WO2021223237A1 - Procédé de détermination de la morphologie du flux sanguin, dispositif ultrasonore, et support de stockage informatique - Google Patents

Procédé de détermination de la morphologie du flux sanguin, dispositif ultrasonore, et support de stockage informatique Download PDF

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Publication number
WO2021223237A1
WO2021223237A1 PCT/CN2020/089256 CN2020089256W WO2021223237A1 WO 2021223237 A1 WO2021223237 A1 WO 2021223237A1 CN 2020089256 W CN2020089256 W CN 2020089256W WO 2021223237 A1 WO2021223237 A1 WO 2021223237A1
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blood flow
blood
target area
flow
ultrasonic
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PCT/CN2020/089256
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English (en)
Chinese (zh)
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沈莹莹
杜宜纲
李雷
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深圳迈瑞生物医疗电子股份有限公司
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Priority to CN202080053442.6A priority Critical patent/CN114173674A/zh
Priority to PCT/CN2020/089256 priority patent/WO2021223237A1/fr
Publication of WO2021223237A1 publication Critical patent/WO2021223237A1/fr

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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
    • 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

Definitions

  • the embodiments of the present invention relate to the field of ultrasound detection, and more specifically, to a method for determining blood flow morphology, an ultrasound device, and a computer storage medium.
  • the blood flow velocity obtained by traditional methods such as Color Doppler and Pulsed Wave Doppler (PW) is the projection component in the ultrasonic emission direction, because the velocity as the projection component cannot reflect the blood flow. Therefore, the shape of the blood flow determined based on the projection component is also inaccurate.
  • PW Pulsed Wave Doppler
  • an embodiment of the present invention provides a method for determining blood flow morphology, the method including:
  • the morphology of blood flow in the blood vessel is displayed.
  • an embodiment of the present invention also provides a method for determining blood flow morphology, and the method includes:
  • the morphology of blood flow in the blood vessel is displayed.
  • an embodiment of the present invention also provides an ultrasonic device, including:
  • the transmission/reception selection switch is used to excite the ultrasonic probe to transmit ultrasonic beams to a target area in at least two directions via a transmitting circuit, the target area including blood vessels, and to receive the return of the ultrasonic beam from the target area Ultrasonic echo
  • a memory for storing programs executed by the processor
  • the display is used to display the shape of the blood flow in the blood vessel.
  • an embodiment of the present invention also provides a computer storage medium on which a computer program is stored, and when the computer program is executed by a processor, the steps of the method for determining the blood flow pattern described in the above aspect are implemented.
  • the embodiment of the present invention can determine the shape of blood flow based on the speed of blood flow, especially the vector speed of blood flow, which can reflect the actual condition of blood flow and provide a richer reference for hemodynamic research.
  • the parameters provide a more accurate basis for subsequent blood flow morphology analysis.
  • Figure 1 is a block diagram of an ultrasound device
  • Figure 2 is a schematic diagram of the fluid form
  • Figure 3 is a schematic flowchart of determining blood flow morphology according to an embodiment of the present invention.
  • Figure 4 is another schematic flowchart of determining blood flow morphology according to an embodiment of the present invention.
  • FIG. 5 is another schematic flowchart of determining blood flow morphology according to an embodiment of the present invention.
  • Fig. 6 is a schematic diagram of input and output of the classification neural network according to the embodiment of the present invention.
  • FIG. 7 is another schematic flowchart of determining blood flow morphology according to an embodiment of the present invention.
  • Fig. 8 is a schematic diagram showing blood flow morphology according to an embodiment of the present invention.
  • Fig. 9 is another schematic diagram showing blood flow morphology according to an embodiment of the present invention.
  • Fig. 10 is another schematic diagram showing the blood flow morphology according to the embodiment of the present invention.
  • Figure 11 is a schematic diagram showing blood flow morphology according to an embodiment of the present invention.
  • Figure 12 is another schematic diagram showing blood flow morphology according to an embodiment of the present invention.
  • Figure 13 is a schematic diagram of the cardiac cycle
  • Fig. 14 is another schematic diagram showing the blood flow morphology according to the embodiment of the present invention.
  • Fig. 15 is a schematic diagram of velocity component angle synthesis according to an embodiment of the present invention.
  • the embodiment of the present invention provides an ultrasonic device, which can obtain more accurate blood flow morphology.
  • FIG. 1 shows a block diagram of an ultrasound device.
  • the ultrasound device 10 includes an ultrasound probe 110, a transmission/reception selection switch 120, a transmission circuit 160, a reception circuit 170, a memory 130, a processor 140, and a display 150.
  • the transmission/reception selection switch 120 may excite the ultrasonic probe 110 to transmit an ultrasonic beam to the target area via the transmitting circuit 160, and receive the ultrasonic echo of the ultrasonic beam returning from the target area through the ultrasonic probe 110 via the receiving circuit 170.
  • the processor 140 may obtain an ultrasonic echo signal based on the ultrasonic echo of the ultrasonic beam, and process the ultrasonic echo signal.
  • the transmission/reception selection switch 120 may excite the ultrasonic probe 110 to transmit an ultrasonic beam to a target area via the transmitting circuit 160, the target area including blood vessels, and receive the ultrasonic wave returned from the target area through the ultrasonic probe 110 via the receiving circuit 170 Ultrasonic echo of the beam.
  • the processor 140 may obtain an ultrasonic echo signal based on the ultrasonic echo; and determine the blood flow velocity in the blood vessel based on the ultrasonic echo signal; and then obtain the blood flow morphology based on the blood flow velocity.
  • the blood flow velocity can be the vector velocity of the blood flow, and the vector velocity can be calculated by any method such as the spot tracking method, the transverse wave oscillation method, and the multi-angle deflection transmitting/receiving method.
  • the transmitting/receiving selection switch 120 can excite the ultrasonic probe 110 to transmit ultrasonic beams to a target area in at least two directions via the transmitting circuit 160, and the target area includes blood vessels, and The ultrasonic echo of the ultrasonic beam returned from the target area is received by the ultrasonic probe 110 via the receiving circuit 170.
  • the processor 140 may obtain an ultrasonic echo signal in each of the at least two directions based on the ultrasonic echo; determine the ultrasonic echo signal in each of the at least two directions according to the ultrasonic echo signal in each of the at least two directions.
  • the velocity component of the blood flow along each of the at least two directions; the vector velocity of the blood flow in the blood vessel is determined according to the velocity component in each of the at least two directions.
  • the processor 140 may also obtain an ultrasound echo signal based on the ultrasound echo; and obtain an ultrasound image of the target area based on the ultrasound echo signal. For example, beam synthesis, quadrature demodulation, wall filtering, etc. can be performed on the ultrasonic echo signal.
  • the ultrasound image obtained by the processor 140 may be stored in the memory 130. And, the ultrasound image may be displayed on the display 150.
  • the shape of blood vessels and the like may also be displayed by the display 150.
  • the display 150 in the ultrasound device 10 may be a touch display screen, a liquid crystal display screen, etc.; or the display 150 may be an independent display device such as a liquid crystal display or a TV set independent of the ultrasound device 10; or the display 150 may be Displays of electronic devices such as smartphones and tablets, etc. Wherein, the number of displays 150 may be one or more.
  • the memory 130 in the ultrasound device 10 may be a flash memory card, a solid-state memory, a hard disk, or the like. It can be a volatile memory and/or a non-volatile memory, a removable memory and/or a non-removable memory, etc.
  • the processor 140 in the ultrasound device 10 may be implemented by software, hardware, firmware, or any combination thereof, and may use a circuit, a single or multiple application specific integrated circuits (ASIC), or a single or multiple ASICs.
  • ASIC application specific integrated circuits
  • the components included in the ultrasound device 10 shown in FIG. 1 are only schematic, and may include more or fewer components.
  • the ultrasound apparatus 10 may also include input devices such as a keyboard, a mouse, a scroll wheel, a trackball, etc., and/or may include an output device such as a printer.
  • the corresponding external input/output port can be a wireless communication module, a wired communication module, or a combination of the two.
  • the external input/output ports can also be implemented based on USB, bus protocols such as CAN, and/or wired network protocols. The present invention is not limited to this.
  • FIG. 2 is a schematic diagram of some types of common fluid forms.
  • Common fluid forms include plug flow, laminar flow, vortex, turbulent, counter flow, Secondary flow, etc.
  • the common blood flow pattern in human blood vessels is laminar flow.
  • it appears as laminar flow, and its mass points move smoothly and linearly in a direction parallel to the blood vessel.
  • the flow velocity is largest at the center of the blood vessel and smallest near the blood vessel wall.
  • the secondary flow as shown in Figure 2 includes a schematic diagram along section A (longitudinal section) and a schematic diagram along section B (transverse section).
  • the secondary flow may be due to the physiological structure of blood vessel bifurcation, or it may be It is caused by the presence of lesions such as plaques.
  • blood flow morphology can also be referred to as blood flow type, type and other terms, which are not limited in this application.
  • blood flow morphology contains information related to human physiological diseases, and related analysis and research on blood flow morphology can provide a potential basis for disease diagnosis.
  • the embodiment of the present invention provides a method for determining the blood flow pattern.
  • a flowchart of the method is shown in FIG. 3, and the method includes:
  • S102 Determine the shape of the blood flow in the blood vessel according to the speed
  • the blood flow velocity in S101 refers to the vector velocity of the blood flow, and the vector velocity can be obtained by an ultrasound device.
  • a schematic flow chart of the method for determining the blood flow morphology includes:
  • S110 Transmit an ultrasonic beam to a target area, where the target area includes blood vessels;
  • S130 Determine the vector velocity of the blood flow in the blood vessel according to the ultrasonic echo signal
  • S140 Determine the shape of the blood flow in the blood vessel according to the vector velocity
  • the vector velocity of the blood flow can represent the actual flow state of the blood flow, and the vector velocity includes not only the magnitude but also the direction.
  • the direction of the vector velocity of the blood flow at different positions of the blood vessel is generally different; and the direction of the vector velocity of the blood flow at the same position of the blood vessel at different times may also be different.
  • S101 may include S110 to S130.
  • the vector velocity can be obtained based on the vector blood flow imaging method of spot tracking.
  • which can be based on ultrasound B image data, using absolute difference summation to achieve speckle tracking.
  • it can be calculated based on plane wave emission and spot tracking method.
  • the vector velocity can be obtained by the vector blood flow imaging method based on the transverse wave oscillation method.
  • the longitudinal velocity is obtained through the traditional calculation method based on the Doppler principle
  • the lateral velocity is calculated by the ultrasonic sound field that generates the lateral oscillation and then based on the autocorrelation method, and then the vector velocity is obtained by merging the longitudinal and lateral velocities.
  • a multi-angle deflection transmitting/receiving method can be used to obtain the vector velocity.
  • Each angle is calculated using the traditional Doppler principle to obtain the velocity component of the angle.
  • the speed measurement results of multiple different angles are combined to obtain the actual speed size and direction, that is, the vector speed.
  • each velocity component is equivalent to the projection of the vector velocity in the direction of the component.
  • the velocity component can also be called the sub-velocity.
  • vertical lines are made by halving the divided speeds (as shown in Figure 15). According to the intersection of the two vertical lines The target position or the vector velocity of the target point can be determined.
  • the blood flow velocity obtained by the traditional PW is based on the velocity after angle correction.
  • the above method for determining the vector velocity of blood flow does not require angle correction, and can obtain a more realistic velocity and direction of blood flow, which is more accurate than traditional angle correction. Speed can more accurately represent the actual flow state of blood flow.
  • the vector velocity mentioned in this application is the actual velocity of blood flow (such as red blood cells in the blood flow), or closer to the actual velocity of blood flow (such as red blood cells in the blood flow); its velocity direction is The actual flow direction of blood flow (such as red blood cells in the blood flow), or closer to the actual flow direction of blood flow (such as red blood cells in the blood flow); as shown in Figure 2, the direction of the vector velocity can be in the imaging plane In the interval from 0° to 360°, its direction can characterize the actual flow direction of blood flow.
  • FIG. 5 is another schematic flowchart of determining the blood flow pattern according to the embodiment of the present invention, including:
  • S1101 Transmit an ultrasonic beam to a target area along at least two directions, where the target area includes blood vessels;
  • S1102. Receive the ultrasonic echo of the ultrasonic beam returning from the target area to obtain an ultrasonic echo signal along each of the at least two directions;
  • S1103 Determine the velocity component of the blood flow in the blood vessel along each of the at least two directions according to the ultrasonic echo signals along each of the at least two directions;
  • S1104 Determine the vector velocity of the blood flow in the blood vessel according to the velocity component in each of the at least two directions;
  • S140 Determine the shape of the blood flow in the blood vessel according to the vector velocity
  • S101 in FIG. 3 includes S1101 to S1104, and S102 in FIG. 3 includes S140.
  • the shape of the blood flow in the blood vessel can be determined according to the vector velocity and the patient data as auxiliary information.
  • the patient data may refer to medical record information related to the patient.
  • the patient data as auxiliary information may include at least one of the following: age, medical history, examination location, and the like.
  • the form in S140 may be any of the following: laminar flow, turbulent flow, vortex flow, counter flow, secondary flow.
  • a pre-trained classification neural network may be used in S140 to determine the shape of the blood flow.
  • the vector velocity can be input to the classification neural network, and the output of the classification neural network, that is, the shape of the blood flow, can be obtained.
  • the classification neural network may be a convolutional neural network (convolutional neural network, CNN) based on deep learning.
  • a classification neural network may be obtained through training.
  • a training sample set can be constructed, the training sample set includes a plurality of training samples, and each training sample has a blood flow vector velocity and has been marked with a blood flow shape. Use the training sample set to train the classification neural network until it converges.
  • data can be obtained from various channels or sources as training samples.
  • it can be obtained from a doctor.
  • the doctor obtains the vector velocity of the blood flow through an ultrasound device and checks the shape of the marked blood flow through experience.
  • the vector speed can be obtained from the network or other places, and the shape can be manually labeled as a training sample.
  • an initial classification neural network can be constructed.
  • the classification neural network can include a convolutional layer, a pooling layer, a fully connected layer, and so on. Subsequently, the classification neural network can be trained, and a large number of iterations will be performed during the training process until the convergence completes the training.
  • at least one of various artificial intelligence algorithms such as backpropagation (BP), stochastic gradient descent, or learning rate attenuation can be used to optimize the network convergence, identify the type, type and distribution of blood flow, and perform Instance segmentation.
  • BP backpropagation
  • stochastic gradient descent stochastic gradient descent
  • learning rate attenuation can be used to optimize the network convergence, identify the type, type and distribution of blood flow, and perform Instance segmentation.
  • a test sample set can also be constructed to verify the classification neural network after training, so that stable neural network parameters can be obtained, and the reliability of the fluid shape can be determined.
  • the training sample set can also be updated, such as adding new training samples.
  • the classification neural network can further update the classification neural network. As an example, it can be updated after adding a certain number of new training samples. In this way, by updating the classification neural network, the output result of the classification neural network can be made more accurate.
  • the shape of the blood flow in the blood vessel can be determined based on the magnitude and direction of the vector velocity.
  • the magnitude and direction of the vector velocity can be indicated by a marker with a direction indicator (for example, an arrow, a line, or a bubble, etc.).
  • the direction of the marker can indicate the direction of the vector velocity of the blood flow corresponding to the target position.
  • the length or size of the marker can indicate the vector velocity of the blood flow corresponding to the target position.
  • feature matching can be performed on the markers contained in the target area, so as to determine the shape of the blood flow in the blood vessel.
  • markers with arrows are used to characterize the magnitude and direction of the vector velocity of blood flow in the blood vessel.
  • the length of the arrow represents the magnitude of the vector velocity
  • the direction of the arrow represents the direction of the vector velocity.
  • the blood flow pattern of the target area is the secondary flow pattern.
  • other blood flow patterns such as vortex and turbulence, you can refer to the above-mentioned similar methods for understanding, and will not be described in detail here.
  • the determination of the blood flow pattern based on the vector velocity has been related to the description. It can be understood that the present application is not limited to the two-dimensional blood flow pattern shown in FIG. 2 and may also be a three-dimensional blood flow pattern.
  • the two-dimensional blood flow shape it can be determined based on the two-dimensional vector velocity; for the three-dimensional blood flow shape, it can be determined based on the three-dimensional vector velocity, which is not limited here.
  • the three-dimensional vector velocity can also be understood by referring to the relevant description of the vector velocity obtained by the vector blood flow imaging method; among them, the way of obtaining the vector velocity for multi-angle deflection transmission/reception is different from obtaining the two-dimensional vector velocity in that the three-dimensional vector velocity Velocity needs to be obtained by angular synthesis of at least three velocity components that are not in the same plane.
  • the velocity of the blood flow in S101 may be the velocity component along the ultrasonic emission direction calculated by the ultrasonic echo signal obtained by transmitting the ultrasonic wave to the blood vessel area, and the velocity component may be determined by the ultrasonic device.
  • the obtained, as shown in Fig. 7, is a schematic flow chart of the method for determining the blood flow pattern, including:
  • S110 Transmit an ultrasonic beam to a target area, where the target area includes blood vessels;
  • S1301 Determine the velocity component of the blood flow in the blood vessel along the ultrasonic emission direction according to the ultrasonic echo signal
  • S1401 Determine the shape of the blood flow in the blood vessel according to the velocity component
  • S101 in FIG. 3 includes S110 to S1301, and S102 in FIG. 3 includes S1401.
  • the shape of the blood flow in the blood vessel can be determined according to the velocity component combined with patient data as auxiliary information.
  • the patient data may refer to medical record information related to the patient.
  • the patient data as auxiliary information may include at least one of the following: age, medical history, examination location, and the like.
  • the form in S1401 may be any one of the following: disorderly and orderly.
  • the determination of the blood flow morphology by the vector velocity is more accurate, can better reflect the actual state of the blood flow, and provide a strong basis for the subsequent blood flow morphology analysis.
  • another pre-trained classification neural network may be used in S1401 to determine the shape of the blood flow.
  • the input of this other classification neural network is the velocity component, and the output blood flow is disordered or orderly.
  • classification neural network used in S1401 may be similar to the classification neural network in S140, for example, may include a convolutional layer, a pooling layer, a fully connected layer, and the like. Regarding another classification neural network, I will not go into details here.
  • the form of blood flow in a specific area in the blood vessel may be displayed in S103, where the specific area may be a target area or a sub-area of the target area.
  • the target area is all or part of the area covered by the ultrasound beam.
  • the form of the blood flow at each position of the blood flow in a specific area can be displayed.
  • different display modes can be used to represent different forms, where the different display modes can be colors, shading, and so on.
  • the morphology of each position in a specific area is displayed. Different background colors are used to indicate different morphologies.
  • the morphologies shown include laminar flow, vortex flow and turbulent flow. form.
  • the form of the blood flow at each position of the blood flow in a specific area may be displayed, and the proportion of different forms may be displayed.
  • the three forms of laminar flow, eddy current and turbulent flow in a specific area are shown, and the proportion of each form is shown. That is, 64.4% of the specific area is laminar flow, and the specific area 26.1% of the area is vortex, and 9.5% of the specific area is turbulence.
  • S103 can display the proportions of various shapes in a specific area of the blood vessel.
  • any one of the following methods may be used to display the proportions of different forms of blood flow: pie chart, bar chart, different colors, shading differences, data reports, etc.
  • Figure 10 shows the proportions of various forms represented by a bar graph. Among them, 64.4% of the specific area is laminar flow, 26.1% of the specific area is eddy current, and the specific area is 9.5% of it is turbulent flow. It should be understood that the ratio can also be displayed in other ways, which will not be listed here.
  • the change of each ratio over time can be expressed in the form of a curve.
  • multiple curves can be used to represent the changes in the proportion of each form over time.
  • it may be displayed in a plurality of different coordinate systems.
  • they can be displayed simultaneously in the same coordinate system.
  • the horizontal axis may represent time and the vertical axis may represent the ratio, and the ratio of the different forms of blood flow at each position of the blood flow in a specific region may be displayed as the change in the cardiac cycle.
  • Figure 11 shows the changes in the proportions of laminar flow, vortex flow and turbulent flow over time. In addition, it can further display the proportions of each morphology at a specific time (such as t in Figure 11).
  • the proportions of laminar flow, vortex flow and turbulent flow are 26% and 42 respectively. % And 32%.
  • the proportion of laminar flow can be determined according to the proportion between the abscissa and the solid line
  • the proportion of eddy current can be determined according to the proportion between the solid line and the broken line
  • the proportion of turbulence can be determined according to the proportion between the broken line and 100% .
  • the specific time (t) may represent the current display frame.
  • a speed curve, a heart rate curve or other curves obtained by statistics along time can also be displayed in the same coordinate system.
  • time can be represented on the horizontal axis, and the vertical axis can be scaled, showing the proportions of each shape, and also displaying the speed curve, heart rate curve or other curves obtained by statistics along the time, so as to determine the shape of blood flow and The relationship between speed, heart rate or other parameters.
  • Figure 12 shows that the change in the proportion of laminar flow is basically the same as the speed curve, heart rate curve or other curves obtained by statistics along time (sometimes may also be inconsistent)
  • the blood vessel velocity curve far away from the heart has a lag compared to the heart rate. Since the blood flow of the human body fluctuates according to the heart rate cycle, this can more clearly reflect the proportion of the shape, the blood flow velocity, and the phase of the heart rate. Or the correspondence between other parameters.
  • the corresponding proportions of various forms of blood flow in blood vessels in a specific area within a preset period of time can also be counted; various types of blood flow in blood vessels in a specific area can be displayed. Corresponding proportions of different forms within the preset duration.
  • the preset duration may be assumed to be the length of time between the first moment and the second moment.
  • the preset duration is one cardiac cycle, or the preset duration is a duration specified by the user.
  • a cardiac cycle may refer to the time interval between two adjacent diastolic troughs (ED), as shown in FIG. 13.
  • ED diastolic troughs
  • PS systolic peaks
  • the ratio of each form within the preset time length from the first time (t0) to the second time (t1) can be determined according to FIG. 11.
  • the ratio of the area of the laminar flow area represented by the diagonal line (that is, the area between the solid line representing the laminar flow and the horizontal and vertical coordinates) to the total area of the rectangular frame can be determined as the ratio of the laminar flow within the preset time period.
  • the rectangular frame is the area enclosed by the abscissa t0 to t1 and the ordinate 0-100%.
  • the corresponding proportion of the turbulence within the preset duration can be obtained, and the corresponding proportion of the turbulence within the preset duration can be obtained.
  • any one of the following methods can be used to display the corresponding proportions of various forms of blood flow in blood vessels in a specific area within a preset period of time: pie chart, bar chart, different colors, and differences in shading. , Data report, etc.
  • a pie chart shows the corresponding proportions of laminar flow, vortex flow and turbulent flow within a preset period of time.
  • FIGS. 8 to 14 multiple embodiments for displaying the blood flow pattern in a specific area are described above in conjunction with FIGS. 8 to 14, but these are only schematic, and the shape and the like can also be displayed in other ways.
  • the blood flow patterns in multiple specific areas can also be displayed at the same time. On the one hand, the blood flow patterns of multiple specific areas can be displayed at the same time, which improves efficiency; on the other hand, the blood flow patterns of multiple specific areas displayed at the same time can be compared and analyzed to more quickly determine whether there is an abnormality.
  • ultrasound images can be obtained through ultrasound echo signals, such as ultrasound images of the target area or sub-regions of the target area; then, in S103, the ultrasound image and the blood flow morphology of the specific area can be displayed at the same time.
  • the transmission/reception selection switch 120 may excite the ultrasound probe 110 to transmit an ultrasonic beam to a target area, including blood vessels, via a transmitting circuit, and receive ultrasonic echoes of the ultrasonic beam returned from the target area.
  • the processor 140 may obtain an ultrasonic echo signal based on the ultrasonic echo; determine the vector velocity of the blood flow in the blood vessel according to the ultrasonic echo signal; determine the blood flow shape in the blood vessel according to the vector velocity.
  • the display 150 can display the form of blood flow in the blood vessel.
  • the transmission/reception selection switch 120 may excite the ultrasonic probe 110 to transmit an ultrasonic beam to a target area including blood vessels in at least two directions via the transmitting circuit, and receive the ultrasonic echo of the ultrasonic beam returned from the target area.
  • the processor 140 may obtain an ultrasonic echo signal in each of the at least two directions based on the ultrasonic echo; determine the ultrasonic echo signal in each of the at least two directions according to the ultrasonic echo signal in each of the at least two directions.
  • the velocity component of the blood flow along each of the at least two directions; the vector velocity of the blood flow in the blood vessel is determined according to the velocity component of each of the at least two directions; according to the vector velocity, Determine the shape of blood flow in the blood vessel.
  • the display 150 can display the form of blood flow in the blood vessel.
  • the embodiment of the present invention also provides a computer storage medium on which a computer program is stored.
  • the computer program is executed by a computer or a processor, the steps of the method for determining the blood flow pattern shown in any one of FIGS. 3 to 5 or FIG. 7 can be realized.
  • the computer storage medium is a computer-readable storage medium.
  • the computer program instructions when run by the computer or processor, cause the computer or processor to perform the following steps: transmit an ultrasonic beam to a target area, the target area including blood vessels; and receive the ultrasonic wave returned from the target area The ultrasonic echo of the beam to obtain the ultrasonic echo signal; according to the ultrasonic echo signal, determine the vector velocity of the blood flow in the blood vessel; according to the vector velocity, determine the blood flow form in the blood vessel; and display the blood vessel The shape of the blood flow.
  • the computer program instructions when run by the computer or processor, cause the computer or processor to perform the following steps: transmit ultrasound beams to a target area in at least two directions, the target area includes blood vessels, and receive The ultrasonic echo of the ultrasonic beam returned to the target area; the ultrasonic echo signal in each of the at least two directions is obtained based on the ultrasonic echo; the ultrasonic echo in each of the at least two directions is obtained according to the ultrasonic echo in each of the at least two directions Wave signal to determine the velocity component of the blood flow in the blood vessel along each of the at least two directions; determine the velocity component of the blood flow in the blood vessel according to the velocity component in each of the at least two directions Vector speed; according to the vector speed, determine the shape of blood flow in the blood vessel; and display the shape of blood flow in the blood vessel.
  • the computer storage medium may include, for example, a memory card of a smart phone, a storage component of a tablet computer, a hard disk of a personal computer, a read-only memory (ROM), an erasable programmable read-only memory (EPROM), a portable compact disk read-only memory ( CD-ROM), USB memory, or any combination of the above storage media.
  • the computer-readable storage medium may be any combination of one or more computer-readable storage media.
  • an embodiment of the present invention also provides a computer program product, which contains instructions, when the instructions are executed by a computer, the computer executes any one of the above-mentioned FIGS. 3 to 5 or the determination of the blood flow pattern shown in FIG. 7 Method steps.
  • the embodiment of the present invention can determine the shape of blood flow based on the speed of blood flow, especially the vector speed of blood flow, which can reflect the actual condition of blood flow and provide a richer reference for hemodynamic research.
  • the parameters provide a more accurate basis for subsequent blood flow morphology analysis.
  • the disclosed device and method may be implemented in other ways.
  • the device embodiments described above are only illustrative.
  • the division of the units is only a logical function division, and there may be other divisions in actual implementation, for example, multiple units or components may be combined or It can be integrated into another device, or some features can be ignored or not implemented.
  • the various component embodiments of the present invention may be implemented by hardware, or by software modules running on one or more processors, or by a combination of them.
  • a microprocessor or a digital signal processor may be used in practice to implement some or all of the functions of some modules in the article analysis device according to the embodiment of the present invention.
  • the present invention can also be implemented as a device program (for example, a computer program and a computer program product) for executing part or all of the methods described herein.
  • a program for realizing the present invention may be stored on a computer-readable medium, or may have the form of one or more signals.
  • Such a signal can be downloaded from an Internet website, or provided on a carrier signal, or provided in any other form.

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Abstract

Procédé de détermination de la morphologie d'un flux sanguin, dispositif ultrasonore, et support de stockage informatique. Le procédé consiste : à émettre un faisceau ultrasonore dans au moins deux sens vers une région cible comprenant un vaisseau sanguin (S1101) ; à recevoir un écho ultrasonore renvoyé pour obtenir un signal d'écho ultrasonore dans chacun desdits deux sens (S1102) ; à déterminer, en fonction du signal d'écho ultrasonore dans chaque sens, un composant de vitesse dans chaque sens destiné à la vitesse d'un flux sanguin dans le vaisseau sanguin (S1103) ; à déterminer une vitesse vectorielle du flux sanguin en fonction du composant de vitesse dans chaque sens (S1104) ; à déterminer la morphologie du flux sanguin dans le vaisseau sanguin en fonction de la vitesse vectorielle (S140) ; et à afficher la morphologie du flux sanguin dans le vaisseau sanguin (S103). De cette manière, en fonction des modes de réalisation de la présente invention, la morphologie d'un flux sanguin peut être déterminée en fonction de la vitesse du flux sanguin, spécialement la vitesse vectorielle du flux sanguin, qui peuvent refléter les conditions réelles du flux sanguin, fournir plus de paramètres de référence relatifs à la recherche hémodynamique, et fournir une base plus précise destinée à l'analyse ultérieure de la morphologie du flux sanguin.
PCT/CN2020/089256 2020-05-08 2020-05-08 Procédé de détermination de la morphologie du flux sanguin, dispositif ultrasonore, et support de stockage informatique WO2021223237A1 (fr)

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PCT/CN2020/089256 WO2021223237A1 (fr) 2020-05-08 2020-05-08 Procédé de détermination de la morphologie du flux sanguin, dispositif ultrasonore, et support de stockage informatique

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