值。
  6. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述第一晶元组和所述第二晶元组发射的信号的频率在1MHz-16MHz的范围内。
  7. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述第一晶元组发射的信号的频率F1和所述第二晶元组发射的信号的频率F2满足如下关系：
    F1<F2，
    F2取F1的余数大于0.5MHz，
    F2<3F1。
  8. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述多普勒血流检测装置包括探头，所述第一晶元组和所述第二晶元组设置在所述探头内；所述方法还包括：
    确定所述探头在检测状态下的滚转角，所述滚转角为所述探头中发射晶元发射的声场在水平面上的投影方向与待检测血管中血流运动方向之间的夹角，所述发射晶元为所述第一晶元组和/或所述第二晶元组中的发射晶元；
    根据所述滚转角对所述血流速度测量值进行修正，得到修正后的血流速度测量值。
  9. 根据权利要求8所述的利用双晶元组确定血流速度的方法，其中，所述多普勒血流检测装置还包括设置在探头内的姿态传感器；所述确定所述探头在检测状态下的滚转角，包括：
    利用所述姿态传感器确定所述探头在检测状态下的滚转角。
  10. 根据权利要求9所述的利用双晶元组确定血流速度的方法，其中，所述姿态传感器包括三轴加速度传感器；所述确定所述探头在检测状态下的滚转角，包括：
    基于所述三轴加速度传感器获得在检测状态下重力加速度在相互垂直的三个坐标轴方向上的加速度分量；
    根据所述加速度分量确定所述滚转角。
  11. 根据权利要求9所述的利用双晶元组确定血流速度的方法，其中，所述姿态传感器包括陀螺仪；所述确定所述探头在检测状态下的滚转角，包括：
    基于所述陀螺仪获得在检测状态下的所述滚转角。
  12. 根据权利要求8所述的利用双晶元组确定血流速度的方法，其中，
    所述根据所述滚转角对所述血流速度测量值进行修正，得到修正后的血流速度测量值，包括采用以下公式得到修正后的血流速度测量值：
    V1＝V/sinφ；其中，V1表示修正后的血流速度测量值，V表示修正前的血流速度测量值，φ表示滚转角。
  13. 根据权利要求1所述的利用双晶元组确定血流速度的方法，其中，所述获取第一晶元组血流速度测量值和/或所述获取第二晶元组血流速度测量值，包括：
    获取发射角，所述发射角为所述第一晶元组和/或所述第二晶元组中发射晶元发射信号的方向与待检测血管中血流运动方向之间的夹角；
    获取所述多普勒血流检测装置中位于同一晶元组中的所述发射晶元和接收晶元之间的距离以及所述发射晶元与所述待检测血管之间的距离；
    根据所述发射角、所述发射晶元和接收晶元之间的距离、以及所述发射晶元与所述待检测血管之间的距离确定接收角，所述接收角为所述第一晶元组和/或所述第二晶元组中接收晶元接收信号的方向与血流运动方向之间的夹角；
    根据所述发射角和所述接收角确定所述第一频谱波形和/或所述第二频谱波形。
  14. 根据权利要求13所述的利用双晶元组确定血流速度的方法，其中，所述发射晶元与所述待检测血管之间的距离包括第一距离，所述第一距离为沿所述发射晶元发射信号的方向上所述发射晶元到所述待检测血管的距离；
    所述根据所述发射角、所述发射晶元和接收晶元之间的距离、以及所述发射晶元与所述待检测血管之间的距离确定接收角，包括采用以下公式确定接收角：
    |β-α|＝arctan(D/L)；其中，β为接收角，α为发射角，|β-α|为接收角与发射角之间的差值的绝对值，D为发射晶元和接收晶元之间的距离，L为第一距离。
  15. 根据权利要求14所述的利用双晶元组确定血流速度的方法，其中，获取所述发射晶元与所述待检测血管之间的距离，包括：获取所述发射晶元发射信号至所述接收晶元接收所述信号所需的时长；根据所述所需的时长以及所述信号的传播速度确定所述信号在所述所需的时长内传播的距离；根据所述传播的距离确定所述第一距离。
  16. 根据权利要求14所述的利用双晶元组确定血流速度的方法，其中，所述获取 所述发射晶元与所述待检测血管之间的距离，包括：
    获取由用户基于输入设备输入的第二距离，所述第二距离为沿垂直于皮肤表面的方向上所述发射晶元到所述待检测血管的距离；
    根据所述第二距离确定所述第一距离，其中采用以下公式确定所述第一距离：
    L＝H/sinα；其中，H为第二距离。
  17. 一种多普勒血流检测装置，其中，用于实现上述权利要求1至17中任意一项所述的利用双晶元组确定血流速度的方法。
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