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WO2018195944A1 - 超声成像设备及利用超声检测血管壁剪切指数的方法 - Google Patents

超声成像设备及利用超声检测血管壁剪切指数的方法 Download PDF

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Publication number
WO2018195944A1
WO2018195944A1 PCT/CN2017/082480 CN2017082480W WO2018195944A1 WO 2018195944 A1 WO2018195944 A1 WO 2018195944A1 CN 2017082480 W CN2017082480 W CN 2017082480W WO 2018195944 A1 WO2018195944 A1 WO 2018195944A1
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WIPO (PCT)
Prior art keywords
vessel wall
blood vessel
velocity
shear index
index
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Ceased
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PCT/CN2017/082480
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English (en)
French (fr)
Inventor
杜宜纲
沈莹莹
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Shenzhen Mindray Bio Medical Electronics Co Ltd
Original Assignee
Shenzhen Mindray Bio Medical Electronics Co Ltd
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Application filed by Shenzhen Mindray Bio Medical Electronics Co Ltd filed Critical Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority to CN202111316389.7A priority Critical patent/CN113967036B/zh
Priority to US16/608,625 priority patent/US11896427B2/en
Priority to PCT/CN2017/082480 priority patent/WO2018195944A1/zh
Priority to CN201780018341.3A priority patent/CN109069113B/zh
Publication of WO2018195944A1 publication Critical patent/WO2018195944A1/zh
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • A61B8/08—Clinical applications
    • A61B8/0891—Clinical applications 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
    • A61B8/06—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
    • A61B8/13—Tomography
    • A61B8/14—Echo-tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • 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
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • 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
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/467—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/467—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means
    • A61B8/469—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means for selection of a region of interest

Definitions

  • the present invention relates to an imaging method, and more particularly to an ultrasonic imaging apparatus and a method for detecting a blood vessel wall shear index using ultrasonic waves in the ultrasonic imaging apparatus.
  • Vascular wall shear index such as WSS (Wall Shear Stress) is a well-recognized parameter associated with arteriosclerosis in the medical community.
  • the vascular wall shear index is usually related to the gradient of the blood flow velocity component along the tangential direction of the vessel wall near the vessel wall. Therefore, when calculating or detecting the value of WSS, it is necessary to know the magnitude and direction of the blood flow velocity in the blood vessel so as to obtain the component value of the tangential direction along the blood vessel wall.
  • a traditional detection method is to detect the component of the blood flow along the direction of the ultrasonic wave by detecting the color Doppler using the Doppler principle, and it is difficult to obtain the component of the blood flow along the tangential direction of the blood vessel wall, so the WSS cannot be accurately measured. Therefore, the calculation method based on the traditional color ultrasound can only make a qualitative analysis of WSS.
  • Another traditional method of detection is to obtain the magnitude and direction of blood flow velocity by phase-contrast magnetic resonance angiography (PC-MRA), and then calculate WSS.
  • PC-MRA phase-contrast magnetic resonance angiography
  • the phase contrast magnetic resonance angiography-based detection method has a long inspection time and is expensive, and the examination also causes inconvenience to the patient and the doctor. For example, the examination comfort is poor, and ECG (Electrocardiograph) is required. ) Calibration, signals may be disturbed, etc.
  • the present invention provides an ultrasonic imaging apparatus and a method for detecting a blood vessel wall shear index by using ultrasonic waves, which can accurately detect a blood vessel wall shear index at a low cost.
  • the ultrasonic imaging apparatus disclosed in the embodiment of the invention comprises a probe, a transmitting circuit, a receiving circuit and a processor.
  • the transmitting circuit is for exciting the probe to emit ultrasonic waves to a region of interest comprising vascular tissue.
  • the receiving circuit is configured to receive an echo signal generated after the ultrasonic wave is emitted.
  • the processor is configured to: obtain an ultrasound image of the region of interest according to the echo signal; obtain a particle flow velocity of a plurality of points in the blood vessel according to the echo signal, where the particle velocity includes Blood flow Speed magnitude and direction; determining a blood vessel wall in the ultrasound image, and obtaining a position to be measured on the blood vessel wall; calculating a blood vessel wall shear index at the position to be measured according to a particle flow velocity at a plurality of points near the position to be measured; And controlling a display device to display an ultrasound image and a vessel wall shear index.
  • the transmitting circuit exciting the probe to transmit ultrasonic waves to the region of interest comprising the vascular tissue comprises transmitting a plurality of angularly deflected first ultrasonic waves in a multi-angle deflection emission, the processor receiving the plurality of ultrasonic waves according to the receiving circuit
  • the first echo signals reflected from the respective angles of the points respectively obtain the velocity components of each point along the respective angles, and the obtained velocity components of different angles of each point are respectively angle-fitted, and the plurality of points are synthesized. The velocity of the particle flow.
  • the ultrasonic wave emitted by the transmitting circuit to excite the probe to the region of interest including the vascular tissue further includes a second ultrasonic wave, and the image generating module generates the ultrasonic image according to the second echo signal obtained by the receiving circuit receiving the second ultrasonic wave.
  • the first ultrasonic wave is different from the second ultrasonic wave.
  • the processor calculates a blood vessel wall shear index at a position to be measured according to a particle flow velocity at a plurality of points near the position to be measured, including: determining a tangential direction of the blood vessel wall at the position to be measured; and extracting is located at a test a particle flow velocity at a plurality of points near the position; a velocity component along a tangential direction of the particle velocity of the plurality of points is calculated; and a blood vessel wall shear index at the position to be measured is obtained based on the plurality of calculated velocity components.
  • the determining, by the processor, the tangential direction of the blood vessel wall at the position to be tested comprises: determining, in response to the adjustment action of the blood vessel wall identification, the direction of the tangential mark used to mark the tangential direction of the blood vessel wall identifier after adjustment The tangential direction of the vessel wall.
  • the processor determines a blood vessel wall of the position of the blood vessel to be detected in response to an increase in a blood vessel wall identifier on the ultrasound image.
  • the processor determines that the brightness in the ultrasound image is higher than a preset brightness threshold, and determines that the area where the brightness is higher than the preset brightness threshold is a blood vessel wall.
  • the processor calculates blood flow energy of the position of the blood vessel to be detected, finds the edge of the blood flow energy; and determines that the brightness in the ultrasound image is higher than the preset brightness threshold and is at the edge of the blood flow energy a region, the region where the brightness is higher than the preset brightness threshold and at the edge of the blood flow energy is a blood vessel wall.
  • the processor further compares the blood flow energy with an energy threshold, and determines that the position of the blood flow energy below the energy threshold is at the edge of the blood flow energy.
  • the vessel wall shear index comprises a velocity gradient
  • the processor further derives the velocity gradient from the plurality of velocity components to the normal phase radius of the vessel wall at the current location to be measured.
  • the vessel wall shear index further comprises a wall shear stress
  • the processor further calculates the wall shear stress by integrating the blood flow viscosity coefficient with the velocity gradient.
  • the blood vessel wall shear index further comprises an oscillating shear index
  • the processor further calculates the oscillating shear index according to an integral of the wall shear stress in a cardiac cycle.
  • the processor further controls superimposing the particle flow of the plurality of points in the blood vessel on the ultrasound image after the analysis module obtains the particle point flow velocity of the plurality of points in the blood vessel according to the echo signal. Shooting speed.
  • the processor controlling the display device to display an ultrasound image and a vessel wall shear index, comprising: controlling the display The device displays the velocity gradient, wall shear stress and/or oscillating shear index of the vessel wall at at least one location to be measured, either separately or simultaneously.
  • the processor controls to display a velocity gradient value of the vessel wall at a position to be measured, a map of the wall shear stress value versus time, and/or a value and/or a map of the oscillating shear index value at different cardiac cycles;
  • the control switch displays a map of the velocity gradient value, the wall shear stress value, and/or the oscillating shear index value of the vessel wall at the plurality of locations to be measured at the current time.
  • the processor is further configured to control a position having a maximum or minimum or average velocity gradient, a wall shear stress in a vessel wall at the at least one to-beside position or within a cardiac cycle for a period of time and The position of the maximum or minimum or average oscillating shear index and the corresponding maximum or minimum or average velocity gradient, wall shear stress, and oscillating shear index for each cardiac cycle.
  • the processor further finds a vessel bifurcation position based on the ultrasound image and controls a velocity gradient, a wall shear stress, and/or an oscillating shear index that indicates the vessel bifurcation position.
  • the processor further determines a centerline of the blood vessel in the region of interest based on the ultrasound image; and determining that the position at which the plurality of centerlines intersect is the vessel bifurcation position.
  • the ultrasound image is a two-dimensional image or a three-dimensional image.
  • a method for detecting a blood vessel wall shear index by using ultrasound comprising: transmitting an ultrasonic wave to a region of interest including a blood vessel; receiving an ultrasonic wave to obtain an echo signal; and obtaining an ultrasonic image according to the echo signal; Obtaining a particle flow velocity of a plurality of points in the blood vessel according to the echo signal, the particle flow velocity including a blood flow velocity magnitude and a direction; determining a blood vessel wall in the ultrasound image; obtaining a to-be-measured position on the blood vessel wall; The blood vessel wall shear index at the position to be measured is calculated according to the particle flow velocity at a plurality of points near the position to be measured; the ultrasound image and the blood vessel wall shear index are displayed.
  • the step of "transmitting ultrasonic waves to a region of interest comprising a blood vessel” comprises: transmitting a plurality of angularly deflected first ultrasonic waves in a manner of multi-angle deflection emission to the scanning target; said step "according to said echo signal
  • the particle velocity of a plurality of points in a blood vessel includes: a first echo signal reflected from each angle of a plurality of points respectively obtains a velocity component of each point along each angle, and the obtained angle of each point is different
  • the velocity components are respectively angle-fitted, and the particle velocity of the plurality of points is synthesized.
  • the step of "transmitting ultrasonic waves to the region of interest including the blood vessel” further comprises: transmitting the second ultrasonic wave to the region of interest containing the blood vessel;
  • the step of "acquiring the ultrasound image according to the echo signal” comprises: receiving a second ultrasonic wave, obtaining a second echo signal; obtaining an ultrasonic image according to the second echo signal, the first ultrasonic wave being different from the second ultrasonic wave.
  • the step “calculating the blood vessel wall shear index at the position to be tested according to the particle flow velocity at a plurality of points near the position to be tested” includes: determining a tangential direction of the blood vessel wall at the position to be measured; and extracting is located at a test a particle flow velocity at a plurality of points near the position; a velocity component along a tangential direction of the particle velocity of the plurality of points is calculated; and a blood vessel wall shear index at the position to be measured is obtained based on the plurality of calculated velocity components.
  • step of "determining the tangential direction of the blood vessel wall” includes determining, in response to the adjustment action of the blood vessel wall identification, the direction of the tangential mark in the blood vessel wall identifier for marking the tangential direction after the adjustment The tangential direction of the vessel wall.
  • the step of "determining a blood vessel wall in an ultrasound image” comprises: determining a blood vessel wall of the blood vessel to be detected in response to an increase in a blood vessel wall identifier on the ultrasound image.
  • the step of “determining the blood vessel wall in the ultrasound image” includes: determining an area in the ultrasound image that is higher than a preset brightness threshold, and determining that the brightness is higher than the preset brightness threshold. Vascular wall.
  • the step of "determining a blood vessel wall in the ultrasound image” comprises: calculating blood flow energy of the position of the blood vessel to be detected; finding an edge of the blood flow energy; and determining that the brightness in the ultrasound image is higher than the preset A region of brightness threshold and at the edge of blood flow energy, determining that the region of brightness above the predetermined brightness threshold and at the edge of blood flow energy is a vessel wall.
  • the step of "finding the edge of the blood flow energy” comprises comparing the blood flow energy with an energy threshold, and determining that the blood flow energy is lower than the energy threshold is the edge of the blood flow energy.
  • the step of “calculating the blood vessel wall shear index at the position to be measured according to the particle flow velocity at a plurality of points near the position to be tested” includes: The velocity component is derived from the normal phase radius of the vessel wall at the current location to be measured to obtain the velocity gradient.
  • the blood vessel wall shear index further includes wall shear stress
  • the step “calculating the blood vessel wall shear index at the position to be tested according to the particle flow velocity at a plurality of points near the position to be tested” further includes: The wall shear stress is calculated by integrating the blood flow viscosity coefficient with the velocity gradient.
  • the blood vessel wall shear index further includes an oscillating shear index
  • the step of “calculating the blood vessel wall shear index at the position to be tested according to the particle flow velocity at a plurality of points near the position to be tested” further includes:
  • the oscillating shear index is calculated from the integral of the wall shear stress over a cardiac cycle.
  • the method further comprises the step of superimposing and displaying the particle points of the plurality of points in the blood vessel on the ultrasound image Flow rate.
  • the blood vessel wall shear index comprises a velocity gradient, a wall shear stress and/or an oscillating shear index
  • the step of "displaying the ultrasound image and the vessel wall shear index" comprises: displaying at least one to be performed separately or simultaneously by the map The velocity gradient, wall shear stress, and/or oscillating shear index of the vessel wall at the location.
  • the step of “displaying the velocity gradient, the wall shear stress and/or the oscillating shear index of the blood vessel wall at the at least one position to be tested separately or simultaneously by the map” includes: controlling the display of the blood vessel wall at a position to be tested a velocity gradient value, a wall shear stress value versus time curve and/or a oscillating shear index at different cardiac cycles and/or a map; or a control switch showing a velocity gradient value of the vessel wall at a plurality of locations to be measured, A map of the wall shear stress value and/or the oscillating shear index value at the current time.
  • the method further comprises the steps of: controlling the position of the vessel wall having the maximum or minimum or average velocity gradient, the wall shear stress in a period of time or a cardiac cycle in the at least one to-beside position The position of the maximum or minimum or average oscillating shear index and the corresponding maximum or minimum or average velocity gradient, wall shear stress, and oscillating shear index for each cardiac cycle.
  • the method further comprises the steps of: finding a vessel bifurcation position based on the ultrasound image; and controlling a velocity gradient, a wall shear stress, and/or an oscillatory shear index showing the vessel bifurcation position.
  • the step of "finding the blood vessel bifurcation position according to the ultrasound image” includes: determining a center line of the blood vessel in the region of interest according to the ultrasound image; and determining that the position where the plurality of center lines intersect is the blood vessel bifurcation position .
  • the ultrasound image is a two-dimensional image or a three-dimensional image.
  • a method for detecting a blood vessel wall shear index by using ultrasound comprising: transmitting an ultrasonic wave to a region of interest including a blood vessel; receiving an ultrasonic wave to obtain an echo signal; and obtaining an ultrasonic image according to the echo signal; Obtaining a particle flow velocity of a plurality of points in the blood vessel according to the echo signal, the particle flow velocity including a blood flow velocity magnitude and a direction; determining a blood vessel wall and a position to be tested in the ultrasound image; according to the blood vessel wall Calculating the velocity of the particle at a plurality of points near the position to be measured, calculating the corresponding vessel wall shear index at the position to be measured; generating an index mark, the attribute of the index mark correlating with the calculated value of the blood vessel wall shear index; An index mark corresponding to the position to be tested is marked at the position to be tested on the wall.
  • the computer readable storage medium disclosed in the embodiment of the present invention stores a plurality of program instructions, where the plurality of program instructions are used to execute the foregoing method after being invoked by the processor, and at least includes: transmitting an ultrasonic wave to a region of interest including a blood vessel; Receiving an ultrasonic wave, obtaining an echo signal; obtaining an ultra according to the echo signal Acoustic image; according to the echo signal, obtaining a particle flow velocity of a plurality of points in the blood vessel, the particle flow velocity including a blood flow velocity magnitude and direction; determining a blood vessel wall in the ultrasound image; obtaining a blood vessel wall Measuring position; calculating a blood vessel wall shear index at a position to be measured according to a particle flow velocity at a plurality of points near the position to be measured; displaying an ultrasound image and a blood vessel wall shear index.
  • the computer readable storage medium disclosed in the embodiment of the present invention stores a plurality of program instructions, where the plurality of program instructions are used to execute the foregoing method after being invoked by the processor, and further includes: transmitting an ultrasonic wave to the region of interest including the blood vessel; Receiving an ultrasonic wave, obtaining an echo signal; obtaining an ultrasonic image according to the echo signal; obtaining, according to the echo signal, a particle flow velocity of a plurality of points in the blood vessel, the particle flow velocity including a blood flow velocity magnitude and direction Determining the blood vessel wall and the position to be tested in the ultrasound image; calculating the corresponding blood vessel wall shear index at the position to be measured according to the particle flow velocity at a plurality of points near the position of the blood vessel wall; generating an index mark, an index mark The attribute corresponds to a calculated value of the blood vessel wall shear index; an index mark corresponding to the position to be measured is marked at a position to be measured on the blood vessel wall.
  • the ultrasonic imaging apparatus disclosed in the present invention can calculate the position of the sample to be measured by acquiring the velocity of the particle point of the plurality of points near the position of the blood vessel wall to be measured. Corresponding vessel wall shear index, low cost and accurate detection.
  • FIG. 1 is a block diagram showing the structure of an ultrasonic imaging apparatus according to an embodiment of the present invention.
  • FIG. 2 is a schematic diagram of angle fitting of velocity components at different angles according to an embodiment of the present invention.
  • FIG. 3 is a schematic illustration of the addition of a vessel wall marker at a vessel wall on an ultrasound image in accordance with one embodiment of the present invention.
  • FIG. 4 is a schematic illustration of a velocity gradient of a vessel wall in accordance with an embodiment of the present invention.
  • Figure 5 is a schematic diagram of velocity gradient values, wall shear stress values, and/or oscillatory shear index values in accordance with one embodiment of the present invention.
  • Fig. 6 is a schematic view showing the position of a carotid bifurcation in an embodiment of the present invention.
  • FIG. 7 is a flow chart of a method for detecting a blood vessel wall shear index using ultrasound in an embodiment of the present invention.
  • FIG. 8 is a flow chart of a method for detecting a blood vessel wall shear index using ultrasound in another embodiment of the present invention.
  • FIG. 9 is a flow chart of a method for detecting a blood vessel wall shear index using ultrasound in other embodiments of the present invention.
  • FIG. 1 is a structural block diagram of an ultrasonic imaging apparatus 100 according to an embodiment of the present invention.
  • the aforementioned ultrasonic imaging apparatus 100 includes a probe 10, a transmitting circuit 20, a receiving circuit 30, and a processor 40.
  • the aforementioned probe 10 is used to directly or indirectly contact the region of interest 200 to be detected.
  • the aforementioned region of interest 200 to be detected is a region of interest 200 comprising vascular tissue.
  • the aforementioned transmitting circuit 20 is for exciting the aforementioned probe 10 to emit ultrasonic waves to the region of interest 200 containing vascular tissue.
  • the receiving circuit 30 is configured to receive an echo signal generated after the ultrasonic wave is emitted.
  • the processor 40 is connected to the aforementioned transmitting circuit 20 and receiving circuit 30.
  • the processor 40 is configured to obtain an ultrasound image of the foregoing region of interest according to the foregoing echo signal received by the receiving circuit 30.
  • the image generation module 401 generates an ultrasound image corresponding to the region of interest according to a waveform parameter or the like of the echo signal.
  • the processor 40 is further configured to obtain a particle spot velocity of the plurality of points in the blood vessel in the region of interest 200 including the vascular tissue according to the echo signal received by the receiving circuit 30.
  • the aforementioned particle flow velocity includes the magnitude and direction of the blood flow velocity.
  • the aforementioned particle flow velocity is the actual velocity of the blood flow and is used to characterize the true direction and magnitude of blood flow in the blood vessel.
  • the aforementioned processor 40 is for determining a blood vessel wall in the ultrasound image and obtaining a position to be measured on the blood vessel wall.
  • the processor 40 is further configured to calculate a blood vessel wall shear index at a position to be measured according to a particle flow velocity at a plurality of points located near the position to be measured.
  • the processor 40 controls the display device 200 to display the aforementioned ultrasound image and the blood vessel wall shear index after calculating the blood vessel wall shear index at the position to be tested.
  • the aforementioned display device 200 is an external display device, such as a liquid crystal display or the like, in which the aforementioned ultrasonic ultrasonic imaging device 100 is connected by wire or wirelessly.
  • the aforementioned display device 200 may be a display screen integrated in the aforementioned ultrasonic imaging device 100, such as a touch display screen or the like.
  • the aforesaid transmitting circuit 20 energizing the probe 10 to transmit ultrasonic waves to the region of interest 200 comprising vascular tissue comprises: the aforementioned transmitting circuit 20 exciting the aforementioned probe 10 to be deflected at multiple angles to the region of interest 20 comprising vascular tissue.
  • the method transmits a first ultrasonic wave that is deflected at a plurality of angles.
  • the processor obtains the velocity components of each point along each angle according to the first echo signals reflected by the respective angles of the plurality of points received by the receiving circuit 30, and respectively obtains the velocity components of the different angles of each point obtained separately. Angle fitting, synthesizing the particle jet velocity of the aforementioned plurality of points.
  • the first echo signal received by the aforementioned receiving circuit 30 will The echo signal reflected by the plurality of points is included, and the echo signal reflected by each point further includes echo signals reflected from the plurality of angles.
  • the processor obtains velocity components of each point along various angles according to multiple echo signals reflected from multiple angles of each point, and combines the obtained velocity components of different angles of each point to form an angle fitting. The particle spot velocity of the corresponding point is obtained, thereby obtaining the particle spot velocity of the plurality of points.
  • the angle refers to the deflection angle between the direction of emission of the ultrasonic wave and the normal line of the end face of the ultrasonic probe.
  • the emission angle may be an ultrasonic wave in a three-dimensional space system.
  • the velocity component corresponding to each angle can be used frequently The Doppler velocity calculation method.
  • FIG. 2 Please refer to FIG. 2 together for a schematic diagram of angle fitting for velocity components at different angles.
  • Figure 2 only shows an example of angle fitting at two angles. Let the velocity component of one of the angles be V A and the velocity component of the other angle be V B . Then, after fitting by angle, the particle velocity of the above point is F. Wherein, when there are multiple echo signals transmitted from multiple angles, the corresponding velocity components reflected by the plurality of angles will be in different planes, and the velocity components are V A , V B and the particle velocity is V. Also in different planes. Therefore, FIG. 2 is a schematic diagram showing that V A and V B are fitted in a stereo space.
  • the aforesaid transmitting circuit 20 energizing the probe 10 to transmit ultrasound to the region of interest 200 comprising vascular tissue comprises: transmitting a second ultrasonic wave to a region of interest comprising the blood vessel.
  • the second ultrasonic wave is different from the first ultrasonic wave, and the second ultrasonic wave may be emitted after the first ultrasonic wave or before the first ultrasonic wave.
  • the receiving circuit 30 receives the second ultrasonic wave to obtain a second echo signal, that is, the receiving circuit 30 receives the second echo signal generated by the region of interest including the blood vessel in response to the second ultrasonic wave.
  • the processor 40 is specifically configured to obtain an ultrasound image of the foregoing region of interest according to the foregoing second echo signal received by the receiving circuit 30.
  • the aforementioned second ultrasonic wave is an ultrasonic wave for generating an ultrasonic image, which is the same as an ultrasonic wave existing for generating an ultrasonic image.
  • the first ultrasonic wave and the second ultrasonic wave may be the same type of ultrasonic wave, and simultaneously emit an echo signal, a portion of which is used to generate an ultrasound image, part or all of which is used for calculation The velocity of the particle flow at multiple points in the blood vessel.
  • the first ultrasonic wave and the second ultrasonic wave may be one or a combination of a scattered wave, a plane wave, a weakly focused wave, and the like.
  • the first ultrasonic wave and the second ultrasonic wave may belong to different ultrasonic types, and respectively generate an echo signal according to the emission timing, and an echo signal obtained corresponding to the transmitted second ultrasonic wave is used to obtain The ultrasound image, and the echo signal obtained corresponding to the transmitted first ultrasonic wave is used to obtain the particle flow velocity.
  • the first ultrasonic wave may be a combination of one or more of a scattered wave, a plane wave, a weakly focused wave, and the like.
  • the second ultrasonic wave can be a focused wave such that the quality of the ultrasound image is better.
  • the speckle tracking method when the particle velocity of the plurality of points in the blood vessel is obtained, in addition to the multi-angle velocity fitting method described above, the speckle tracking method may be employed, as shown below.
  • an intravascular number is obtained based on the ultrasonic echo signal.
  • the process of particle velocity of a dot may include the following steps.
  • At least two frames of image data may be obtained according to the ultrasonic echo signals obtained as described above, for example, at least first frame image data and second frame image data are obtained.
  • a planar ultrasonic beam can be used to acquire image data of a particle point velocity at which a target point is calculated.
  • the planar ultrasonic beam propagates substantially throughout the imaging region. Therefore, generally, the primary planar beam echo signal obtained corresponding to the planar ultrasonic beam transmitted once is processed to obtain one frame of planar beam echo image data.
  • the ultrasonic image data of the scanning target obtained by performing corresponding processing on the plane beam echo signal obtained by the plane ultrasonic beam is referred to as "planar beam echo image data".
  • a tracking area is selected in the first frame of image data, which may include a target point for which a velocity vector is desired.
  • the tracking area can select a neighborhood of the target point or a data block containing the target point.
  • an area corresponding to the tracking area is searched for in the second frame image data, for example, an area having the greatest similarity with the aforementioned tracking area is searched as the tracking result area.
  • the measure of similarity can use the metrics commonly used in the art.
  • the particle point velocity of the target point can be obtained.
  • the velocity of the particle flow velocity can be determined by the distance between the tracking region and the tracking result region (ie, the displacement of the target point within a preset time interval), divided by the first frame plane beam echo image data, and the second The time interval between the frame plane beam echo image data is obtained, and the velocity direction of the particle spot velocity may be the direction from the tracking region to the tracking result region, that is, the moving direction of the target point within the preset time interval.
  • the processor 40 calculates a blood vessel wall shear index at the position to be measured according to a particle flow velocity at a plurality of points near the position to be tested, and the processor 40 determines the blood vessel wall at the position to be tested. Tangent direction; extracting the velocity of the particle at a plurality of points near the position to be measured; calculating the velocity component of the velocity of the particle at a plurality of points along the tangential direction; obtaining the blood vessel at the position to be tested according to the plurality of calculated velocity components Wall shear index.
  • the foregoing ultrasonic imaging apparatus 100 further includes an input device 50, a user, For example, the physician can observe through the ultrasound image, confirm the position of the vessel wall in the ultrasound image, and increase the vessel wall marker in the vessel wall position in the ultrasound image by the input device 50.
  • the user can increase the blood vessel wall mark B1 at the blood vessel wall observed on the ultrasonic image M1.
  • the aforementioned blood vessel wall mark B1 has two mutually perpendicular reference lines A and reference lines B.
  • the aforementioned reference line A is a black horizontal line shown in FIG. 3
  • the aforementioned reference line B is a white vertical line shown in FIG.
  • the foregoing reference line A is used to identify the direction of the blood vessel wall
  • the processor 40 determines that the tangential direction of the blood vessel wall at the position to be tested includes: changing the direction of the reference line A in response to the adjustment operation of the reference line B by the user, confirming the adjustment After completion, the direction of the aforementioned reference line A is then determined as the tangential direction of the blood vessel wall at the position to be measured.
  • the positional relationship between the reference line A and the reference line B is relatively fixed, and the adjustment of the reference line A is caused when the reference line B is adjusted.
  • the aforementioned blood vessel wall mark B1 may have only the aforementioned reference line A for identifying the direction of the blood vessel wall, and the reference line A may be directly adjusted to change the direction of the reference line A.
  • the processor may also determine the vessel wall using an automatic identification.
  • the processor 40 determines that the blood vessel wall in the ultrasound image includes: the processor 40 determines that the brightness in the ultrasound image is higher than a predetermined brightness threshold, and determines that the brightness is higher than the preset brightness threshold.
  • Vascular wall For example, the processor 40 determines that the blood vessel wall in the ultrasound image includes: calculating blood flow energy of the position of the blood vessel to be detected; finding an edge of the blood flow energy; and determining that the brightness in the ultrasonic image is higher than the preset brightness threshold and In the region at the edge of the blood flow energy, the region where the aforementioned brightness is higher than the aforementioned predetermined brightness threshold and at the edge of the blood flow energy is the blood vessel wall.
  • the processor 40 compares the blood flow energy with an energy threshold, and determines that the position of the blood flow energy lower than the energy threshold is at the edge of the blood flow energy.
  • the aforementioned processor 40 determines that the area within the preset range of the blood vessel wall mark B1 added by the user is the position to be tested.
  • the processor 40 is configured to set a position to be tested according to the previously obtained blood vessel wall, where the position to be tested may be an area within one or more position ranges on the blood vessel wall, or a segment of the blood vessel wall. An area within the range of at least two segments.
  • the aforementioned vessel wall shear index includes a velocity gradient
  • the aforementioned processor 40 Calculating a blood vessel wall shear index at a position to be measured according to a particle flow velocity at a plurality of points near the position to be tested, comprising: the foregoing processor 40, according to the plurality of velocity components of the particle velocity of the plurality of points, respectively
  • the normal phase radius of the vessel wall at the location to be measured is derived to obtain a velocity gradient of the vessel wall.
  • the velocity gradient can be a value that varies over time, so that when the velocity gradient is displayed, the velocity gradient displayed on the interface can change over time, allowing the user to understand the change in velocity gradient over the entire observation period.
  • FIG. 4 Please refer to FIG. 4 together for a schematic diagram of the velocity gradient of the vessel wall.
  • a plurality of velocity components along the tangential direction of the blood vessel wall are included, and the velocity component of the tangential direction along the plurality of blood vessel walls is currently measured.
  • the velocity gradient of the vessel wall can be obtained by deriving the normal phase radius of the vessel wall at the location.
  • the blood vessel wall shear index further includes Wall Shear Stress (WSS), and the processor 40 further calculates a product of the blood flow viscosity coefficient and the velocity gradient obtained as described above.
  • the wall shear stress of the aforementioned vessel wall can be a time-varying value, so when the wall shear stress is displayed, the wall shear stress displayed at the interface can be changed with time, so that the user can understand the wall shear during the entire observation period. The change in shear stress.
  • the wall shear stress is calculated.
  • ⁇ represents WSS (Wall Shear Stress) and ⁇ is a liquid viscosity coefficient.
  • V T represents the tangential component of velocity and r is the normal radius.
  • the aforementioned ⁇ refers specifically to the blood viscosity of the human body, and the human blood is a non-Newtonian fluid, so theoretically the blood viscosity coefficient should be a variable (very few), which is not only related to blood.
  • the hematocrit, plasma viscosity and other parameters are related to the change in velocity gradient, but sometimes this effect is small. If only the approximate calculation is done, the WSS can also be calculated by directly using a specific constant as the blood viscosity coefficient.
  • Pa s 0.0035 Pascals
  • cP centipoise
  • this value varies from person to person. There are some fluctuations in the gender factor, even if the same person has a different blood flow rate. This value can also be measured by the falling ball method.
  • the default value given by the system may be adopted. If the default value is considered to be inaccurate, the new value is manually input, for example, the user inputs a new human blood viscosity coefficient value through the input device 50.
  • the aforementioned vascular wall shear index further includes an Oscillatory Shear Index (OSI), and the processor 40 further calculates the aforementioned oscillating shear according to the integral of the wall shear stress in a cardiac cycle T. Cut the index.
  • the oscillating shear index can measure the shear stress of a wall during a cardiac cycle. Therefore, the oscillating shear index can change with the change of the cardiac cycle.
  • the oscillating shear index displayed at the interface can be It changes as the heartbeat cycle changes, allowing the user to understand the change in the oscillatory shear index over the entire observation period.
  • the processor 40 calculates the oscillation shear index according to the integral value of the integral of the wall shear stress in one cardiac cycle T and the integral value of the absolute value of the wall shear stress in one cardiac cycle T.
  • the foregoing processor 40 is according to the formula:
  • the aforementioned oscillating shear index OSI is calculated.
  • ⁇ represents WSS (Wall Shear Stress)
  • T is a cardiac cycle, that is, the time from the start of one heartbeat to the start of the next heartbeat.
  • the processor 40 is further configured to control, after the particle velocity of the plurality of points in the blood vessel is obtained according to the echo signal, to superimpose and display the particle spot velocity of the plurality of points in the blood vessel on the ultrasonic image.
  • the aforementioned processor 405 controls the aforementioned display device 200 to display an ultrasound image and a vessel wall shear index, including : controlling the aforementioned display device 200 to display the velocity gradient, the wall shear stress and/or the oscillating shear index of the blood vessel wall at the at least one position to be measured, respectively, by the map.
  • the processor 40 controls the display of a velocity gradient value of the vessel wall at a position to be measured, a map of the wall shear stress value as a function of time, and/or a value of the oscillating shear index value at different cardiac cycles and/or a graph.
  • the processor 40 controls the switching of the velocity gradient value, the wall shear stress value, and/or the oscillating shear index value of the vessel wall at the plurality of locations to be measured at the current time.
  • a plurality of segment regions Q1 on the blood vessel represent values of different sizes. It can be the value of the velocity gradient, the value of WSS or OSI. Similarly, the lower wall of the vessel wall can also be displayed. The map on this vessel wall can be constantly updated over time. It is also possible to manually extract velocity gradients at any location on the vessel wall, curves of WSS over time, and values of OSI at different cardiac cycles.
  • the color of each region Q1 on the aforementioned blood vessel varies depending on the velocity gradient, WSS, and OSI values, and the color is not shown in the drawings due to the requirements of the drawings of the application.
  • the colors of the respective regions Q1 on the aforementioned blood vessels are the same, and the degree of color shade varies depending on the velocity gradient, the WSS, and the OSI value.
  • the processor 40 is further configured to control a position having a maximum or minimum or average velocity gradient, a wall shear stress, and a plurality of cardiac motions in a vessel wall at the at least one to-be-side position for a period of time or within a cardiac cycle.
  • the processor 40 is further configured to find a carotid bifurcation position based on the ultrasound image; the display control module 405 is further configured to control a velocity gradient, a wall shear stress, and/or an oscillating shear index that display the aforementioned carotid bifurcation position.
  • the processor 40 is specifically configured to determine a center line Z1 of a blood vessel in a region of interest according to the ultrasound image; and determine that a position at which the plurality of center lines Z1 intersect is the aforementioned carotid bifurcation position J1.
  • Embodiments of the invention are not limited to display and labeling of velocity gradients, wall shear stresses, and/or oscillating shear indices only at the carotid bifurcation locations, and may be applied simultaneously to other vessel intersection locations.
  • the processor also finds a vessel bifurcation location based on the ultrasound image and controls a velocity gradient, wall shear stress, and/or oscillatory shear index that indicates the vessel bifurcation location.
  • the processor may further determine a centerline of the blood vessel in the region of interest based on the ultrasound image; and determine a location at which the plurality of centerlines intersect as a vessel bifurcation location.
  • the aforementioned ultrasound image in the present application may be a two-dimensional image or a three-dimensional image.
  • the aforementioned processor 40 is based on a plurality of points located near the location to be tested. After the particle jet velocity is calculated, the processor 40 can automatically generate an index mark, and the mark at the position to be tested on the blood vessel wall of the ultrasonic image corresponds to the position to be measured. Index mark.
  • the attribute of the index mark is associated with the calculated value of the vascular wall shear index; the foregoing attribute may be a length, a color, or the like corresponding to the calculated value of the mark area.
  • the foregoing ultrasonic imaging apparatus 100 further includes a memory 60.
  • the foregoing memory 60 stores program instructions, and the processor 40 executes the aforementioned functions by calling a program instruction in the foregoing memory 60. step.
  • the present application also provides a computer readable medium having stored therein program instructions that are callable by the processor 40 to perform the aforementioned functions.
  • the aforementioned computer readable storage medium is the aforementioned memory 60.
  • the aforementioned memory 60 may be a storage device such as a memory card, a solid state memory, a hard disk, a compact disk, or the like.
  • the processor 40 may be a central processing unit, a microprocessor, a single chip microcomputer, a digital signal processor, or the like.
  • the aforementioned input device 50 can be a mouse, a touchpad, or the like.
  • the aforementioned input device 50 may also be integrated with the aforementioned display device 200 into a touch display screen.
  • FIG. 7 is a flow chart of a method for detecting a blood vessel wall shear index by using ultrasound according to an embodiment of the invention.
  • the steps in the foregoing methods are not limited to the order in the figures, and those skilled in the art can perform the transformation as needed.
  • the foregoing method is applied to the aforementioned ultrasonic imaging apparatus 100.
  • the foregoing method includes the following steps:
  • Ultrasound is emitted to the region of interest containing the blood vessel (S701).
  • the foregoing step S701 includes transmitting a plurality of angularly deflected first ultrasonic waves in a manner of multi-angle deflection transmission of the scanning target. In some embodiments, the foregoing step S701 further comprises: transmitting a second ultrasonic wave to the region of interest comprising the blood vessel. The first ultrasonic wave may be emitted before the second ultrasonic wave or after the second ultrasonic wave.
  • the ultrasonic wave is received, and an echo signal is obtained (S702).
  • An ultrasound image is obtained based on the aforementioned echo signal (S703).
  • the foregoing step S703 includes: obtaining the aforementioned ultrasonic image according to the second echo signal reflected back in response to the second ultrasonic wave, the first ultrasonic wave being different from the second ultrasonic wave.
  • the particle velocity of the particle flow The degree includes the blood flow velocity magnitude and direction (S704).
  • the foregoing step S704 includes: obtaining a velocity component of each point along each angle according to the first echo signals reflected by the first ultrasonic wave according to respective angles of the plurality of points, and different points of each point obtained.
  • the velocity components of the angle are respectively angle-fitted, and the particle velocity of the plurality of points is synthesized.
  • the blood vessel wall in the ultrasound image is determined (S705).
  • the aforementioned step S705 includes determining the blood vessel wall of the aforementioned blood vessel position to be detected in response to the blood vessel wall identification added on the aforementioned ultrasound image.
  • the foregoing step S705 includes: determining an area in the ultrasound image that is higher than a preset brightness threshold, and determining that the area in which the brightness is higher than the preset brightness threshold is a blood vessel wall.
  • the foregoing step S705 includes: calculating blood flow energy of the position of the blood vessel to be detected; finding an edge of the blood flow energy; and determining that the brightness in the ultrasonic image is higher than the preset brightness threshold and is in blood flow energy In the region at the edge, the region where the aforementioned brightness is higher than the aforementioned predetermined brightness threshold and at the edge of the blood flow energy is the blood vessel wall.
  • the “finding the edge of the blood flow energy” includes: comparing the blood flow energy with an energy threshold, and determining that the blood flow energy is lower than the energy threshold is at the edge of the blood flow energy.
  • the position to be tested on the blood vessel wall is obtained (S706).
  • the foregoing position to be tested may be determined according to an increased blood vessel wall identifier on the aforementioned ultrasound image, for example, determining a region including at least the aforementioned blood vessel wall identifier as a position to be tested.
  • the blood vessel wall shear index at the position to be measured is calculated based on the particle flow velocity at a plurality of points near the position to be measured (S707).
  • the foregoing step S707 includes: determining a tangential direction of the blood vessel wall at the position to be measured; extracting a particle flow velocity at a plurality of points near the position to be measured; and calculating a particle flow velocity of the plurality of points along the tangential direction Velocity component; obtaining a blood vessel wall shear index at the position to be tested according to the plurality of velocity components calculated as described above.
  • the foregoing “determining the tangential direction of the blood vessel wall at the position to be tested” includes determining, in response to the adjustment action on the aforementioned blood vessel wall identification, the direction of the tangential mark in the aforementioned blood vessel wall identifier for marking the tangential direction after the adjustment is The tangential direction of the aforementioned vessel wall.
  • the aforementioned vessel wall shear index includes a velocity gradient, as described above.
  • the calculated plurality of velocity components obtain the vessel wall shear index at the position to be measured includes: deriving the aforementioned plurality of velocity components to the normal phase radius of the vessel wall at the current position to be measured to obtain the aforementioned velocity gradient.
  • V T represents the velocity component, that is, the tangential component of the velocity along the vessel wall
  • the aforementioned blood vessel wall shear index further includes a wall shear stress
  • the foregoing “determining the blood vessel wall shear index at the position to be tested according to the plurality of calculated velocity components” further includes: the aforementioned blood flow The viscous coefficient is integrated with the aforementioned velocity gradient to calculate the aforementioned wall shear stress.
  • the wall shear stress in the vessel wall shear index was calculated.
  • ⁇ represents WSS (Wall Shear Stress) and ⁇ is a liquid viscosity coefficient.
  • v T represents the tangential component of velocity and r is the normal radius.
  • the aforementioned blood vessel wall shear index further includes an OSI-Oscillatory Shear Index
  • the foregoing step "obtains a blood vessel wall shear index at a position to be tested according to the plurality of calculated velocity components"
  • the method further comprises: calculating the aforementioned oscillating shear index according to the integral of the wall shear stress in a cardiac cycle T.
  • the "calculating the aforementioned oscillating shear index according to the integral of the wall shear stress in a cardiac cycle T" further comprises: the absolute value of the integral according to the wall shear stress in a cardiac cycle T and the aforementioned wall shear The integral of the shear stress is calculated over the integral of a cardiac cycle T to obtain the aforementioned oscillating shear index. Specifically, according to the formula: Calculate the aforementioned oscillating shear index. Where ⁇ represents WSS (Wall Shear Stress).
  • the ultrasound image and the vessel wall shear index are displayed (S508).
  • the aforementioned vessel wall shear index includes a velocity gradient, a wall shear stress, and/or an oscillating shear index
  • the foregoing step S508 includes: displaying the velocity of the vessel wall at the at least one location to be measured separately or simultaneously by the map. Gradient, wall Shear stress and/or oscillating shear index.
  • the foregoing “displaying, by the map, the velocity gradient, the wall shear stress and/or the oscillating shear index of the blood vessel wall at the at least one position to be tested” further includes: controlling the display of the blood vessel wall at a position to be tested a map of velocity gradient values, wall shear stress values, and/or oscillating shear index values over time; or control switching to display velocity gradient values, wall shear stress values, and/or oscillations of vessel walls at multiple locations to be measured Cut the map of the index value at the current time.
  • the foregoing “displaying, by the map, the velocity gradient, the wall shear stress and/or the oscillating shear index of the vessel wall at the at least one position to be tested, respectively” further comprises: controlling to display the at least one to-be-side The position of the vessel wall at the location with maximum or minimum velocity gradient, wall shear stress and oscillatory shear index and corresponding maximum or minimum velocity gradient, wall shear stress and oscillatory shear index.
  • the foregoing method for detecting a blood vessel wall shear index by using ultrasound after the foregoing step S704, further comprising the step of superimposing a particle point flow velocity of the plurality of points in the blood vessel superimposed on the ultrasound image.
  • a plurality of arrow marks are superimposed on the ultrasound image, the length of the arrow indicating the magnitude of the velocity, and the pointing of the arrow indicating the direction of the velocity.
  • particle points the size of the particle point indicates the speed, the direction of the particle flow indicates the speed direction
  • triangle rendering frame The area of the triangle frame indicates the speed, the apex of the triangle indicates the direction of the speed
  • the foregoing method for detecting a blood vessel wall shear index by ultrasound further comprises the steps of: finding a carotid bifurcation position according to the ultrasound image; and controlling a velocity gradient and a wall shear stress indicating the position of the carotid bifurcation And / or shock shear index.
  • the foregoing step "finding the carotid bifurcation position according to the ultrasound image” includes: determining a center line of the blood vessel in the region of interest according to the ultrasound image; and determining that the position where the plurality of center lines intersect is the aforementioned carotid bifurcation position.
  • FIG. 8 is a flow chart of a method for detecting a blood vessel wall shear index by using ultrasound according to another embodiment of the present invention.
  • the aforementioned method includes the steps of:
  • the plurality of angularly deflected first ultrasonic waves are emitted to the region of interest including the blood vessel in a multi-angle deflected emission (S801).
  • a second ultrasonic wave is emitted to the region of interest including the blood vessel (S802). Wherein the aforementioned first ultrasound The wave is different from the second ultrasonic wave.
  • Receiving the first ultrasonic wave obtains the first echo signal, and receiving the second ultrasonic wave to obtain the second echo signal (S803).
  • An ultrasound image is obtained based on the aforementioned second echo signal (S804).
  • a particle flow velocity of a plurality of points in the blood vessel is obtained, and the particle velocity of the particle includes a magnitude and a direction of the blood flow velocity (S805).
  • the blood vessel wall in the ultrasound image is determined (S806).
  • the position to be tested on the blood vessel wall is obtained (S807).
  • the blood vessel wall shear index at the position to be measured is calculated based on the particle flow velocity at a plurality of points near the position to be measured (S808).
  • the ultrasound image and the vessel wall shear index are displayed (S809).
  • steps S804-S809 respectively correspond to steps S703-S708 in FIG. 7 one by one, and the detailed steps specifically included in the steps S804-S809 are referred to the description in the steps S703-S708 in FIG. 7, and will not be further described herein.
  • FIG. 9 is a flow chart of a method for detecting a blood vessel wall shear index by using ultrasound in other embodiments of the present invention.
  • the foregoing method includes the steps of:
  • Ultrasound is emitted to the region of interest containing the blood vessel (S901).
  • the ultrasonic wave is received, and an echo signal is obtained (S902).
  • An ultrasound image is obtained based on the aforementioned echo signal (S903).
  • a particle flow velocity of a plurality of points in the blood vessel is obtained, and the particle velocity of the particle includes a magnitude and a direction of the blood flow velocity (S904).
  • the blood vessel wall and the position to be tested in the ultrasound image are determined (S905).
  • the corresponding blood vessel wall shear index at the position to be measured is calculated according to the particle flow velocity at a plurality of points located near the position of the blood vessel wall (S906).
  • index mark is generated, and the attribute of the index mark is associated with the calculated value of the aforementioned blood vessel wall shear index (S907).
  • the attributes of the foregoing index mark include, but are not limited to, a length, a color, and the like, and an index mark having an attribute of a corresponding length, color, or the like may be generated according to the aforementioned blood vessel wall shear index.
  • An index mark corresponding to the aforementioned position to be measured is marked at the position to be measured on the blood vessel wall (S908).
  • Steps S901-S904 in this embodiment are in one-to-one correspondence with steps S701-S704 in FIG. 7, step S905 corresponds to steps S705-S706 in FIG. 7, and step S906 corresponds to step S707 in FIG.
  • steps S901-S904 in this embodiment are in one-to-one correspondence with steps S701-S704 in FIG. 7
  • step S905 corresponds to steps S705-S706 in FIG. 7
  • step S906 corresponds to step S707 in FIG.
  • the present application can accurately detect the vessel wall shear index including the velocity gradient, the wall shear stress, and the oscillating shear index at the vessel wall position at a lower cost.

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Abstract

一种超声波成像设备、利用超声检测血管壁剪切指数的方法及计算机可读存储介质，方法包括：向包含血管的感兴趣区域发射超声波（S701，S801-S802，S901）；接收超声波，获得回波信号（S702，S803，S902）；根据回波信号获得超声图像（S703，S804，S903）；根据回波信号，获得血管内多个点的质点流射速度，质点流射速度包括血流速度大小和方向（S704，S805，S904）；确定超声图像中的血管壁（S705，S806，S905）；获得血管壁上的待测位置（S706，S807，S905）；根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数（S707，S808，S906）；显示超声图像和血管壁剪切指数（S708，S809）。超声成像设备及方法，能够以较低的成本检测血管壁剪切指数。

Description

超声成像设备及利用超声检测血管壁剪切指数的方法 技术领域
本发明涉及一种成像方法，尤其涉及一种超声成像设备及应用于所述超声成像设备中的利用超声检测血管壁剪切指数的方法。
背景技术
血管壁面剪切指数，例如WSS(Wall Shear Stress，血管壁面剪切应力)是医学界公认的和动脉硬化相关的参数。血管壁面剪切指数通常与血管壁附近沿血管壁切线方向的血流速度分量的梯度有关。因此计算或检测WSS这个值时需要先知道血管中血流速度的大小和方向，这样才能得到其沿血管壁切向的分量值。传统的一种检测方法是通过采用多普勒原理的彩超进行检测，得到是血流沿超声传播方向的分量值，难以得到血流沿血管壁切向方向的分量，因此不能准确的测量出WSS，使得基于传统彩超的计算方法只能对WSS做定性的分析。另一个传统的检测方法是通过相位对比磁共振血管造影(PC-MRA，phase-contrast magnetic resonance angiography)得到血流速度的大小和方向，然后再计算WSS。然而，基于相位对比磁共振血管造影的检测方法的检查时间较长，仪器设备昂贵，检查时也会给患者和医生带来诸多不便，例如会导致检查舒适度不佳，需要ECG(Electrocardiograph，心电图)校准，信号可能受干扰等等问题。
发明内容
有鉴于此，本发明提供一种超声成像设备及利用超声检测血管壁剪切指数的方法，能以较低的成本准确地检测血管壁剪切指数。
本发明实施例公开的超声成像设备，包括探头、发射电路、接收电路及处理器。所述发射电路用于激励所述探头向包含血管组织的感兴趣区域发射超声波。所述接收电路用于接收所述超声波发射后所产生的回波信号。所述处理器用于执行以下步骤：根据所述回波信号获得所述感兴趣区域的超声图像；根据所述回波信号获得血管内多个点的质点流射速度，所述质点流射速度包括血流 速度大小和方向；确定超声图像中的血管壁，以及获得血管壁上的待测位置；根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数；以及控制一显示装置显示超声图像和血管壁剪切指数。
其中，所述发射电路激励所述探头向包含血管组织的感兴趣区域发射的超声波包括以多角度偏转发射的方式发射多个角度偏转的第一超声波，所述处理器根据接收电路接收的多个点的各个角度反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，并将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到所述多个点的质点流射速度。
其中，所述发射电路激励所述探头向包含血管组织的感兴趣区域发射的超声波还包括第二超声波，所述图像生成模块根据接收电路接接收第二超声波获得的第二回波信号生成超声图像，其中，所述第一超声波不同于第二超声波。
其中，所述处理器根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数，包括：确定待测位置处血管壁的切线方向；提取位于待测位置附近多个点的质点流射速度；计算多个点的质点流射速度沿切线方向的速度分量；根据所述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
其中，所述处理器确定待测位置处血管壁的切线方向包括：响应对所述血管壁标识的调节动作，确定调节后所述血管壁标识中用于标记切线方向的切线标记的方向为所述血管壁的切线方向。
其中，所述处理器响应在所述超声图像上增加的血管壁标识的确定所述待检测血管位置的血管壁。
其中，所述处理器判断出所述超声图像中的亮度高于一预设亮度阈值的区域，确定所述亮度高于所述预设亮度阈值的区域为血管壁。
其中，所述处理器计算待检测血管位置的血流能量，寻找血流能量的边缘处；以及判断所述超声图像中的亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域，确定所述亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
其中，所述处理器还将血流能量与一能量阈值进行比较，确定血流能量低于所述能量阈值的位置为所述血流能量的边缘处。
其中，所述血管壁剪切指数包括速度梯度，所述处理器还将所述多个速度分量对当前待测位置处的血管壁的法相半径求导得到所述速度梯度。
其中，所述血管壁剪切指数还包括壁面剪切应力，所述处理器还对所述血流粘滞系数与所述速度梯度求积计算得出所述壁面剪切应力。
其中，所述血管壁剪切指数还包括震荡剪切指数，所述处理器还根据壁面剪切应力在一个心动周期内的积分计算得出所述震荡剪切指数。
其中，所述处理器还在所述分析模块根据所述回波信号获得血管内多个点的质点流射速度之后，控制在所述超声图像上叠加显示所述血管内多个点的质点流射速度。
其中，所述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数，所述处理器控制所述显示装置显示超声图像和血管壁剪切指数，包括：控制所述显示装置通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数。
其中，所述处理器控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值随时间变化的图谱和/或震荡剪切指数值在不同心动周期的值和/或图谱；或者控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
其中，所述处理器还用于控制显示所述至少一个待侧位置处的血管壁中在一段时间内或一个心动周期内的具有最大或最小或平均速度梯度、壁面剪切应力的位置和多个心动周期内具有最大或最小或平均震荡剪切指数的位置及对应的最大或最小或平均速度梯度、壁面剪切应力和震荡剪切指数的数值。
其中，所述处理器还根据超声图像找到血管分叉位置，并控制显示所述血管分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
其中，所述处理器还根据超声图像确定感兴趣区域中的血管的中心线；以及确定有多条中心线相交叉的位置为所述血管分叉位置。
其中，所述超声图像为二维图像或三维图像。
本发明实施例公开的利用超声检测血管壁剪切指数的方法，所述方法包括：向包含血管的感兴趣区域发射超声波；接收超声波，获得回波信号；根据所述回波信号获得超声图像；根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；确定超声图像中的血管壁；获得血管壁上的待测位置；根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数；显示超声图像和血管壁剪切指数。
其中，所述步骤“向包含血管的感兴趣区域发射超声波”包括：对扫描目标以多角度偏转发射的方式发射多个角度偏转的第一超声波；所述步骤“根据所述回波信号，获得血管内多个点的质点流射速度”包括：根据多个点的各个角度反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到所述多个点的质点流射速度。
其中，所述步骤“向包含血管的感兴趣区域发射超声波”还包括：所述向包含血管的感兴趣区域发射第二超声波；所述步骤“根据所述回波信号获得超声图像”包括：接收第二超声波，获得第二回波信号；根据所述第二回波信号获得超声图像，所述第一超声波不同于第二超声波。
其中，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”包括：确定待测位置处血管壁的切线方向；提取位于待测位置附近多个点的质点流射速度；计算多个点的质点流射速度沿切线方向的速度分量；根据所述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
其中，所述步骤“确定所述血管壁的切线方向”包括：响应对所述血管壁标识的调节动作，确定调节后所述血管壁标识中用于标记切线方向的切线标记的方向为所述血管壁的切线方向。
其中，所述步骤“确定超声图像中的血管壁”包括：响应在所述超声图像上增加的血管壁标识的确定所述待检测血管位置的血管壁。
其中，所述步骤“确定超声图像中的血管壁”包括：判断出所述超声图像中的亮度高于一预设亮度阈值的区域，确定所述亮度高于所述预设亮度阈值的区域为血管壁。
其中，所述步骤“确定超声图像中的血管壁”包括：计算待检测血管位置的血流能量；寻找血流能量的边缘处；以及在判断所述超声图像中的亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域，确定所述亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
其中，所述步骤“寻找血流能量的边缘处”包括：将血流能量与一能量阈值进行比较，确定血流能量低于所述能量阈值的位置为所述血流能量的边缘处。
其中，所述血管壁剪切指数包括速度梯度，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”包括：将所述多个速度分量对当前待测位置处的血管壁的法相半径求导得到所述速度梯度。
其中，所述血管壁剪切指数还包括壁面剪切应力，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”还包括：对所述血流粘滞系数与所述速度梯度求积计算得出所述壁面剪切应力。
其中，所述血管壁剪切指数还包括震荡剪切指数，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”还包括：根据壁面剪切应力在一个心动周期内的积分计算得出所述震荡剪切指数。
其中，在所述步骤“根据所述回波信号，获得血管内多个点的质点流射速度”之后，所述方法还包括步骤：在超声图像上叠加显示所述血管内多个点的质点流射速度。
其中，所述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数，所述步骤“显示超声图像和血管壁剪切指数”包括：通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数。
其中，所述步骤“通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数”包括：控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值随时间变化的曲线和/或震荡剪切指数在不同心动周期的值和/或图谱；或者控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
其中，所述方法还包括步骤：控制显示所述至少一个待侧位置处的血管壁中在一段时间内或一个心动周期内的具有最大或最小或平均速度梯度、壁面剪切应力的位置和多个心动周期内具有最大或最小或平均震荡剪切指数的位置及对应的最大或最小或平均速度梯度、壁面剪切应力和震荡剪切指数的数值。
其中，所述方法还包括步骤：根据超声图像找到血管分叉位置；以及控制显示所述血管分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
其中，，所述步骤“根据超声图像找到血管分叉位置”包括：根据超声图像确定感兴趣区域中的血管的中心线；以及确定有多条中心线相交叉的位置为所述血管分叉位置。
其中，所述超声图像为二维图像或三维图。
本发明实施例公开的利用超声检测血管壁剪切指数的方法，所述方法包括：向包含血管的感兴趣区域发射超声波；接收超声波，获得回波信号；根据所述回波信号获得超声图像；根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；确定超声图像中的血管壁及待测位置；根据位于血管壁的待测位置附近多个点的质点流射速度，计算待测位置处对应的血管壁剪切指数；生成指数标记，指数标记的属性与所述血管壁剪切指数的计算值关联对应；在血管壁上的待测位置处标记与所述待测位置关联对应的指数标记。
本发明实施例公开的计算机可读存储介质，存储有多条程序指令，所述多条程序指令用于被处理器调用后执行前述的方法，至少包括：向包含血管的感兴趣区域发射超声波；接收超声波，获得回波信号；根据所述回波信号获得超 声图像；根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；确定超声图像中的血管壁；获得血管壁上的待测位置；根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数；显示超声图像和血管壁剪切指数。
本发明实施例公开的计算机可读存储介质，存储有多条程序指令，所述多条程序指令用于被处理器调用后执行前述的方法，还包括：向包含血管的感兴趣区域发射超声波；接收超声波，获得回波信号；根据所述回波信号获得超声图像；根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；确定超声图像中的血管壁及待测位置；根据位于血管壁的待测位置附近多个点的质点流射速度，计算待测位置处对应的血管壁剪切指数；生成指数标记，指数标记的属性与所述血管壁剪切指数的计算值关联对应；在血管壁上的待测位置处标记与所述待测位置关联对应的指数标记。
本发明公开的超声成像设备、利用超声检测血管壁剪切指数的方法及计算机可读存储介质，通过获取血管壁的待测位置附近多个点的质点流射速度，即可计算待测位置处对应的血管壁剪切指数，成本低且检测准确。
附图说明
为了更清楚地说明本发明实施例中的技术方案，下面将对实施例中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本发明的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。
图1为本发明一实施例中的超声成像设备的结构框图。
图2为本发明一实施例中的不同角度的速度分量进行角度拟合的示意图。
图3为本发明一实施例中的在超声图像上的血管壁处增加血管壁标识的示意图。
图4为本发明一实施例中的血管壁的速度梯度的示意图。
图5为本发明一实施例中的速度梯度值、壁面剪切应力值和/或震荡剪切指数值的图谱示意图。
图6为本发明一实施例中的颈动脉分叉位置的示意图。
图7为本发明一实施例中的利用超声检测血管壁剪切指数的方法的流程图。
图8为本发明另一实施例中的利用超声检测血管壁剪切指数的方法的流程图。
图9为本发明其他实施例中的利用超声检测血管壁剪切指数的方法的流程图。
具体实施方式
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有做出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。
请参阅图1，为本发明一实施例中的超声成像设备100的结构框图。前述超声成像设备100包括探头10、发射电路20、接收电路30以及处理器40。前述探头10用于与待检测的感兴趣区域200直接或间接接触。在一些实施例中，前述待检测的感兴趣区域200为包含血管组织的感兴趣区域200。前述发射电路20用于激励前述探头10向包含血管组织的感兴趣区域200发射超声波。前述接收电路30用于接收前述超声波发射后所产生的回波信号。
前述处理器40与前述发射电路20、接收电路30连接。
前述处理器40用于根据前述接收电路30接收的前述回波信号获得前述感兴趣区域的超声图像。其中，前述图像生成模块401根据回波信号的波形参数等生成前述感兴趣区域对应的超声图像。
前述处理器40还用于根据前述接收电路30接收的前述回波信号获得前述包含血管组织的感兴趣区域200中的血管内多个点的质点流射速度。其中，前述质点流射速度包括血流速度大小和方向。前述质点流射速度为血流实际速度，用于表征血流在血管中流动的真实方向和大小。
前述处理器40用于确定超声图像中的血管壁，以及获得血管壁上的待测位置。
前述处理器40并用于根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数。
前述处理器40并在计算出待测位置处的血管壁剪切指数后，控制一显示装置200显示前述超声图像和血管壁剪切指数。在一些实施例中，前述显示装置200为前述超声超声成像设备100通过有线或无线方式连接的外部显示设备，例如液晶显示器等。在另一些实施例中，前述显示装置200可为集成在前述超声成像设备100中的显示屏，例如触摸显示屏等。
在一些实施例中，前述发射电路20激励前述探头10向包含血管组织的感兴趣区域200发射超声波包括：前述发射电路20激励前述探头10向包含血管组织的感兴趣区域20以多角度偏转发射的方式发射多个角度偏转的第一超声波。前述处理器根据接收电路30接收的多个点的各个角度反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，并将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到前述多个点的质点流射速度。
即，当前述发射电路20激励前述探头10向包含血管组织的感兴趣区域20以多角度偏转发射的方式发射多个角度偏转的第一超声波时，前述接收电路30接收的第一回波信号将包括多个点反射回来的回波信号，且每个点反射回来的回波信号还包括多个角度反射回来的回波信号。前述处理器根据每个点的多个角度反射回来的多个回波信号得到每个点沿各个角度的速度分量，并将得到的每个点的不同角度的速度分量分别做角度拟合而合成得到对应点的质点流射速度，从而得到前述多个点的质点流射速度。本文中发射多个角度偏转的第一超声波中，角度是指超声波的发射方向和超声探头端面法线之间的偏转角，例如针对面阵探头，发射角度可以是在三维空间系上的超声波的发射方向和超声探头端面法线之间的偏转角。针对每个角度对应的速度分量可以采用常 规的多普勒速度计算方式。
请一并参阅图2，为不同角度的速度分量进行角度拟合的示意图。图2仅示意出了两个角度进行角度拟合的例子。设某一点的其中一个角度的速度分量为VA，另一个角度的速度分量为VB，则通过角度拟合后，拟合得到前述点的质点流射速度为V。其中，由于有多个角度发射回来的第一回波信号时，前述多个角度反射回来的对应的速度分量将在不同的平面，前述速度分量为VA、VB及质点流射速度为V也在不同的平面中。因此，图2所示的为V A及VB为立体空间上进行拟合的示意图。
在另一些实施例中，前述发射电路20激励前述探头10向包含血管组织的感兴趣区域200发射超声波包括：向包含血管的感兴趣区域发射第二超声波。其中，前述第二超声波不同于第一超声波，且前述第二超声波可后于前述第一超声波发射或先于前述第一超声波发射。
前述接收电路30接收第二超声波，获得第二回波信号，即前述接收电路30接收包含血管的感兴趣区域响应第二超声波产生的第二回波信号。
前述处理器40具体为用于根据前述接收电路30接收的前述第二回波信号获得前述感兴趣区域的超声图像。其中，前述第二超声波为用于产生超声图像的超声波，与现有用于产生超声图像的超声波相同。
在一些实施例中第一超声波和第二超声波可以是相同类型的超声波，并同时发射获得回波信号，该回波信号的一部分用于产生超声图像，该回波信号的部分或全部用于计算血管内多个点的质点流射速度。例如，第一超声波和第二超声波可以为散射波、平面波、弱聚焦波等等中之一或几种的组合。当然，在另一些实施例中，第一超声波和第二超声波可以分属不同的超声波类型，并按照发射时序分别发射获得回波信号，对应于发射的第二超声波获得的回波信号用于获得超声图像，而对应于发射的第一超声波获得的回波信号用于获得质点流射速度。例如，第一超声波可以为散射波、平面波、弱聚焦波等等中之一或几种的组合。第二超声波可以为聚焦波，这样超声图像的质量更好。
此外，根据超声回波信号，获得血管内多个点的质点流射速度时除了采用前述的多角度速度拟合方式，还可以采用斑点跟踪方式，具体如下所示。
例如，在本发明的其中一个实施例中，根据超声回波信号、获得血管内多 个点的质点流射速度的过程可以包括下列步骤。
首先，可以根据前述获得的超声回波信号获得至少两帧图像数据，例如获得至少第一帧图像数据和第二帧图像数据。如前文所述，本实施例中可以采用平面超声波束来获取计算目标点的质点流射速度的图像数据。平面超声波束大体上在整个成像区域中传播，因此，通常，一次发射的平面超声波束所对应获得的一次平面波束回波信号通过处理即可获得一帧平面波束回波图像数据。本文中，将对平面超声波束对应获得的平面波束回波信号进行相应的处理而获得的扫描目标的超声图像数据称之为“平面波束回波图像数据”。
然后，在第一帧图像数据中选择跟踪区域，该跟踪区域可以包含希望获得其速度矢量的目标点。例如，跟踪区域可以选择目标点的某个邻域或者包含目标点的某个数据块。
其次，在第二帧图像数据中搜索与该跟踪区域对应的区域，例如，搜索与前述的跟踪区域具有最大相似性的区域作为跟踪结果区域。这里，相似性的度量可以使用本领域内通常使用的度量方法。
最后，根据前述的跟踪区域和前述的跟踪结果区域的位置以及第一帧图像数据与第二帧图像数据之间的时间间隔，即可获得目标点的质点流射速度。例如，质点流射速度的速度大小可以通过跟踪区域和跟踪结果区域之间的距离(即目标点在预设时间间隔内的移动位移)、除以第一帧平面波束回波图像数据与第二帧平面波束回波图像数据之间的时间间隔获得，而质点流射速度的速度方向可以为从跟踪区域到跟踪结果区域的连线的方向，即目标点在预设时间间隔内的移动方向。
在一些实施例中，前述处理器40根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数包括：前述处理器40确定待测位置处血管壁的切线方向；提取位于待测位置附近多个点的质点流射速度；计算多个点的质点流射速度沿切线方向的速度分量；根据前述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
在一些实施例中，前述处理器40确定超声图像中的血管壁包括：前述处理器40响应在前述超声图像上增加的血管壁标识，确定前述待检测血管位置的血管壁。
其中，如图1所示，前述超声成像设备100还包括输入装置50，用户， 例如医生可通过超声图像进行观察，确认超声图像中的血管壁的位置，并通过输入装置50在超声图像中的血管壁位置上增加血管壁标识。
请一并参阅图3，如图3所示，用户可在超声图像M1上观察到的血管壁处增加血管壁标识B1。如图3所示，前述血管壁标识B1上还有两条相互垂直的基准线A和基准线B。前述基准线A为图3中所示的黑色的横线，前述基准线B为图3中所示的白色的竖线。
其中，前述基准线A用于标识血管壁的方向，前述处理器40确定待测位置处血管壁的切线方向包括：响应用户对基准线B的调节操作而改变基准线A的方向，在确认调节完毕后，然后将前述基准线A的方向确定为待测位置处血管壁的切线方向。其中，前述基准线A和基准线B的位置关系是相对固定的，在调节基准线B的时候引起基准线A的调节。显然，在一些实施例中，前述血管壁标识B1上可仅有前述用于标识血管壁方向的基准线A，可直接对前述基准线A进行调节而改变基准线A的方向。
在另一些实施例中，处理器还可以采用自动识别的方式来确定血管壁。例如，前述处理器40确定超声图像中的血管壁包括：前述处理器40判断出前述超声图像中的亮度高于一预设亮度阈值的区域，确定前述亮度高于前述预设亮度阈值的区域为血管壁。还例如，前述处理器40确定超声图像中的血管壁包括：计算待检测血管位置的血流能量；寻找血流能量的边缘处；以及判断前述超声图像中的亮度高于前述预设亮度阈值且处于血流能量的边缘处的区域，确定前述亮度高于前述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
前述处理器40将血流能量与一能量阈值进行比较，确定血流能量低于前述能量阈值的位置为前述血流能量的边缘处。
由于不是所有的超声扫描都会有血管出现在扫描区域，因此这种单一的判断可能出现错误，通过进一步根据血管能量判断，能显著提高判断的准确度。
在一些实施例中，前述处理器40确定用户添加的血管壁标识B1的预设范围内的区域为待测位置。或者，前述处理器40根据前述获得的血管壁来自定义设置待测位置，此处的待测位置可以是血管壁上一个或多个位置范围内的区域，或者是血管壁上分截段设置的至少两个节段位置范围内的区域。
在一些实施例中，前述血管壁剪切指数包括速度梯度，前述处理器40根 据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数，包括：前述处理器40根据多个点的质点流射速度的前述多个速度分量对当前待测位置处的血管壁的法相半径求导得到血管壁的速度梯度。速度梯度可以是随时间变化的值，因此在显示速度梯度时，在界面上显示的速度梯度可以随时间的变化而变化，从而使用户了解在整个观测时间段内速度梯度的变化。
在一些实施例中，为根据公式
Figure PCTCN2017082480-appb-000001
计算血管壁的速度梯度。其中前述公式中VT表示速度分量，即速度沿血管壁切向的分量，前述速度梯度为速度分量在血管壁的半径r＝R这一法相半径处求导得到的。
请一并参阅图4，为血管壁的速度梯度的示意图。如图4所示，在该血管壁当前待测位置处包括多个沿前述血管壁的切向方向的速度分量，通过对前述多个沿前述血管壁的切向方向的速度分量对当前待测位置处的血管壁的法相半径求导即可得到血管壁的速度梯度。
在一些实施例中，前述血管壁剪切指数还包括壁面剪切应力(Wall Shear Stress，WSS)，前述处理器40还对前述血流粘滞系数与前述求出的速度梯度求积计算得出前述血管壁的壁面剪切应力。壁面剪切应力可以是随时间变化的值，因此在显示壁面剪切应力时，在界面上显示的壁面剪切应力可以随时间的变化而变化，从而使用户了解在整个观测时间段内壁面剪切应力的变化。
具体的，为根据公式：
Figure PCTCN2017082480-appb-000002
计算得出壁面剪切应力。其中，τ表示WSS(Wall Shear Stress，血管壁面剪切应力)，μ是液体粘滞系数。VT表示速度的切向分量，r是法向半径。
在本申请中，前述μ特别指的是人体血液粘滞系数(blood viscosity)，人体血液为非牛顿流体，因此理论上这个血液粘质系数应该是一个变量(非常数)，这个值不仅与血液的红细胞比容、血浆粘度等参数相关，还会随速度梯度的变化而改变，但是有时这种影响很小。如果只做近似计算，也可以直接采用一个特定常数作为血液粘质系数，进行WSS的计算。例如在计算颈动脉 WSS时，可采用一个平均的血液粘质系数值，例如0.0035帕秒(Pa s)，或者用单位厘泊(cP)表示，0.0035Pa s＝3.5cP，当然这个值因人而异会随年龄性别的因素有一些浮动，即使同一个人在血流速度不同时这个值也会有浮动。这个值还可以通过落球法进行测量。在实际应用中可以采用系统给予的默认值，如果认为默认值不准确则通过手动输入新的值进行调整，例如用户通过输入装置50输入新的人体血液粘滞系数值。
在一些实施例中，前述血管壁剪切指数还包括震荡剪切指数(Oscillatory Shear Index,OSI)，前述处理器40还根据壁面剪切应力在一个心动周期T内的积分计算得出前述震荡剪切指数。震荡剪切指数可以衡量一个心动周期内壁面剪切应力的情况，因此，震荡剪切指数可以随心动周期的变化而变化，在显示震荡剪切指数时，在界面上显示的震荡剪切指数可以随心动周期的变化而变化，从而使用户了解在整个观测时间段内震荡剪切指数的变化。进一步的，前述处理器40为根据壁面剪切应力在一个心动周期T内的积分的绝对值以及前述壁面剪切应力的绝对值在一个心动周期T内的积分计算得出前述震荡剪切指数。
具体的，前述处理器40为根据公式：
Figure PCTCN2017082480-appb-000003
计算前述震荡剪切指数OSI。其中，τ表示WSS(Wall Shear Stress，血管壁面剪切应力)，T为一个心动周期，即从一次心跳的起始时刻到下一次心跳的起始时刻之间的时间。
前述处理器40还用于根据前述回波信号获得血管内多个点的质点流射速度之后，控制在前述超声图像上叠加显示前述血管内多个点的质点流射速度。
在一些实施例中，当前述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数时，前述处理器405控制前述显示装置200显示超声图像和血管壁剪切指数，包括：控制前述显示装置200通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数。
前述处理器40控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值随时间变化的图谱和/或震荡剪切指数值在不同心动周期的值和/或图 谱；或者前述处理器40控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
请参阅图5，为速度梯度值、壁面剪切应力值和/或震荡剪切指数值的图谱示意图。如图5所示，血管上的多个节段区域Q1代表了不同大小的值。它可以是速度梯度的值，WSS或者OSI的值。同理，还可以显示血管壁的下壁。这个血管壁上的图谱可以随时间不断的更新变化。还可以手动提取血管壁上任意位置的速度梯度、WSS随时间变化的曲线和OSI在不同心动周期的值。在一些实施例中，前述血管上的各个区域Q1的颜色根据速度梯度、WSS和OSI值的不同而不同，由于申请文件附图的要求，图中并未示出颜色。在一些实施例中，前述血管上的各个区域Q1的颜色相同，颜色深浅程度根据速度梯度、WSS和OSI值的不同而不同。
前述处理器40还用于控制显示前述至少一个待侧位置处的血管壁中在一段时间内或一个心动周期内的具有最大或最小或平均速度梯度、壁面剪切应力的位置和和多个心动周期内具有最大或最小或平均震荡剪切指数的位置及对应的最大或最小或平均速度梯度、壁面剪切应力和震荡剪切指数的数值。
前述处理器40还用于根据超声图像找到颈动脉分叉位置；前述显示控制模块405还用于控制显示前述颈动脉分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
请一并参阅图6，为颈动脉分叉位置的示意图。前述处理器40具体为根据超声图像确定感兴趣区域中的血管的中心线Z1；以及确定有多条中心线Z1相交叉的位置为前述颈动脉分叉位置J1。
本发明的实施例中不限于只在颈动脉分叉位置进行速度梯度、壁面剪切应力和/或震荡剪切指数的显示和标记，还可以同时应用到其他的血管交叉位置处。例如，在其中一个实施例中，处理器还根据超声图像找到血管分叉位置，并控制显示血管分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。更进一步地，处理器还可以根据超声图像确定感兴趣区域中的血管的中心线；以及确定有多条中心线相交叉的位置为血管分叉位置。
其中，本申请中前述的超声图像可为二维图像或三维图像。
其中，在一些实施例中，前述处理器40根据位于待测位置附近多个点的 质点流射速度，计算待测位置处的血管壁剪切指数后，前述处理器40还可自动生成指数标记，并在超声图像的血管壁上的待测位置处标记与前述待测位置关联对应的指数标记。其中，指数标记的属性与前述血管壁剪切指数的计算值关联对应；前述属性可为前述标记区域的与计算值关联对应的长度、颜色等。
如图1所示，前述超声成像设备100还包括存储器60，在一些实施例中，前述存储器60中存储有程序指令，前述处理器40通过调用执行前述存储器60中的程序指令而执行前述的功能步骤。
在一些实施例中，本申请还提供一种计算机可读介质，前述计算机可读介质中存储有可被处理器40调用而执行前述功能的程序指令。其中，在本申请中，前述计算机可读存储介质即为前述存储器60。前述存储器60可为存储卡、固态存储器、硬盘、光碟等存储装备。
其中，前述处理器40可为中央处理器、微处理器、单片机、数字信号处理器等。前述输入装置50可为鼠标、触摸板等。在一些实施例中，当前述显示装置200为整合在超声成像设备100中的显示屏且前述输入装置50为触摸板时，前述输入装置50还可与前述显示装置200整合成触摸显示屏。
请参阅图7，为本发明一实施例中的利用超声检测血管壁剪切指数的方法的流程图。其中，前述方法中的步骤并不限于图中的顺序，本申请技术领域的人员可以根据需要进行变换。前述方法应用于前述的超声成像设备100中。前述方法包括如下步骤：
向包含血管的感兴趣区域发射超声波(S701)。
在一些实施例中，前述步骤S701包括：对扫描目标以多角度偏转发射的方式发射多个角度偏转的第一超声波。在一些实施例中，前述步骤S701还包括：向包含血管的感兴趣区域发射第二超声波。其中，前述第一超声波可先于前述第二超声波发射，或者后于前述第二超声波发射。
接收超声波，获得回波信号(S702)。
根据前述回波信号获得超声图像(S703)。
在一些实施例中，前述步骤S703包括：根据响应第二超声波反射回来的第二回波信号获得前述超声图像，前述第一超声波不同于第二超声波。
根据前述回波信号，获得血管内多个点的质点流射速度，前述质点流射速 度包括血流速度大小和方向(S704)。
在一些实施例中，前述步骤S704包括：根据多个点的各个角度响应第一超声波反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到前述多个点的质点流射速度。
确定超声图像中的血管壁(S705)。在一些实施例中，前述步骤S705包括：响应在前述超声图像上增加的血管壁标识确定前述待检测血管位置的血管壁。
在另一些实施例中，前述步骤S705包括：判断出前述超声图像中的亮度高于一预设亮度阈值的区域，确定前述亮度高于前述预设亮度阈值的区域为血管壁。在再一些实施例中，前述步骤S705包括：计算待检测血管位置的血流能量；寻找血流能量的边缘处；以及判断前述超声图像中的亮度高于前述预设亮度阈值且处于血流能量的边缘处的区域，确定前述亮度高于前述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
其中，前述“寻找血流能量的边缘处”包括：将血流能量与一能量阈值进行比较，确定血流能量低于前述能量阈值的位置为前述血流能量的边缘处。
获得血管壁上的待测位置(S706)。其中，前述待测位置可根据在前述超声图像上增加的血管壁标识来确定，例如确定至少包括前述血管壁标识的区域为待测位置。
根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数(S707)。
在一些实施例中，前述步骤S707包括：确定待测位置处血管壁的切线方向；提取位于待测位置附近多个点的质点流射速度；计算多个点的质点流射速度沿切线方向的速度分量；根据前述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
在一些实施例中，前述“确定待测位置处血管壁的切线方向”包括：响应对前述血管壁标识的调节动作，确定调节后前述血管壁标识中用于标记切线方向的切线标记的方向为前述血管壁的切线方向。
在一些实施例中，前述血管壁剪切指数包括速度梯度，前述“根据前述 计算出来的多个速度分量获得待测位置处的血管壁剪切指数”包括：将前述多个速度分量对当前待测位置处的血管壁的法相半径求导得到前述速度梯度。
在一些实施例中，为根据公式
Figure PCTCN2017082480-appb-000004
计算血管壁的速度梯度。其中前述公式中VT表示速度分量，即速度沿血管壁的切向分量，前述速度梯度为速度分量在血管壁的半径r＝R这一法相半径处求导得到的。
在一些实施例中，前述前述血管壁剪切指数还包括壁面剪切应力，前述“根据前述计算出来的多个速度分量获得待测位置处的血管壁剪切指数”还包括：对前述血流粘滞系数与前述速度梯度求积计算得出前述壁面剪切应力。
具体的，为根据公式：
Figure PCTCN2017082480-appb-000005
计算得出血管壁剪切指数中的壁面剪切应力。其中，τ表示WSS(Wall Shear Stress，血管壁面剪切应力)，μ是液体粘滞系数。vT表示速度的切向分量，r是法向半径。
在一些实施例中，前述血管壁剪切指数还包括震荡剪切指数(OSI-Oscillatory Shear Index)，前述步骤“根据前述计算出来的多个速度分量获得待测位置处的血管壁剪切指数”还包括：根据壁面剪切应力在一个心动周期T内的积分计算得出前述震荡剪切指数。
其中，所述“根据壁面剪切应力在一个心动周期T内的积分计算得出前述震荡剪切指数”进一步包括：根据壁面剪切应力在一个心动周期T内的积分的绝对值以及前述壁面剪切应力的绝对值在一个心动周期T内的积分计算得出前述震荡剪切指数。具体的，为根据公式：
Figure PCTCN2017082480-appb-000006
计算前述震荡剪切指数。其中，τ表示WSS(Wall Shear Stress，血管壁面剪切应力)。
显示超声图像和血管壁剪切指数(S508)。在一些实施例中，前述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数，前述步骤S508包括：通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面 剪切应力和/或震荡剪切指数。
其中，前述“通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数”还进一步包括：控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值随时间变化的图谱；或者控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
在一些实施例中，前述“通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数”还进一步包括：控制显示前述至少一个待侧位置处的血管壁中具有最大或最小速度梯度、壁面剪切应力和震荡剪切指数的位置及对应的最大或最小速度梯度、壁面剪切应力和震荡剪切指数的数值。
其中，在一些实施例中，前述利用超声检测血管壁剪切指数的方法，在前述步骤S704之后，还包括步骤：在超声图像上叠加显示前述血管内多个点的质点流射速度。如图3和图5所示，在超声图像上叠加多个箭头标识，箭头的长度标识速度大小，箭头的指向标识速度方向。当然除了采用箭头标识血管内多个点的质点流射速度时还可以采用其他速度指示器，例如，颗粒点(颗粒点的大小表示速度的大小，颗粒流动的方向表示速度方向)，三角渲染框(三角框面积表示速度的大小，三角框顶点表示速度方向)等等。
其中，在一些实施例中，前述利用超声检测血管壁剪切指数的方法还包括步骤：根据超声图像找到颈动脉分叉位置；以及控制显示前述颈动脉分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
其中，前述步骤“根据超声图像找到颈动脉分叉位置”包括：根据超声图像确定感兴趣区域中的血管的中心线；以及确定有多条中心线相交叉的位置为前述颈动脉分叉位置。
请参阅图8，为本发明另一实施例中的利用超声检测血管壁剪切指数的方法的流程图。在另一实施例中，前述方法包括步骤：
向包含血管的感兴趣区域以多角度偏转发射的方式发射多个角度偏转的第一超声波(S801)。
向包含血管的感兴趣区域发射第二超声波(S802)。其中，前述第一超声 波不同于第二超声波。
接收第一超声波获得第一回波信号，接收第二超声波获得第二回波信号(S803)。
根据前述第二回波信号获得超声图像(S804)。
根据前述第一回波信号，获得血管内多个点的质点流射速度，前述质点流射速度包括血流速度大小和方向(S805)。
确定超声图像中的血管壁(S806)。
获得血管壁上的待测位置(S807)。
根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数(S808)。
显示超声图像和血管壁剪切指数(S809)。
其中，前述步骤S804-S809分别一一对应图7中的步骤S703-S708，其具体包括的更详细的步骤请参考图7中的步骤S703-S708部分的描述，在此不再多加描述。
请参阅图9，为本发明另一些实施例中的利用超声检测血管壁剪切指数的方法的流程图。在本实施例中，前述方法包括步骤：
向包含血管的感兴趣区域发射超声波(S901)。
接收超声波，获得回波信号(S902)。
根据前述回波信号获得超声图像(S903)。
根据前述回波信号，获得血管内多个点的质点流射速度，前述质点流射速度包括血流速度大小和方向(S904)。
确定超声图像中的血管壁及待测位置(S905)。
根据位于血管壁的待测位置附近多个点的质点流射速度，计算待测位置处对应的血管壁剪切指数(S906)。
生成指数标记，指数标记的属性与前述血管壁剪切指数的计算值关联对应(S907)。具体的，前述指数标记的属性包括但不限于长度、颜色等，可以根据前述血管壁剪切指数生成具有对应长度、颜色等属性的指数标记。
在血管壁上的待测位置处标记与前述待测位置关联对应的指数标记(S908)。
其中，本实施例中的步骤S901-S904与图7中的步骤S701-S704一一对应，步骤S905与图7中的步骤S705-S706对应，步骤S906与图7中的步骤S707对应，该些步骤具体包括的更详细的步骤请参考图7中的对应步骤部分的描述，在此不再多加描述。
其中，前述存储器60/计算机可读存储介质中存储的多条程序指令被处理器40调用执行后，可执行图7-图9任一附图中所示的方法中的部分步骤或全部步骤或其中步骤的任意组合。
从而，本申请通过较低的成本即可准确地检测血管壁位置处包括速度梯度、壁面剪切应力和震荡剪切指数在内的血管壁剪切指数。
以上所述是本发明的优选实施例，应当指出，对于本技术领域的普通技术人员来说，在不脱离本发明原理的前提下，还可以做出若干改进和润饰，这些改进和润饰也视为本发明的保护范围。

Claims (40)

  1. 一种超声成像设备，其特征在于，包括：
    探头；
    发射电路，用于激励所述探头向包含血管组织的感兴趣区域发射超声波；
    接收电路，用于接收所述超声波发射后所产生的回波信号；以及
    处理器，用于执行如下步骤：
    根据所述回波信号获得所述感兴趣区域的超声图像；
    根据所述回波信号获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；
    确定超声图像中的血管壁，以及获得血管壁上的待测位置；
    根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数；以及
    控制一显示装置显示超声图像和血管壁剪切指数。
  2. 如权利要求1所述的超声成像设备，其特征在于，所述发射电路激励所述探头向包含血管组织的感兴趣区域发射的超声波包括以多角度偏转发射的方式发射多个角度偏转的第一超声波，所述处理器根据接收电路接收的多个点的各个角度反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，并将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到所述多个点的质点流射速度。
  3. 如权利要求2所述的超声成像设备，其特征在于，所述发射电路激励所述探头向包含血管组织的感兴趣区域发射的超声波还包括第二超声波，所述图像生成模块根据接收电路接接收第二超声波获得的第二回波信号生成超声图像，其中，所述第一超声波不同于第二超声波。
  4. 如权利要求1所述的超声成像设备，其特征在于，所述处理器根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数，包括：
    确定待测位置处血管壁的切线方向；
    提取位于待测位置附近多个点的质点流射速度；
    计算多个点的质点流射速度沿切线方向的速度分量；
    根据所述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
  5. 如权利要求4所述的超声成像设备，其特征在于，所述处理器确定待测位置处血管壁的切线方向包括：
    响应对所述血管壁标识的调节动作，确定调节后所述血管壁标识中用于标记切线方向的切线标记的方向为所述血管壁的切线方向。
  6. 如权利要求1所述的超声成像设备，其特征在于，所述处理器响应在所述超声图像上增加的血管壁标识的确定所述待检测血管位置的血管壁。
  7. 如权利要求1所述的超声成像设备，其特征在于，所述处理器判断出所述超声图像中的亮度高于一预设亮度阈值的区域，确定所述亮度高于所述预设亮度阈值的区域为血管壁。
  8. 如权利要求1所述的超声成像设备，其特征在于，所述处理器计算待检测血管位置的血流能量，寻找血流能量的边缘处；以及判断所述超声图像中的亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域，确定所述亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
  9. 如权利要求8所述的超声成像设备，其特征在于，所述处理器还将血流能量与一能量阈值进行比较，确定血流能量低于所述能量阈值的位置为所述血流能量的边缘处。
  10. 如权利要求1所述的超声成像设备，其特征在于，所述血管壁剪切指数包括速度梯度，所述处理器还将所述多个速度分量对当前待测位置处的血管壁的法相半径求导得到所述速度梯度。
  11. 如权利要求10所述的超声成像设备，其特征在于，所述血管壁剪切指数还包括壁面剪切应力，所述处理器还对所述血流粘滞系数与所述速度梯度求积计算得出所述壁面剪切应力。
  12. 如权利要求11所述的超声成像设备，其特征在于，所述血管壁剪切指数还包括震荡剪切指数，所述处理器还根据壁面剪切应力在一个心动周期内的积分计算得出所述震荡剪切指数。
  13. 如权利要求1-12任一项所述的超声成像设备，其特征在于，所述处理器还在所述分析模块根据所述回波信号获得血管内多个点的质点流射速度之后，控制在所述超声图像上叠加显示所述血管内多个点的质点流射速度。
  14. 如权利要求1所述的超声成像设备，其特征在于，所述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数，所述处理器控制所述显示装置显示超声图像和血管壁剪切指数，包括：
    控制所述显示装置通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数。
  15. 如权利要求14所述的超声成像设备，其特征在于，所述处理器控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值随时间变化的图谱和/或震荡剪切指数值在不同心动周期的值和/或图谱；或者
    控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
  16. 如权利要求14所述的超声成像设备，其特征在于，所述处理器还用于控制显示所述至少一个待侧位置处的血管壁中在一段时间内或一个心动周期内的具有最大或最小或平均速度梯度、壁面剪切应力的位置和多个心动周期内具有最大或最小或平均震荡剪切指数的位置及对应的最大或最小或平均速度梯度、壁面剪切应力和震荡剪切指数的数值。
  17. 如权利要求14所述的超声成像设备，其特征在于，所述处理器还根据超声图像找到血管分叉位置，并控制显示所述血管分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
  18. 如权利要求17所述的超声成像设备，其特征在于，所述处理器还根据超声图像确定感兴趣区域中的血管的中心线；以及确定有多条中心线相交叉的位置为所述血管分叉位置。
  19. 如权利要求1-12任一项所述的超声成像设备，其特征在于，所述超声图像为二维图像或三维图像。
  20. 一种利用超声检测血管壁剪切指数的方法，其特征在于，所述方法包括：
    向包含血管的感兴趣区域发射超声波；
    接收超声波，获得回波信号；
    根据所述回波信号获得超声图像；
    根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速 度包括血流速度大小和方向；
    确定超声图像中的血管壁；
    获得血管壁上的待测位置；
    根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数；
    显示超声图像和血管壁剪切指数。
  21. 如权利要求20所述的方法，其特征在于，所述步骤“向包含血管的感兴趣区域发射超声波”包括：
    对扫描目标以多角度偏转发射的方式发射多个角度偏转的第一超声波；
    所述步骤“根据所述回波信号，获得血管内多个点的质点流射速度”包括：
    根据多个点的各个角度反射回来的第一回波信号分别得到每个点沿各个角度的速度分量，将得到的每个点的不同角度的速度分量分别做角度拟合，合成得到所述多个点的质点流射速度。
  22. 如权利要求21所述的方法，其特征在于，所述步骤“向包含血管的感兴趣区域发射超声波”还包括：所述向包含血管的感兴趣区域发射第二超声波；所述步骤“根据所述回波信号获得超声图像”包括：
    接收第二超声波，获得第二回波信号；
    根据所述第二回波信号获得超声图像，所述第一超声波不同于第二超声波。
  23. 如权利要求20所述的方法，其特征在于，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”包括：
    确定待测位置处血管壁的切线方向；
    提取位于待测位置附近多个点的质点流射速度；
    计算多个点的质点流射速度沿切线方向的速度分量；
    根据所述计算出来的多个速度分量获得待测位置处的血管壁剪切指数。
  24. 如权利要求23所述的方法，其特征在于，所述步骤“确定所述血管壁的切线方向”包括：
    响应对所述血管壁标识的调节动作，确定调节后所述血管壁标识中用于标记切线方向的切线标记的方向为所述血管壁的切线方向。
  25. 如权利要求20所述的方法，其特征在于，所述步骤“确定超声图像中的血管壁”包括：
    响应在所述超声图像上增加的血管壁标识的确定所述待检测血管位置的血管壁。
  26. 如权利要求20所述的方法，其特征在于，所述步骤“确定超声图像中的血管壁”包括：
    判断出所述超声图像中的亮度高于一预设亮度阈值的区域，确定所述亮度高于所述预设亮度阈值的区域为血管壁。
  27. 如权利要求20所述的方法，其特征在于，所述步骤“确定超声图像中的血管壁”包括：
    计算待检测血管位置的血流能量；
    寻找血流能量的边缘处；以及
    在判断所述超声图像中的亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域，确定所述亮度高于所述预设亮度阈值且处于血流能量的边缘处的区域为血管壁。
  28. 如权利要求27所述的方法，其特征在于，所述步骤“寻找血流能量的边缘处”包括：
    将血流能量与一能量阈值进行比较，确定血流能量低于所述能量阈值的位置为所述血流能量的边缘处。
  29. 如权利要求20所述的方法，其特征在于，所述血管壁剪切指数包括速度梯度，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”包括：
    将所述多个速度分量对当前待测位置处的血管壁的法相半径求导得到所述速度梯度。
  30. 如权利要求29所述的方法，其特征在于，所述血管壁剪切指数还包括壁面剪切应力，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”还包括：
    对所述血流粘滞系数与所述速度梯度求积计算得出所述壁面剪切应力。
  31. 如权利要求30所述的方法，其特征在于，所述血管壁剪切指数还包 括震荡剪切指数，所述步骤“根据位于待测位置附近多个点的质点流射速度，计算待测位置处的血管壁剪切指数”还包括：
    根据壁面剪切应力在一个心动周期内的积分计算得出所述震荡剪切指数。
  32. 如权利要求20-31任一项所述的方法，其特征在于，在所述步骤“根据所述回波信号，获得血管内多个点的质点流射速度”之后，所述方法还包括步骤：
    在超声图像上叠加显示所述血管内多个点的质点流射速度。
  33. 如权利要求20所述的方法，其特征在于，所述血管壁剪切指数包括速度梯度、壁面剪切应力和/或震荡剪切指数，所述步骤“显示超声图像和血管壁剪切指数”包括：
    通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数。
  34. 如权利要求21所述的方法，其特征在于，所述步骤“通过图谱分别或同时显示至少一个待测位置处的血管壁的速度梯度、壁面剪切应力和/或震荡剪切指数”包括：
    控制显示一个待测位置处的血管壁的速度梯度值、壁面剪切应力值随时间变化的曲线和/或震荡剪切指数在不同心动周期的值和/或图谱；或者
    控制切换显示多个待测位置处的血管壁的速度梯度值、壁面剪切应力值和/或震荡剪切指数值在当前时刻的图谱。
  35. 如权利要求33所述的方法，其特征在于，所述方法还包括步骤：
    控制显示所述至少一个待侧位置处的血管壁中在一段时间内或一个心动周期内的具有最大或最小或平均速度梯度、壁面剪切应力的位置和多个心动周期内具有最大或最小或平均震荡剪切指数的位置及对应的最大或最小或平均速度梯度、壁面剪切应力和震荡剪切指数的数值。
  36. 如权利要求33所述的方法，其特征在于，所述方法还包括步骤：
    根据超声图像找到血管分叉位置；以及
    控制显示所述血管分叉位置的速度梯度、壁面剪切应力和/或震荡剪切指数。
  37. 如权利要求36所述的方法，其特征在于，所述步骤“根据超声图像 找到血管分叉位置”包括：
    根据超声图像确定感兴趣区域中的血管的中心线；以及
    确定有多条中心线相交叉的位置为所述血管分叉位置。
  38. 如权利要求20所述的方法，其特征在于，所述超声图像为二维图像或三维图像。
  39. 一种利用超声检测血管壁剪切指数的方法，其特征在于，所述方法包括：
    向包含血管的感兴趣区域发射超声波；
    接收超声波，获得回波信号；
    根据所述回波信号获得超声图像；
    根据所述回波信号，获得血管内多个点的质点流射速度，所述质点流射速度包括血流速度大小和方向；
    确定超声图像中的血管壁及待测位置；
    根据位于血管壁的待测位置附近多个点的质点流射速度，计算待测位置处对应的血管壁剪切指数；
    生成指数标记，指数标记的属性与所述血管壁剪切指数的计算值关联对应；
    在血管壁上的待测位置处标记与所述待测位置关联对应的指数标记。
  40. 一种计算机可读存储介质，存储有多条程序指令，其特征在于，所述多条程序指令用于被处理器调用后执行如权利要求20-39任一项所述的方法中的步骤。
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