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WO2014190541A1 - Procédé et système de mesure de l'angle de phase d'une contrainte de cisaillement à la paroi - Google Patents

Procédé et système de mesure de l'angle de phase d'une contrainte de cisaillement à la paroi Download PDF

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Publication number
WO2014190541A1
WO2014190541A1 PCT/CN2013/076553 CN2013076553W WO2014190541A1 WO 2014190541 A1 WO2014190541 A1 WO 2014190541A1 CN 2013076553 W CN2013076553 W CN 2013076553W WO 2014190541 A1 WO2014190541 A1 WO 2014190541A1
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Prior art keywords
stress
phase angle
displacement
wall
interest
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Chinese (zh)
Inventor
郑海荣
牛丽丽
钱明
孟龙
肖杨
王丛知
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Shenzhen Institute of Advanced Technology of CAS
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Shenzhen Institute of Advanced Technology of CAS
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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
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/481—Diagnostic techniques involving the use of contrast agents, e.g. microbubbles introduced into the bloodstream
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/06—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—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
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties

Definitions

  • the present application relates to a technique for measuring stress in a pipe wall, and more particularly to a method and system for measuring a phase angle of a pipe wall stress.
  • Cardiovascular disease has become the "top killer” with the highest cause of death in human beings. It is also a "silent and fierce" of people's health. There is an urgent need to develop new early diagnostic methods.
  • Vascular endothelial cells lining the inner surface of the entire cardiovascular system are the dividing cells between the blood vessel wall and the blood, and form the basis of the cardiovascular closed conduit system. The function of vascular endothelial cells is complex and diverse, and maintains the homeostasis of the cardiovascular system as an important "regulatory tissue" in the body.
  • vascular endothelial dysfunction is closely related to the occurrence and development of various cardiovascular diseases, both as an early manifestation of cardiovascular disease and as a first step in the development of atherosclerotic morphology. Therefore, the correct evaluation of vascular endothelial function and acute identification of early vascular lesions can provide an effective means for early diagnosis and prevention of common cardiovascular diseases such as hypertension, coronary heart disease, diabetes and their corresponding target organ diseases, and provide a new direction for clinical treatment.
  • SPA stress phase angle
  • the stress phase angle reflects the unsynchronization of pressure and fluid waveforms. It is the only parameter that affects the effects of arterial wall mechanics and fluid mechanics on vascular endothelial cells. Therefore, if the role of the stress phase angle in the detection of vascular lesions can be clarified, new diagnostic methods and evidences for early vascular lesions can be provided.
  • the current research mainly verifies the correctness of the stress phase angle theory from the cellular level through computer simulation.
  • Hasegawa et al. used a radio frequency echo signal obtained at a high frame rate to simultaneously measure the radial strain and flow field velocity of the arterial wall. However, the method calculates the flow field velocity depending on the angle between the ultrasound beam and the direction of blood flow. J. Luo et al. used the speckle tracking method to simultaneously measure the axial velocity and blood flow velocity of the arterial wall. However, this method requires a higher frame rate (8 kHz).
  • the current magnetic resonance imaging mentioned in the literature cannot meet the requirements of real-time measurement, and the reported ultrasonic methods have special requirements for imaging systems, and they all have certain limitations.
  • the non-transparency of the flow path or fluid makes it difficult to apply the widely used optical methods. Summary of the invention
  • the technical problem to be solved by the present application is to provide a real-time and accurate method for measuring the phase angle of the pipe wall stress in view of the deficiencies of the prior art.
  • Another technical problem to be solved by the present application is to provide a measurement system based on the above method.
  • a method for measuring a phase angle of a pipe wall stress comprising:
  • the high-frequency ultrasonic imaging device is used to acquire the ultrasonic images of the multi-frame regions of interest continuously; the cross-correlation analysis is performed on the corresponding regions of the two adjacent ultrasonic images to obtain the circumferential stress and the flow field shear stress of the pipe wall;
  • a waveform diagram showing the circumferential stress of the tube wall and the shear stress of the flow field with respect to time is measured, and the stress phase angle is measured.
  • the imaging device acquires an ultrasound image of the region of interest in at least three consecutive cardiac cycles; the waveform of the circumferential stress and the flow field shear stress with respect to time is plotted, and the measured stress phase angle includes: The stress phase angle is measured by a waveform diagram of the stress and blood flow shear stress as a function of the cardiac cycle.
  • the use of the high-frequency ultrasound imaging apparatus to acquire an ultrasound image for continuously acquiring a plurality of regions of interest includes: acquiring an ultrasound image obtained by continuously acquiring N regions of interest using a high-frequency ultrasound imaging device g (1 )(r, e), g (2) (r,9)...g (N) (r,e), where (r,0) is the pixel coordinate in the image plane; the cross-correlation analysis is performed on the corresponding regions of two adjacent ultrasound images , obtaining the circumferential stress and flow field shear stress of the pipe wall include:
  • the flow field shear stress is calculated by the product of the fluid viscosity and the flow field velocity gradient.
  • the g (n) (r, 0) and g (n+1) (r, 0) are divided into small mesh regions, and the translational displacement of each mesh region is calculated to include: g (n) ( r, 0) and g (n+1) (r, 0) are divided into small grid regions.
  • the two-dimensional cross-correlation algorithm is combined with sub-pixel algorithm and filter interpolation algorithm to calculate the translational displacement of each mesh region.
  • the estimating the rotation and deformation of the tube wall with the displacement gradient and the high velocity gradient flow comprises: estimating the rotation and deformation of the tube wall and the high velocity gradient flow using the displacement gradient using a multiple iteration algorithm.
  • the method further includes: using an error vector culling algorithm based on frequency domain filtering and continuity equation to improve the accuracy of the result.
  • a measurement system for a tube wall stress phase angle comprising an ultrasound imaging module and a measurement module, the ultrasound imaging module comprising an ultrasound microbubble and a high frequency ultrasound imaging device, the ultrasound microbubbles being used for tracing in a fluid;
  • the high-frequency ultrasonic imaging device is configured to acquire an ultrasound image that continuously acquires a plurality of regions of interest;
  • the measurement module includes a cross-correlation analysis unit and a stress phase angle measurement unit, and the cross-correlation analysis unit is configured to perform cross-correlation analysis on corresponding regions of two adjacent ultrasonic images to obtain circumferential stress and flow field shear of the pipe wall. Stress; the stress phase angle measuring unit is used to draw a waveform diagram of the circumferential stress of the tube wall and the shear stress of the flow field with respect to time, and measure the stress phase angle.
  • the tube wall comprises a blood vessel wall;
  • the fluid comprises blood;
  • the ultrasound imaging device is further configured to acquire an ultrasound image of a region of interest within at least three consecutive cardiac cycles;
  • the stress phase angle measurement unit is further configured to draw A waveform diagram of the circumferential stress of the vessel wall and the shear stress of the blood flow as a function of the cardiac cycle, and the stress phase angle is measured.
  • the ultrasonic imaging apparatus is further configured to continuously acquire ultrasonic images g (1 )(r, e), g (2) (r, 9)...g (N) (r, e ) of the N regions of interest. ), where (r, 0) is the pixel coordinate in the image plane; the cross-correlation analysis unit is further configured to:
  • the flow field shear stress is calculated by the product of the fluid viscosity and the flow field velocity gradient.
  • the cross-correlation analysis unit is further configured to: divide g (n) (r, 0) and g (n+1) (r, 0) into small mesh regions, and use a two-dimensional cross-correlation algorithm combined with a sub-pixel algorithm And the filter interpolation algorithm calculates the translational displacement of each mesh region.
  • the cross-correlation analysis unit is further configured to: estimate the rotation and deformation of the pipe wall and the high velocity gradient flow using the displacement gradient using a plurality of iterative algorithms.
  • the cross-correlation analysis unit is further configured to: improve error accuracy by using an error vector culling algorithm based on frequency domain filtering and continuity equations.
  • cross-correlation analysis of adjacent frame images by high-frequency ultrasound imaging apparatus and ultrasonic microbubble imaging enables simultaneous, real-time, and accurate circumferential stress and flow field shearing A waveform plot of stress versus time to measure the stress phase angle.
  • the spatial resolution of the result is improved by reducing the mesh area.
  • the measurement of the stress phase angle applied to the blood vessel wall is easy for the clinician to implement, and is not easily affected by other factors.
  • the measurement module can be integrated into an existing imaging device as an image post-processing software module to enhance the function of the imaging system without hardware upgrade and upgrade of the existing clinical imaging system. Low cost, easy to be accepted by hospitals and doctors, convenient for clinical promotion.
  • FIG. 1 is a flow chart of an embodiment of a method for measuring a stress phase angle of a pipe wall according to the present application
  • Fig. 2 is a schematic view showing the structure of an embodiment of a measuring system for stress phase angle of a pipe wall according to the present application. detailed description
  • FIG. 1 is a flow chart showing an embodiment of a method for measuring a stress phase angle of a pipe wall according to the present application, including:
  • Step 102 adding ultrasound contrast microbubbles to the fluid
  • Step 104 Acquire an ultrasonic image that continuously acquires a plurality of regions of interest using a high-frequency ultrasonic imaging device;
  • Step 106 Perform cross-correlation analysis on the corresponding regions of the two adjacent ultrasonic images to obtain circumferential stress and flow field shear stress of the pipe wall;
  • Step 108 Draw a waveform diagram of the circumferential stress of the tube wall and the shear stress of the flow field with respect to time, and measure the phase angle of the stress.
  • the tube wall comprises a blood vessel wall;
  • the fluid comprises blood;
  • the step 102 comprises: acquiring an ultrasound image of the region of interest within three to five consecutive cardiac cycles using a high frequency ultrasound imaging device;
  • the misalignment 108 comprises: mapping the blood vessel A waveform diagram of wall circumferential stress and blood flow shear stress as a function of cardiac cycle, measuring the stress phase angle.
  • the step 104 includes: collecting, by using a high-frequency ultrasonic imaging device, an ultrasonic image obtained by continuously acquiring N regions of interest g (1) (r, 0), g (2) (r, 9) ... g (N) (r, e), where ( ⁇ , ⁇ ) is the pixel coordinate in the image plane;
  • step 106 includes:
  • Step S04 estimating the rotation and deformation of the pipe wall and the high-speed gradient flow by using the displacement gradient;
  • Step S06 reducing the spatial resolution of the mesh region to improve the result;
  • Step S08 performing calculation for each mesh area to obtain a wall displacement and a fluid velocity vector distribution map
  • Step S12 calculating the circumferential stress of the pipe wall by the product of the elastic modulus and the displacement gradient;
  • Step S14 passing the viscosity and flow of the fluid
  • the flow field shear stress is calculated by the product of the field velocity gradient.
  • S02 includes: dividing g (n) (r, 0) and g (n+1) (r, 0) into small mesh regions, using a two-dimensional cross-correlation algorithm to combine sub-pixel algorithms and filtering
  • the interpolation algorithm calculates the translational displacement of each grid region i or.
  • step S04 includes: estimating the rotation and deformation of the tube wall and the high velocity gradient flow using the displacement gradient using a plurality of iterative algorithms.
  • the method further includes:
  • Step 202 Adding a tracer particle to the fluid, an ultrasound contrast microbubble, and collecting a continuous multi-frame region of interest using a high frame ultrasound imaging system at a high frame rate. Ultrasound contrast images of the (vascular wall and contrast blood flow area).
  • V max FR * W / 4. W is the selected diagnostic window. If W-set, FR must ensure that the maximum speed of the ROI can be measured.
  • Continuous Multiframe is an image frame within 3 - 5 cardiac cycles.
  • the polar coordinate system is transformed into a Cartesian coordinate system.
  • the two-dimensional cross-correlation algorithm is combined with the sub-pixel algorithm and the filtering interpolation algorithm to calculate the translational displacement of each diagnostic window.
  • the multiple iterative algorithm and the error vector culling algorithm are used to improve the measurement accuracy. , reduce measurement error.
  • the two-dimensional standard cross-correlation algorithm uses the gray-scale distribution similarity of an image to calculate the displacement of two ports (ie, kl in frame 1 and frame 2). Its expression is:
  • f and g are the gray values in the two analysis windows, and A is the corresponding gray level average.
  • the sub-pixel method can be used to accurately scale to the decimal level.
  • the Gaussian peak fitting formula is adopted:
  • Rpq represents the maximum value of the cross-correlation function
  • i and ] represent the corresponding coordinates when the cross-correlation function takes the maximum value
  • R pq ⁇ ! ' , R pq + ! ' , ⁇ ( ⁇ ⁇ ) and ⁇ ( J +!) Do not represent the value of the cross-correlation function on the four grid points around R pq l, J and the nearest neighbor in the cross-correlation function array.
  • this embodiment uses median filtering and bilinear interpolation.
  • the specific formula is as follows: + ⁇ ) + threshold * std(u(x - l:x + l, yl:y + l )) + if) -threshold * std(u(x -I: x + l,y -I: y + i)
  • the iterative algorithm is used to further calculate the rotation and deformation of the region of interest through the displacement gradient of the two-dimensional translational displacement, and the two-dimensional displacement of the geometric transformation is obtained.
  • Dr r (The specific process of the x iterative algorithm is: First, set the number of iterations K (usually 2-3 times) ⁇ Then, for the kth iteration, use the k-1th displacement gradient to reset the analysis window Gray value.
  • the error vector culling algorithm is a correction method based on the continuity equation. Specifically, first, according to the initial displacement vector, an initial value vail is set, and the value val of each point is calculated by the following formula:
  • This embodiment uses a displacement gradient to estimate the rotation and deformation of the vessel wall and the high velocity gradient flow by a plurality of iterative algorithms.
  • the diagnostic window is reduced by using a cross-correlation algorithm to calculate the displacement, and the spatial resolution of the result is improved.
  • Step 206 The circumferential stress of the vessel wall is calculated by the product of the elastic modulus and the displacement gradient, and the flow field shear stress is calculated by the product of the blood viscosity and the flow field velocity gradient. Therefore, it is possible to plot the circumferential stress of the vessel wall and the curve of the blood flow shear stress as a function of the cardiac cycle, thereby measuring the stress phase angle.
  • the stress phase angle is the phase angle between the circumferential stress of the vessel wall and the shear stress of the blood flow. Studies have shown that the circumferential stress of the vessel wall is synchronous with the change in diameter. Therefore, the stress phase angle can be expressed as:
  • D is the diameter
  • Q is the blood flow
  • P is the pressure
  • ⁇ is the blood flow shear stress.
  • the resistance phase angle is determined by the outer end resistance, elasticity, and wave reflection.
  • ⁇ -Q is the phase angle (WQPA) between blood flow shear stress and blood flow
  • WQPA is closely related to the geometry of the blood vessel. It can be seen that the stress phase angle is closely related to the vessel geometry and the elasticity of the vessel wall.
  • SPA (p(0-T).
  • ⁇ is the circumferential stress
  • ⁇ is the blood flow shear stress.
  • FIG. 2 is a schematic structural view of an embodiment of a measurement system for a tube wall stress phase angle according to the present application, comprising: an ultrasound imaging module and a measurement module, the ultrasound imaging module including an ultrasonic microbubble and a high frequency ultrasound imaging device, and the ultrasonic microbubble Tracer in a fluid; a high-frequency ultrasound imaging apparatus is used to acquire an ultrasound image that continuously acquires a plurality of regions of interest; the measurement module further includes a cross-correlation analysis unit and a stress phase angle measurement unit.
  • the cross-correlation analysis unit is configured to perform cross-correlation analysis on corresponding regions of two adjacent ultrasonic images to obtain circumferential stress and flow field shear stress of the pipe wall; the stress phase angle measuring unit is used for drawing circumferential stress of the pipe wall and A waveform diagram of the flow field shear stress versus time, measuring the stress phase angle.
  • the tube wall comprises a blood vessel wall; the fluid comprises blood; the ultrasound imaging device is further configured to acquire an ultrasound image of the region of interest within three to five cardiac cycles; the stress phase angle measurement unit is further configured to draw the vessel wall circumference The stress phase angle is measured by a waveform diagram of the stress and blood flow shear stress as a function of the cardiac cycle.
  • the ultrasound imaging apparatus is further configured to continuously acquire ultrasound images g (1) (r, 0), g (2) (r, 9), ... g (N) (r ) , e), where (r, 0) is the pixel coordinate in the image plane;
  • the cross-correlation analysis unit is also used to:
  • the flow field shear stress is calculated by the product of the fluid viscosity and the flow field velocity gradient.
  • the cross-correlation analysis unit is further configured to: estimate the rotation and deformation of the tube wall and the high velocity gradient flow using the displacement gradient using a plurality of iterative algorithms.
  • the cross-correlation analysis unit is further configured to: estimate the rotation and deformation of the tube wall and the high-speed gradient flow with the displacement gradient using a multiple iteration algorithm. In one embodiment, the cross-correlation analysis unit is further configured to: use an error vector culling algorithm based on frequency domain filtering and continuity equations to improve the accuracy of the result.
  • the ultrasound imaging module is used to add a tracer particle-ultrasound contrast microbubble to the fluid, and to acquire an ultrasound contrast image of a continuous multi-frame region of interest (vessel wall and contrast blood flow region) at a high frame rate using a high frequency ultrasound imaging system.
  • V max FR * W / 4. W is the selected diagnostic window. If W-set, FR must ensure that the maximum speed of the ROI can be measured.
  • Continuous Multiframe is an image frame within 3 - 5 cardiac cycles.
  • ⁇ ⁇ ) ... ⁇ , ⁇ ) to be a continuous ultrasound contrast image
  • (r, e) is the pixel coordinate in the image plane.
  • the region of interest g (n+1) (r, 0) is then selected on f n+1) (r, e).
  • Each region of interest is divided into small grid regions - diagnostic windows.
  • the cross-correlation analysis unit first transforms the polar coordinate system into a rectangular coordinate system, and uses a two-dimensional cross-correlation algorithm combined with a sub-pixel algorithm and a filter interpolation algorithm to calculate the translational displacement of each diagnostic window, using multiple iterative algorithms.
  • the error vector culling algorithm improves measurement accuracy and reduces measurement error.
  • the two-dimensional standard cross-correlation algorithm of the cross-correlation analysis unit uses the gray-scale distribution similarity of the image to calculate the displacement of the two analysis windows (i.e., kl in the first frame and the second frame). Its table:
  • the sub-pixel method can be used to accurately scale to the decimal level.
  • the Gaussian peak fitting formula is adopted: Indicates the maximum value of the cross-correlation function, ⁇ and the corresponding coordinate indicating the maximum value of the cross-correlation function, R pq ⁇ ! ' , R pq + ! ' , ⁇ ( ⁇ ⁇ ) and ⁇ J +! ) respectively represent the values of the cross-correlation functions on the four grid points around R pq l, J and the nearest neighbor in the cross-correlation function array.
  • the present embodiment uses median filtering and bilinear interpolation, and the specific formula is as follows:
  • the iterative algorithm is used to further calculate the rotation and deformation of the region of interest through the displacement gradient of the two-dimensional translational displacement, and the two-dimensional displacement of the geometric transformation is obtained.
  • Dr 2! r (x, y).
  • an error vector culling algorithm is used for the two-dimensional displacement of the geometric transformation to improve the accuracy, and a relative displacement vector between the first frame and the second frame is obtained.
  • the error vector culling algorithm is a correction method based on the continuity equation. Specifically, first, according to the initial displacement vector, an initial value vail is set, and the value val of each point is calculated by the following formula:
  • the displacement gradient is used to estimate the rotation and deformation of the vessel wall and the high velocity gradient flow by a plurality of iterative algorithms.
  • the diagnostic window is reduced by using a cross-correlation algorithm to calculate the displacement, and the spatial resolution of the result is improved.
  • the circumferential stress of the blood vessel wall is calculated by the product of the elastic modulus and the displacement gradient, and the flow field shear stress is passed through the blood viscosity and the flow field velocity ladder.
  • the product of degrees is calculated. Therefore, it is possible to plot the circumferential stress of the vessel wall and the shear stress of the blood flow as a function of the cardiac cycle, thereby measuring the stress phase angle.
  • the stress phase angle is the phase angle between the circumferential stress of the vessel wall and the shear stress of the blood flow. Studies have shown that the circumferential stress of the vessel wall is synchronous with the change in diameter. Therefore, the stress phase angle can be expressed as:
  • D is the diameter
  • Q is the blood flow
  • P is the pressure
  • ⁇ is the blood flow shear stress.
  • the resistance phase angle is the external resistance, elasticity and wave
  • the reflection is determined.
  • ⁇ ( ⁇ -Q) is the phase angle between the blood flow shear stress and the blood flow (WQPA), and WQPA is closely related to the geometry of the blood vessel.
  • WQPA blood flow shear stress and the blood flow
  • the measurement of the stress phase angle can be carried out by the method and system of the above embodiment:
  • Preparation of blood phantom Tiny nylon particles having a diameter of 5 ⁇ m, 10 ⁇ m, or 20 ⁇ m are used as scatterers.
  • a suitable amount of nylon particles and a suitable weight of liquid (85.41% pure water, 10.25% pure glycerin, 3.42% dextran, 0.92% surfactant) were mixed by a magnetic stirrer. Filter the residual small pieces in the blood phantom. The bubbles in the blood phantom are removed by reduced pressure.
  • the ratio of water to glycerol determines the speed of sound and density of the blood phantom.
  • Pulsating circulation system It consists of Harvard's blood flow pulsation pump (55-3305, USA), pressure sensor, elastic vascular phantom, sink, and high frequency ultrasound imaging system.
  • the pulsating pump generates a pulsating flow, which passes through the transmission pipeline to the vascular phantom, which causes the vascular phantom to produce periodic contraction and relaxation, and adjusts the pumping volume, frequency, and systolic/diastolic time ratio of the pulsating pump to mimic the vascular pulsation of the human body. Blood flow movement.
  • experiments were conducted to study the effects of vessel geometry and vessel wall elasticity on the stress phase angle.
  • the prior art mainly verifies the correctness of the stress phase angle theory from the cellular level through computer simulation.
  • the measurement method of the present application can accurately obtain the waveform of the circumferential stress of the blood vessel wall and the change of the blood flow shear stress with the cardiac cycle, and measure the phase angle of the stress, which can be used to deeply study the geometrical shape of the blood vessel and the phase angle of the stress when the elasticity of the blood vessel wall changes.
  • the evolutionary law provides new means for early diagnosis of cardiovascular disease.

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Abstract

L'invention concerne un procédé de mesure de l'angle de phase d'une contrainte de cisaillement à la paroi, comprenant : l'addition de microbulles à contraste ultrasonique dans un fluide ; l'utilisation d'un dispositif d'imagerie ultrasonique à haute fréquence pour acquérir consécutivement des trames multiples d'images ultrasoniques d'une zone d'intérêt ; la réalisation d'une analyse de corrélation croisée des zones correspondant à deux images ultrasoniques voisines pour obtenir la contrainte circonférentielle (CC) à la paroi et la contrainte de cisaillement à la paroi (CCP) du champ d'écoulement ; et le traçage d'un oscillogramme du changement de la CC à la paroi et de la CCP du champ d'écoulement par rapport au temps pour mesurer un angle de phase de contrainte (APC). L'invention concerne également un système de mesure de l'angle de phase d'une contrainte de cisaillement à la paroi. Un mode de réalisation de la présente invention utilise un dispositif d'imagerie ultrasonique à haute fréquence et une imagerie à microbulles ultrasoniques pour réaliser une analyse de corrélation croisée sur des trames voisines d'images pour acquérir, de manière synchrone et précise, en temps réel, un oscillogramme de la CC et de la CCP du champ d'écoulement par rapport au temps, ce qui permet de mesurer ainsi un APC.
PCT/CN2013/076553 2013-05-31 2013-05-31 Procédé et système de mesure de l'angle de phase d'une contrainte de cisaillement à la paroi Ceased WO2014190541A1 (fr)

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WO2018195944A1 (fr) * 2017-04-28 2018-11-01 深圳迈瑞生物医疗电子股份有限公司 Appareil et procédé d'imagerie ultrasonore destinés à détecter l'indice de cisaillement de la paroi vasculaire en utilisant des ondes ultrasonores
US11398023B2 (en) 2017-05-04 2022-07-26 Koninklijke Philips N.V. System and method for concurrent visualization and quantification of wall shear stress in blood vessels

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