CN115802949A

CN115802949A - Ultrasonic imaging apparatus and display method of elasticity parameter

Info

Publication number: CN115802949A
Application number: CN202080102763.0A
Authority: CN
Inventors: 郭跃新; 李双双
Original assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Current assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority date: 2020-12-30
Filing date: 2020-12-30
Publication date: 2023-03-14
Also published as: WO2022141247A1

Abstract

An ultrasound imaging apparatus and a display method of elasticity parameters, comprising: acquiring ultrasound echo data (1 ') of a cardiac cycle of a target vessel and acquiring a target parameter trend map (2') for embodying the cardiac cycle; obtaining pulse wave propagation speed (3') corresponding to the systolic period starting time and the systolic period ending time in the cardiac cycle according to the ultrasonic echo data; displaying the target parameter trend graph, the pulse wave propagation speeds corresponding to the systolic period starting time and the systolic period ending time, and marking the systolic period starting time and the systolic period ending time (4') corresponding to the pulse wave propagation speeds on corresponding positions of the target parameter trend graph respectively. The change trend of the target parameter in the target parameter trend graph represents the cardiac cycle, and the relevance between the pulse wave propagation speed and the cardiac cycle at two moments can be visually represented by combining the systolic start time and the systolic end time which are marked in the target parameter trend graph and correspond to the pulse wave propagation speed and the displayed pulse wave propagation speed.

Description

Ultrasonic imaging apparatus and display method of elasticity parameter

Technical Field

The application relates to the field of medical instruments, in particular to an ultrasonic imaging device and a display method of elastic parameters.

Background

The cardiac cycle refers to the process that the cardiovascular system undergoes from the start of one heartbeat to the start of the next heartbeat. The cardiac cycle of one time can be divided into eight time phases, the blood pressure, the blood vessel diameter and the blood vessel elasticity under different time phases are different, a periodic dynamic change is presented, the change trends are similar (as shown in figure 1), and the three reach a peak value at the end of the rapid ejection period and then gradually decline.

The blood vessel pulse wave imaging technology is an important means for clinical angiosclerosis detection. The pulse wave is a radially pulsating, axially propagating, pulsed mechanical wave (see fig. 2) generated by the pumping of blood from the heart at the vessel wall. The pulse wave is embodied as two vessel dilations generated when the left ventricle starts pumping (rapid ejection phase) and when the pumping is finished (pre-diastole phase), respectively. The two dilations are generally labeled as the pulse waves of the early (BS) and late (ES) systoles, which travel along the artery from the proximal to the distal End. Whereas the pulse wave propagation velocity (PWV) has been shown to be positively correlated with the stiffness of the arterial wall at that moment. The velocity of the two pulse waves is recorded and provided to the clinician for determining the degree of hardening of the artery.

The current blood vessel pulse wave imaging technology adopts a time-space diagram mode (figure 3) independent of a traditional ultrasonic B diagram when displaying the pulse wave propagation process: the X-axis represents time, the Y-axis represents the horizontal position of the blood vessel, and the color represents pulse information of the blood vessel wall. And the magnitude of the pulse wave velocity is expressed in the form of a number. The disadvantages of this display approach are: the space-time diagram lacks intuitiveness in expressing time information, and cannot well show the relevance between the pulse wave generation period and the corresponding time phase.

Disclosure of Invention

The application mainly provides an ultrasonic imaging device and a display method of elasticity parameters, and aims to enhance the relevance of the elasticity parameters and a cardiac cycle.

The application provides a display method of an elasticity parameter in a first aspect, which includes:

acquiring ultrasound echo data of at least one cardiac cycle of a target vessel;

generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device;

obtaining a pulse wave propagation speed corresponding to a systolic start time in the at least one cardiac cycle and a pulse wave propagation speed corresponding to a systolic end time in the at least one cardiac cycle according to the ultrasonic echo data;

displaying the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic period starting time and the pulse wave propagation speed corresponding to the systolic period ending time on a display interface, and marking the systolic period starting time and the systolic period ending time corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively.

A second aspect of the present application provides a display method of an elasticity parameter, including:

obtaining an elastic parameter corresponding to a systolic starting time in the at least one cardiac cycle and an elastic parameter corresponding to a systolic ending time in the at least one cardiac cycle according to the ultrasonic echo data;

displaying the target parameter trend graph, the elasticity parameter corresponding to the contraction period starting time and the elasticity parameter corresponding to the contraction period ending time on a display interface, and marking the contraction period starting time and the contraction period ending time corresponding to the elasticity parameter on corresponding positions of the target parameter trend graph respectively.

A third aspect of the present application provides an ultrasound imaging apparatus comprising:

an ultrasonic probe;

the transmitting circuit is used for exciting the ultrasonic probe to transmit ultrasonic waves to a target blood vessel;

the receiving circuit is used for controlling the ultrasonic probe to receive the echo of the ultrasonic wave returned from the detected blood vessel so as to obtain an echo signal;

the human-computer interaction device is used for carrying out visual output and acquiring input of a user;

a processor for acquiring ultrasound echo data for at least one cardiac cycle of a target vessel; generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device; obtaining a pulse wave propagation speed corresponding to the systolic starting time in at least one cardiac cycle and a pulse wave propagation speed corresponding to the systolic ending time in at least one cardiac cycle according to the ultrasonic echo data; and controlling a human-computer interaction device to display the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic starting moment and the pulse wave propagation speed corresponding to the systolic ending moment on a display interface, and marking the systolic starting moment and the systolic ending moment corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively.

The present application provides in a fourth aspect an ultrasound imaging apparatus comprising:

an ultrasonic probe;

the receiving circuit is used for controlling the ultrasonic probe to receive the echo of the ultrasonic wave returned from the detected blood vessel to obtain an echo signal;

the human-computer interaction device is used for performing visual output and acquiring the input of a user;

a processor for acquiring ultrasound echo data of at least one cardiac cycle of a target vessel; generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device; obtaining an elastic parameter corresponding to a systolic starting time in the at least one cardiac cycle and an elastic parameter corresponding to a systolic ending time in the at least one cardiac cycle according to the ultrasonic echo data; and controlling a human-computer interaction device to display the target parameter trend graph, the elastic parameters corresponding to the contraction period starting time and the elastic parameters corresponding to the contraction period ending time on a display interface, and marking the contraction period starting time and the contraction period ending time corresponding to the elastic parameters on corresponding positions of the target parameter trend graph respectively.

A fifth aspect of the present application provides an ultrasound imaging apparatus comprising:

a memory for storing a program;

a processor for executing the program to implement the method as described above.

According to the ultrasonic imaging device and the display method of the elastic parameters of the embodiment, the ultrasonic echo data of at least one cardiac cycle of the target blood vessel and the target parameter trend chart for representing the at least one cardiac cycle are obtained; obtaining the pulse wave propagation speed corresponding to the systolic starting time in the at least one cardiac cycle and the pulse wave propagation speed corresponding to the systolic ending time in the at least one cardiac cycle according to the ultrasonic echo data; displaying the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic period starting time and the pulse wave propagation speed corresponding to the systolic period ending time on a display interface, and marking the systolic period starting time and the systolic period ending time corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively. The change trend of the target parameter in the target parameter trend graph represents the cardiac cycle, and the relevance between the pulse wave propagation speed corresponding to two moments and the cardiac cycle can be very intuitively represented by combining the systolic start time and the systolic end time which are marked in the target parameter trend graph and correspond to the pulse wave propagation speed and the displayed corresponding pulse wave propagation speed.

Drawings

FIG. 1 is a graph of changes in caliber and blood pressure over a single cardiac cycle;

FIG. 2 is a schematic diagram of pulse wave propagation;

FIG. 3 is a time-space diagram of a prior art ultrasound imaging device;

FIG. 4 is a block diagram of an ultrasound imaging apparatus according to an embodiment of the present invention;

FIG. 5 is a flowchart illustrating a method for displaying elastic parameters according to an embodiment of the present invention;

FIG. 6 is a flowchart illustrating a method for displaying elastic parameters according to an embodiment of the present invention;

fig. 7 is a target parameter trend chart of an embodiment of the ultrasonic imaging apparatus provided by the present invention.

Detailed Description

The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. Wherein like elements in different embodiments are numbered with like associated elements. In the following description, numerous specific details are set forth in order to provide a better understanding of the present application. However, one skilled in the art will readily recognize that some of the features may be omitted or replaced with other elements, materials, methods in different instances. In some instances, certain operations related to the present application have not been shown or described in this specification in order not to obscure the core of the present application with unnecessary detail, and it is not necessary for those skilled in the art to describe these operations in detail, so that they may be fully understood from the description in the specification and the general knowledge in the art.

Furthermore, the features, operations, or characteristics described in the specification may be combined in any suitable manner to form various embodiments. Also, the various steps or actions in the method descriptions may be transposed or transposed in order, as will be apparent to one of ordinary skill in the art. Thus, the various sequences in the specification and drawings are for the purpose of describing certain embodiments only and are not intended to imply a required sequence unless otherwise indicated where such sequence must be followed.

The ordinal numbers used herein for the components, such as "first," "second," etc., are used merely to distinguish between the objects described, and do not have any sequential or technical meaning. The term "connected" and "coupled" as used herein includes both direct and indirect connections (couplings), unless otherwise specified.

The ultrasonic imaging equipment and the elastic parameter display method can be applied to human bodies and various animals.

Aiming at the defects of the current pulse wave imaging display mode, the application provides a new elastic parameter display scheme, on one hand, the relevance of the elastic parameters and the cardiac cycle is enhanced by a target parameter trend graph capable of showing the cardiac cycle; on the other hand, the elasticity of the vessels at the target time can also be evaluated. This is illustrated in detail below by means of some examples.

As shown in fig. 4, the ultrasound imaging apparatus provided by the present invention includes an ultrasound probe 30, a transmitting/receiving circuit 40 (i.e., a transmitting circuit 410 and a receiving circuit 420), a beam forming module 50, an IQ demodulation module 60, a processor 20, a human-computer interaction device 70, and a memory 80.

The ultrasonic probe 30 includes a transducer (not shown) composed of a plurality of array elements arranged in an array, the plurality of array elements are arranged in a row to form a linear array, or are arranged in a two-dimensional matrix to form an area array, and the plurality of array elements may also form a convex array. The array elements are used for transmitting ultrasonic waves according to the excitation electric signals or converting the received ultrasonic waves into electric signals. Each array element can thus be used to perform a conversion between electrical pulse signals and ultrasound waves, so as to transmit ultrasound waves to the object to be imaged (for example, an arterial blood vessel in the present embodiment) and also to receive echoes of ultrasound waves reflected back through tissue. In the ultrasonic detection, it can be controlled by the transmitting circuit 410 and the receiving circuit 420 which array elements are used for transmitting ultrasonic waves and which array elements are used for receiving ultrasonic waves, or the time slots of the array elements are controlled for transmitting ultrasonic waves or receiving echoes of ultrasonic waves. The array elements participating in ultrasonic wave transmission can be simultaneously excited by the electric signals, so that the ultrasonic waves are transmitted simultaneously; or the array elements participating in the ultrasonic wave transmission can be excited by a plurality of electric signals with certain time intervals, so that the ultrasonic waves with certain time intervals are continuously transmitted.

The array elements, for example, using piezoelectric crystals, convert the electrical signals into ultrasound signals according to the transmit sequence transmitted by transmit circuitry 410, which may include one or more scan pulses, one or more reference pulses, one or more push pulses, and/or one or more doppler pulses, depending on the application. The ultrasonic signals include focused waves, plane waves, divergent waves, and the like according to the morphology of the waves.

The user selects a suitable position and angle by moving the ultrasonic probe 30 to transmit ultrasonic waves to the object 10 to be imaged and receive echoes of the ultrasonic waves returned by the object 10 to be imaged, and outputs ultrasonic echo signals, wherein the ultrasonic echo signals are channel analog electric signals formed by taking the receiving array elements as channels and carry amplitude information, frequency information and time information.

The transmitting circuit 410 is configured to generate a transmitting sequence according to the control of the processor 20, where the transmitting sequence is configured to control some or all of the plurality of array elements to transmit ultrasonic waves to the object to be imaged, and the transmitting sequence parameters include the position of the array element for transmission, the number of array elements, and ultrasonic beam transmitting parameters (e.g., amplitude, frequency, number of transmissions, transmitting interval, transmitting angle, wave pattern, focusing position, etc.). In some cases, the transmit circuit 410 is further configured to phase delay the transmitted beams so that different transmit elements transmit ultrasound at different times so that each transmitted ultrasound beam can be focused in a predetermined region of interest. In different operating modes, such as a B image mode, a C image mode, and a D image mode (doppler mode), the parameters of the transmitted sequence may be different, and the echo signals received by the receiving circuit 420 and processed by subsequent modules and corresponding algorithms may generate a B image reflecting the anatomical structure of the tissue, a C image reflecting the blood flow information, and a D image reflecting the doppler spectrum image.

The receiving circuit 420 is configured to receive the ultrasonic echo signal from the ultrasonic probe 30 and process the ultrasonic echo signal. The receive circuit 420 may include one or more amplifiers, analog-to-digital converters (ADCs), and the like. The amplifier is used for amplifying the received echo signal after proper gain compensation, and the amplifier is used for sampling the analog echo signal according to a preset time interval so as to convert the analog echo signal into a digitized echo signal, wherein amplitude information, frequency information and phase information are still reserved in the digitized echo signal. The data output by the receiving circuit 420 may be output to the beamforming module 50 for processing or to the memory 80 for storage.

The beam forming module 50 is in signal connection with the receiving circuit 420, and is configured to perform corresponding beam forming processing such as delaying and weighted summing on the echo signals, because distances from ultrasonic receiving points in the measured tissue to the receiving array elements are different, channel data of the same receiving point output by different receiving array elements have delay differences, delay processing is required to be performed, phases are aligned, and weighted summing is performed on different channel data of the same receiving point, so as to obtain ultrasound image data after beam forming, where the ultrasound image data output by the beam forming module 50 is also referred to as radio frequency data (RF data). The beam synthesis module 50 outputs the radio frequency data to the IQ demodulation module 60. In some embodiments, the beam forming module 50 may also output the rf data to the memory 80 for buffering or saving, or directly output the rf data to the processor 20 for image processing.

Beamforming module 50 may perform the above functions in hardware, firmware, or software, for example, beamforming module 50 may include a central controller Circuit (CPU), one or more microprocessor chips, or any other electronic components capable of processing input data according to specific logic instructions, which when implemented in software, may execute instructions stored on a tangible and non-transitory computer readable medium (e.g., memory) to perform beamforming calculations using any suitable beamforming method. The beam forming module 50 may be integrated into the processor 20 or may be separately disposed, and the invention is not limited thereto.

The IQ demodulation module 60 removes the signal carrier by IQ demodulation, extracts the tissue structure information included in the signal, and filters and removes noise, and the signal obtained at this time is called a baseband signal (IQ data pair). The IQ demodulation module 60 outputs the IQ data pair to the processor 20 for image processing.

In some embodiments, the IQ demodulation module 60 further buffers or saves the IQ data pair output to the memory 80, so that the processor 20 reads the data from the memory 80 for subsequent image processing.

The IQ demodulation module 60 may also perform the above functions in hardware, firmware or software, and in some embodiments, the IQ demodulation module 60 may also be integrated with the beam synthesis module 50 in a single chip.

The processor 20 is used to configure a central controller Circuit (CPU), one or more microprocessors, a graphics controller circuit (GPU) or any other electronic components capable of processing input data according to specific logic instructions, which may perform control on peripheral electronic components according to the input instructions or predetermined instructions, or perform data reading and/or saving on the memory 80, or may process the input data by executing programs in the memory 80, such as performing one or more processing operations on acquired ultrasound data according to one or more operating modes, the processing operations including, but not limited to, adjusting or defining the form of ultrasound waves emitted by the ultrasound probe 30, generating various image frames for display by a display of the subsequent human-computer interaction device 70, or adjusting or defining the content and form of display on the display, or adjusting one or more image display settings (e.g., ultrasound images, interface components, regions of interest) displayed on the display.

The acquired ultrasound data may be processed by the processor 20 in real time during the scan as the echo signals are received, or may be temporarily stored on the memory 80 and processed in near real time in an online or offline operation.

In this embodiment, the processor 20 controls the operations of the transmitting circuit 410 and the receiving circuit 420, for example, controls the transmitting circuit 410 and the receiving circuit 420 to operate alternately or simultaneously. The processor 20 may also determine an appropriate operation mode according to the selection of the user or the setting of the program, form a transmission sequence corresponding to the current operation mode, and send the transmission sequence to the transmitting circuit 410, so that the transmitting circuit 410 controls the ultrasound probe 30 to transmit the ultrasound wave using the appropriate transmission sequence.

The processor 20 is also configured to process the ultrasound echo signals to generate a gray scale image of the signal intensity variations over the scan range, which reflects the anatomical structure inside the tissue, referred to as a B-image. The processor 20 may output the B image to a display of the human interaction device 70 for display.

The human-computer interaction device 70 is used for human-computer interaction, namely receiving input of a user and outputting visual information; the input of a user can be received by the touch screen integrated with the display, and the touch screen can adopt a keyboard, an operating button, a mouse, a track ball, a touch pad and the like; the display can be used for outputting visual information.

Based on the ultrasonic imaging device shown in fig. 4, the display method of the elasticity parameter is shown in fig. 5, and includes the following steps:

step 1, ultrasonic echo data of at least one cardiac cycle of a target blood vessel are obtained. For example, the processor 20 controls the transmit circuit 410 to excite the ultrasound probe 30 to transmit ultrasound waves to the target blood vessel 10. The ultrasonic probe 30 emits ultrasonic waves toward the blood vessel 10 to be examined. The receiving circuit 420 controls the ultrasonic probe 30 to receive the echo of the ultrasonic wave returned from the blood vessel to be detected, and obtains an echo signal. Echo signals are acquired from the ultrasound probe 30 by the receiving circuit 420 and processed (e.g., analog-to-digital converted, beamformed, etc.) to obtain ultrasound echo data containing at least one cardiac cycle. Of course, in an alternative embodiment, the processor 20 may also directly acquire the ultrasound echo data from the memory 80, which is not described herein. In this embodiment, the ultrasound echo data is data obtained by beamforming an ultrasound echo obtained by using a blood vessel of a target object as a detection object.

And 2, generating a target parameter trend graph for representing at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend graph for representing at least one cardiac cycle from an external device. The processor 20 may generate a trend map of the target parameter for representing the cardiac cycle from the ultrasound echo data. The target parameter may be a pulsation parameter reflecting pulsation of a vessel wall of the blood vessel (e.g. in a radial direction), a velocity of blood flow in the blood vessel, or blood pressure, which may be obtained from ultrasound echo data, and which is related to cardiac pulsation, the value of which varies periodically with time, and the variation period is a cardiac cycle. The ultrasound imaging device may further comprise a communication interface (not shown in the figure) for communicating with an external device. The processor 20 may also obtain a trend map of the target parameter used to represent the cardiac cycle directly from an external device via the communication interface. The trend chart of the target parameter obtained from the external device can be blood pressure or a trend chart of an electrocardiogram parameter (an electrocardiogram signal), the trend charts of the parameters can be obtained through conventional medical devices (such as a monitor, a blood pressure measuring instrument and the like) or even wearable devices, the parameters are related to heart pulsation, the numerical value of the parameters changes periodically with time, and the change period is a heart cycle.

And 3, obtaining the elastic parameters corresponding to the systolic starting time (also called an early systolic period BS) in at least one cardiac cycle and the elastic parameters corresponding to the systolic ending time (also called a late systolic period ES) in at least one cardiac cycle according to the ultrasonic echo data. For example, the processor 20 may obtain the elasticity parameter corresponding to the systolic start time in the at least one cardiac cycle and the elasticity parameter corresponding to the systolic end time in the at least one cardiac cycle from the ultrasound echo data. The elasticity parameter is a parameter reflecting the elasticity of the blood vessel, and may be, for example, a pulse wave propagation velocity, a young's modulus, or compliance.

And 4, displaying the target parameter trend graph, the elastic parameters corresponding to the contraction period starting time and the elastic parameters corresponding to the contraction period ending time on a display interface, and marking the contraction period starting time and the contraction period ending time corresponding to the elastic parameters on corresponding positions of the target parameter trend graph respectively. For example, the processor 20 controls the human-computer interaction device 70 to display the target parameter trend graph, the elastic parameter corresponding to the systolic start time, and the elastic parameter corresponding to the systolic end time on the display interface, and mark the systolic start time and the systolic end time corresponding to the elastic parameter at corresponding positions of the target parameter trend graph. The change trend of the target parameter in the target parameter trend graph represents the cardiac cycle, and the relevance between the elastic parameter corresponding to the two moments and the cardiac cycle can be very intuitively represented by combining the systolic start time and the systolic end time marked in the target parameter trend graph and corresponding to the elastic parameter and the displayed corresponding elastic parameter.

The step 1 may acquire the ultrasound echo data of the target blood vessel in a certain time period, where the certain time period may be greater than or equal to one cardiac cycle, may be set by default of the system, or may be freely adjusted and set by the user. When acquiring the ultrasound echo data of a certain period of time, the ultrasound echo data of at least one cardiac cycle may be acquired continuously in units of one cardiac cycle, or the ultrasound echo data of a plurality of cardiac cycles may be acquired in segments. For example, in the case of real-time acquisition, the ultrasound imaging device acquires ultrasound echo data in real time according to an echo signal obtained by the ultrasound probe, and the real-time acquisition time is one or more cardiac cycles.

Of course, the present invention is not satisfied, and a more detailed embodiment is provided below. The elastic parameter may be a pulse wave propagation velocity, young's modulus or compliance, and the following description will be given by taking the elastic parameter as the pulse wave propagation velocity, as shown in fig. 6, the method for displaying the pulse wave propagation velocity includes the following steps:

step 1', ultrasound echo data of at least one cardiac cycle of a target blood vessel is acquired. For example, echo signals are acquired from the ultrasound probe 30 via the receiving circuit 420 and processed to obtain ultrasound echo data including at least one cardiac cycle, and the processor 20 acquires the ultrasound echo data of at least one cardiac cycle of the target blood vessel. And for example, the processor 20 retrieves the ultrasound echo data from memory. See step 1 of the above embodiment specifically, which is not described herein again.

And 2', generating a target parameter trend map for representing at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing at least one cardiac cycle from an external device. In the present embodiment, the target parameter is described as an example of a pulsation parameter reflecting pulsation of a blood vessel wall (for example, in a radial direction). Under the action of the heart, the vessel wall is mainly pulsating in the radial direction of the vessel. The processor 20 obtains the pulsation parameters at each time in the at least one cardiac cycle according to the ultrasound echo data, and further generates a pulsation parameter trend graph. For example, the processor 20 obtains displacement information of the upper tube wall and/or the lower tube wall of the blood vessel from the ultrasound echo data, and generates a target parameter trend map from the displacement information of the upper tube wall and/or the lower tube wall of the blood vessel.

In particular, the processor 20 detects the position of the vessel wall (upper and lower) in different frames of at least one cardiac cycle from the ultrasound echo data; calculating the radial displacement of each detection point on the vascular wall, which is arranged along the axial direction of the blood vessel, at different time points according to the positions of the vascular wall in different frames; and obtaining the pulsation parameters of the detection points at different time points according to the radial displacement of the detection points on the vessel wall. The pulsation parameter may be a vessel diameter, a change speed of the vessel diameter, a change acceleration of the vessel diameter, a displacement of a unilateral vessel wall, a radial movement speed of the unilateral vessel wall, a radial movement acceleration of the unilateral vessel wall, or the like. And subtracting the radial displacement of the upper pipe wall detection point from the corresponding radial displacement of the lower pipe wall detection point to obtain the pipe diameter variation of the blood vessel at the detection point. The first derivative and the second derivative of the radial displacement and the variation of the vessel diameter are respectively calculated in the time dimension, so that the radial velocity, the radial acceleration, the variation velocity and the variation acceleration of the vessel diameter and the like can be obtained. That is, since each parameter of the pulsation parameters can be obtained from the vessel diameter at different times, the present embodiment will be described by taking the vessel diameter as an example. Since the target parameter trend graph mainly represents each time phase of the cardiac cycle, the target parameter trend graph (taking the target parameter as the blood vessel diameter, for example, a blood vessel diameter change trend graph, as shown in fig. 7) can be generated according to the blood vessel diameter corresponding to one of the detection points.

As described in the previous embodiment, in some embodiments, the processor 20 may also obtain a trend map of the target parameter from an external device for representing the at least one cardiac cycle. The target parameters acquired from the external equipment are the same as the ultrasonic echo data in time, and the target parameter trend graph and the ultrasonic echo data can be acquired in the same time period, so that the target parameter trend graph and the ultrasonic echo data can be conveniently and temporally corresponding to each other in the follow-up process. The target parameter trend graph acquired from the external device may be a blood pressure trend graph, an electrocardiogram, or the like.

And 3', obtaining the pulse wave propagation speed corresponding to the systolic starting time in at least one cardiac cycle and the pulse wave propagation speed corresponding to the systolic ending time in at least one cardiac cycle according to the ultrasonic echo data. Specifically, by the method in step 2', the pulsation parameters of the blood vessel wall at different time points at each detection point (at least two points) can be obtained, and the processor 20 obtains the propagation speed of the pulse wave propagating on the blood vessel wall along the axial direction according to the pulsation parameters of each detection point. For example, the processor 20 detects a first time at which the beat parameter at each detection point reaches a first predetermined threshold. The first predetermined threshold may be set according to user requirements, for example, for the pulse wave in the early contraction period, the pulsation parameter may be selected as the radial displacement, and the first predetermined threshold may be the minimum value of the empirical value of the maximum radial displacement (corresponding to the peak), or may be 50% or more of the empirical value of the maximum radial displacement, or the like. For the pulse wave of late systole, the first time when the pulse parameter of each detection point is in the first predetermined threshold interval and is the maximum value is detected, the peak of the early systole can be excluded by setting the maximum value of the first predetermined threshold interval, the maximum value of the late systole (the lower peak in the cardiac cycle) can be included by setting the minimum value of the first predetermined threshold interval, and the first time when the peak of the pulse wave of the late systole is reached can be reflected by the judgment of the maximum value (the conventional mathematical method). This embodiment will be described with respect to the pulse wave in the early contraction stage as an example. The processor 20 obtains the propagation speed of the pulse wave on the blood vessel wall in the ultrasound image according to the position of each detection point in the blood vessel axial direction and the first time corresponding to each detection point. And obtaining the propagation velocity of the pulse wave at each detection point according to the position of the two adjacent detection points in the axial direction of the blood vessel and the difference value of the first time corresponding to the two adjacent detection points. In order to improve the accuracy, the selected detection points are multiple, the more the detection points are in the processing capacity range, the better the detection points are, the corresponding relation between the time and the space of each detection point is obtained, linear fitting is carried out on each point to obtain an oblique line, and the slope of the oblique line is the average propagation speed of the pulse wave in the current cardiac cycle.

Since the positions of the detection points and the corresponding first time are known, the pulse wave propagation speed at the systolic phase start (BS) and the systolic phase End (ES) of the anterior wall of the artery, the propagation speed of any detection point on the blood vessel wall, the average propagation speed of any segment, and the like can be calculated by the method. The pulse wave propagation velocity of the present embodiment may be the pulse wave propagation velocity corresponding to the detection point, or may be the average pulse wave propagation velocity of the entire blood vessel, which may reflect the elasticity of the blood vessel.

Processor 20 may also generate corresponding ultrasound images from the ultrasound echo data. For example, the blood vessels of the target object may be B-imaged (two-dimensional or three-dimensional Tissue gray scale imaging), or M-imaged and doppler-imaged, which may include Tissue Doppler Imaging (TDI) and Tissue Velocity Imaging (TVI), for example.

And 4', displaying the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic period starting time and the pulse wave propagation speed corresponding to the systolic period ending time on a display interface, and marking the systolic period starting time and the systolic period ending time corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively. The trend graph comprises one of a curve graph, a line graph, a scatter diagram, a histogram, a bar graph and a box line graph, and can reflect the change trend of the target parameters along with time. The present embodiment is illustrated by taking a graph as an example, as shown in FIG. 7, a vascular tubeThe radial trend graph comprises a curve a of the change of the pipe diameter along with time, wherein the X axis is the time, and the Y axis is the pipe diameter. Eight phases of the cardiac cycle (not shown in the figure) can be marked on the target parameter trend graph, so that the doctor can better grasp the variation trend of the target parameter. The systolic start time and the systolic end time may be marked on the coordinate axis, or may be marked on the variation curve a as shown in fig. 7. The mark of the systolic start time and the systolic end time may be the same, or may be different as shown in fig. 7, and the specific marking manner is not limited, and the two times may be marked, and certainly, the two times may be highlighted better. The pulse wave propagation speeds corresponding to the systolic period starting time and the systolic period ending time can be displayed outside the target parameter trend graph and displayed on the same display interface with the target parameter trend graph; as shown in FIG. 7, the pulse wave propagation velocity PWV corresponding to the systolic start time may be displayed at a position adjacent to the marked systolic start time _BS Marking the end time of the systolic period on the target parameter trend graph, and displaying the pulse wave propagation speed PWV corresponding to the end time of the systolic period at the position adjacent to the marked end time of the systolic period _ES . It can be seen that, compared with the current space-time diagram (fig. 3), the tube diameter variation curve a represents each time phase in a cardiac cycle better, the pulse wave propagation speed is marked on the curve, and the relevance between the pulse wave and the corresponding time phase of the cardiac cycle can be visually represented.

The processor 20 may further display an ultrasound image obtained based on the ultrasound echo data on a display interface through the human-computer interaction device 70, so that a doctor can conveniently view the target parameter trend graph and know the state of the blood vessel through the ultrasound image at the same time.

It should be noted that, the caliber, blood pressure and elasticity of blood vessel all change dynamically in a cardiac cycle, and the change trends are similar, that is, the blood pressure rises, the caliber increases and the elasticity of blood vessel rises during the contraction; blood pressure decreases, vessel diameter decreases, vessel elasticity decreases during diastole. The pulse wave occurs only twice in one cardiac cycle and can only reflect the elasticity of the blood vessels at the moment of occurrence. Can be combined with blood pressure, pulse wave or vessel diameter, pulse wave, and can be estimatedVascular elasticity at any time during a cardiac cycle. The present embodiment will be described with reference to the diameter of the vessel and the pulse wave as examples. Can obtain the target parameter D at any time in at least one cardiac cycle _t Target parameter D of the start of the systolic phase _BS And a target parameter D at the end of the systolic period _ES . Further, processor 20 bases on the target parameter D at any time _t Target parameter D of the start of the systolic phase _BS Pulse wave propagation velocity PWV corresponding to the systolic period start time _BS Target parameter D of the end of the systolic phase _ES Pulse wave propagation velocity PWV corresponding to the end time of systole _ES Calculating the pulse wave propagation velocity PWV corresponding to any time in the at least one cardiac cycle _t The pulse wave velocity PWV corresponding to the time is displayed on the display interface of the human-computer interaction device 70 _t . Therefore, the method can also estimate the elasticity of the blood vessel at any time in the cardiac cycle, and is beneficial to the evaluation of the elasticity of the blood vessel by a doctor. It should be noted that the target parameter D at any time point in the at least one cardiac cycle is _t The target parameter D may be selected by the user based on the trend graph of the target parameter, or the corresponding time is input by the user, and the processor 20 outputs the target parameter D at any time based on the ultrasonic echo data _t Or may be a characteristic time automatically determined by the system (e.g., a peak time or a valley time of the target parameter in the cardiac cycle).

Similarly, the pulse wave propagation velocity PWV corresponding to any one time _t Or can be displayed on the target parameter trend chart, namely, any moment is marked on the target parameter trend chart, and the corresponding pulse wave propagation speed PWV at any moment is displayed at the adjacent position of any marked moment _t . Is convenient for the doctor to check.

This any one time includes: at least one of the time determined according to the operation of the user, the time corresponding to the maximum value of the target parameter in the cardiac cycle and the time corresponding to the minimum value of the target parameter in the cardiac cycle. In this embodiment, the any time includes: the time corresponding to the maximum value of the target parameter in the cardiac cycle and the time corresponding to the minimum value of the target parameter in the cardiac cycle. The time corresponding to the maximum value of the target parameter in the cardiac cycle and the time corresponding to the minimum value of the target parameter in the cardiac cycle can be obtained through a trend curve in the trend graph of the target parameter, or certainly can be determined by a user, for example, the processor 20 receives a point selected by the user on the trend curve through the human-computer interaction device 70, and takes the point as the maximum value of the target parameter, and receives another point selected by the user on the trend curve, and takes the point as the minimum value of the target parameter. Therefore, the doctor can see the positions of the BS and the ES in the cardiac cycle and the corresponding pulse wave propagation speed through the target parameter trend graph, and can also see the time corresponding to the extreme value of the target parameter and the pulse wave propagation speed, so that sufficient information is provided for the doctor to evaluate the elasticity of the blood vessel and the associated time.

In this embodiment, the pulse wave propagation velocity PWV at the target time is calculated by the following formula _t ：

D _t Being a target parameter at any one time, D _BS PWV, a target parameter for the start of the systolic phase _BS The corresponding pulse wave propagation speed at the initial moment of systole, D _ES PWV, a target parameter for the end of the systolic phase _ES The pulse wave propagation speed corresponding to the end time of the systole.

For these two moments: the time corresponding to the maximum value of the target parameter in the cardiac cycle and the time corresponding to the minimum value of the target parameter in the cardiac cycle refer to the formula 1, and the corresponding pulse wave propagation velocity PWV _MAX 、PWV _MIN The calculation formula of (a) is as follows:

PWV _MAX the propagation velocity D of the pulse wave corresponding to the time corresponding to the maximum value of the target parameter in the cardiac cycle _MAX Is the maximum value of the target parameter in the cardiac cycle. PWV _MIN The propagation velocity of the pulse wave corresponding to the time corresponding to the minimum value of the target parameter in the cardiac cycle, D _MIN Is the minimum value of the target parameter in the cardiac cycle.

The points on the trend curve in the target parameter trend graph can be selected, the user wants to know the pulse wave propagation speed at any time, the target parameter trend graph displayed on the display interface through the human-computer interaction device can be selected, the processor 20 receives a selected instruction of the user through the human-computer interaction device, any selected time can be obtained from the point corresponding to the instruction, the target parameter corresponding to any selected time can be obtained according to any selected time and the trend curve, and therefore the pulse wave propagation speed PWV corresponding to any selected time can be obtained according to the formula 1 _t And displayed in the target parameter trend graph. Therefore, the method can evaluate the elasticity of the blood vessel at any time in the whole cardiac cycle, and is convenient for doctors to master the elasticity information of the blood vessel.

It should be noted that the target parameter trend graph may be obtained according to the ultrasound echo data, such as a blood vessel diameter change trend graph, a blood flow velocity change trend graph, and the like; the target parameter trend graph may also be directly obtained from an external device, such as a blood pressure trend graph, an ECG trend graph, etc., and the related description is the same as the foregoing embodiments, which is not repeated herein.

Since the young's modulus and the compliance can be calculated by the pulse wave propagation speed and the tube diameter variation, or by the pulse wave propagation speed and the blood pressure variation, in the embodiment where the elasticity parameter is the young's modulus or the compliance, only a step of calculating the young's modulus or the compliance according to the pulse wave propagation speed and the tube diameter variation, or the pulse wave propagation speed and the blood pressure variation is needed to be added.

Those skilled in the art will appreciate that all or part of the functions of the methods in the above embodiments may be implemented by hardware, or may be implemented by a computer program. When all or part of the functions of the above embodiments are implemented by a computer program, the program may be stored in a computer-readable storage medium, and the storage medium may include: a read only memory, a random access memory, a magnetic disk, an optical disk, a hard disk, etc., and the program is executed by a computer to realize the above functions. For example, the program may be stored in a memory of the device, and when the program in the memory is executed by the processor, all or part of the functions described above may be implemented. In addition, when all or part of the functions in the above embodiments are implemented by a computer program, the program may be stored in a storage medium such as a server, another computer, a magnetic disk, an optical disk, a flash disk, or a removable hard disk, and may be downloaded or copied to a memory of a local device, or may be version-updated in a system of the local device, and when the program in the memory is executed by a processor, all or part of the functions in the above embodiments may be implemented.

Reference is made herein to various exemplary embodiments. However, those skilled in the art will recognize that changes and modifications may be made to the exemplary embodiments without departing from the scope hereof. For example, the various operational steps, as well as the components used to perform the operational steps, may be implemented in differing ways depending upon the particular application or consideration of any number of cost functions associated with operation of the system (e.g., one or more steps may be deleted, modified or incorporated into other steps).

Additionally, as will be appreciated by one skilled in the art, the principles herein may be reflected in a computer program product on a computer readable storage medium, which is pre-loaded with computer readable program code. Any tangible, non-transitory computer-readable storage medium may be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-ROMs, DVDs, blu Ray disks, etc.), flash memory, and/or the like. These computer program instructions may be loaded onto a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions which execute on the computer or other programmable data processing apparatus create means for implementing the functions specified. These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including means for implementing the function specified. The computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified.

While the principles herein have been illustrated in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components and otherwise, used in the practice of the disclosure, which are particularly adapted to specific environments and operative requirements, may be employed without departing from the principles and scope of the present disclosure. The above modifications and other changes or modifications are intended to be included within the scope of this document.

The foregoing detailed description has been described with reference to various embodiments. However, one skilled in the art will recognize that various modifications and changes may be made without departing from the scope of the present disclosure. Accordingly, the disclosure is to be considered in all respects as illustrative and not restrictive, and all such modifications are intended to be included within the scope thereof. Also, advantages, other advantages, and solutions to problems have been described above with regard to various embodiments. However, the benefits, advantages, solutions to problems, and any element(s) that may cause any element(s) to occur or become more pronounced are not to be construed as a critical, required, or essential feature or element of any or all the claims. As used herein, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Furthermore, the term "coupled," and any other variation thereof, as used herein, refers to a physical connection, an electrical connection, a magnetic connection, an optical connection, a communicative connection, a functional connection, and/or any other connection.

Those having skill in the art will recognize that many changes may be made to the details of the above-described embodiments without departing from the underlying principles of the invention. Accordingly, the scope of the invention should be determined from the following claims.

Claims

A method for displaying an elasticity parameter, comprising:

acquiring ultrasound echo data of at least one cardiac cycle of a target vessel;

generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device;

obtaining a pulse wave propagation speed corresponding to a systolic start time in the at least one cardiac cycle and a pulse wave propagation speed corresponding to a systolic end time in the at least one cardiac cycle according to the ultrasonic echo data;

displaying the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic period starting time and the pulse wave propagation speed corresponding to the systolic period ending time on a display interface, and marking the systolic period starting time and the systolic period ending time corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively.
The method of claim 1, wherein generating a target parameter trend map from the ultrasound echo data for embodying the at least one cardiac cycle comprises:

and obtaining displacement information of the upper tube wall and/or the lower tube wall of the blood vessel according to the ultrasonic echo data, and generating a target parameter trend graph for representing the at least one cardiac cycle according to the displacement information of the upper tube wall and/or the lower tube wall of the blood vessel.
The method according to claim 1 or 2, wherein the displaying the pulse wave velocity corresponding to the systolic start time and the pulse wave velocity corresponding to the systolic end time on the display interface and marking the systolic start time and the systolic end time corresponding to the pulse wave velocity on the corresponding positions of the target parameter trend graph respectively comprises:

marking the systolic period starting time on the target parameter trend graph, displaying the pulse wave propagation speed corresponding to the systolic period starting time at the adjacent position of the mark, marking the systolic period ending time on the target parameter trend graph, and displaying the pulse wave propagation speed corresponding to the systolic period ending time at the adjacent position of the mark.
The method of claim 1 or 2, further comprising:

determining a target parameter D at any time during the at least one cardiac cycle _t Target parameter D of the start of the systolic phase _BS And a target parameter D at the end of the systolic period _ES ；

According to the target parameter D at any moment _t Target parameter D of the start of the systolic phase _BS Pulse wave propagation velocity PWV corresponding to systolic period start time _BS Target parameter D at the end of the systolic phase _ES And pulse wave propagation velocity PWV corresponding to the end time of systole _ES Determining the pulse wave propagation velocity PWV corresponding to any time _t Showing any one ofPulse wave propagation velocity PWV corresponding to time _t 。
The method of claim 4, wherein said any one time comprises: at least one of the time determined according to the operation of the user, the time corresponding to the maximum value of the target parameter in the at least one cardiac cycle and the time corresponding to the minimum value of the target parameter in the at least one cardiac cycle.
The method of claim 4, wherein said target parameter D is dependent on said any time instant _t Target parameter D of the start of the systolic phase _BS Pulse wave propagation velocity PWV corresponding to systolic period start time _BS Target parameter D of the end of the systolic phase _ES And pulse wave propagation velocity PWV corresponding to the end time of systole _ES Determining the pulse wave propagation velocity PWV corresponding to any time _t The method comprises the following steps:

calculating the pulse wave propagation velocity PWV corresponding to any moment according to the following formula _t ：
The method as claimed in claim 4, wherein said displaying the Pulse Wave Velocity (PWV) corresponding to any one time instant _t The method comprises the following steps:

marking any moment on the target parameter trend graph, and displaying the pulse wave propagation speed PWV corresponding to any moment at the position adjacent to the marked moment _t 。
The method of any of claims 1 to 7, wherein the trend graph comprises: a graph, a line graph, a scatter plot, a histogram, a bar graph, or a box plot.
The method of any of claims 1 to 7, wherein the target parameters comprise: a pulsation parameter reflecting pulsation of a blood vessel wall of the blood vessel, a velocity of blood flow in the blood vessel, a blood pressure, or an electrocardiographic parameter.
The method of claim 9, wherein the beating parameters comprise: the method comprises the following steps of (1) vessel diameter, change speed of the vessel diameter, change acceleration of the vessel diameter, displacement of a unilateral vessel wall, radial movement speed of the unilateral vessel wall or radial movement acceleration of the unilateral vessel wall.
A display method of elasticity parameters is characterized by comprising the following steps:

acquiring ultrasound echo data of at least one cardiac cycle of a target vessel;

generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device;

obtaining an elastic parameter corresponding to a systolic starting time in the at least one cardiac cycle and an elastic parameter corresponding to a systolic ending time in the at least one cardiac cycle according to the ultrasonic echo data;

displaying the target parameter trend graph, the elasticity parameter corresponding to the contraction period starting time and the elasticity parameter corresponding to the contraction period ending time on a display interface, and marking the contraction period starting time and the contraction period ending time corresponding to the elasticity parameter on corresponding positions of the target parameter trend graph respectively.
The method of claim 11, wherein the elasticity parameter comprises: pulse wave propagation velocity, young's modulus, or compliance.
An ultrasound imaging apparatus, comprising:

an ultrasonic probe;

the transmitting circuit is used for exciting the ultrasonic probe to transmit ultrasonic waves to a target blood vessel;

the receiving circuit is used for controlling the ultrasonic probe to receive the echo of the returned ultrasonic wave to obtain an echo signal;

the human-computer interaction device is used for performing visual output and acquiring the input of a user;

a processor for acquiring ultrasound echo data for at least one cardiac cycle of a target vessel; generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device; obtaining a pulse wave propagation speed corresponding to the systolic starting time in at least one cardiac cycle and a pulse wave propagation speed corresponding to the systolic ending time in at least one cardiac cycle according to the ultrasonic echo data; and controlling a human-computer interaction device to display the target parameter trend graph, the pulse wave propagation speed corresponding to the systolic starting moment and the pulse wave propagation speed corresponding to the systolic ending moment on a display interface, and marking the systolic starting moment and the systolic ending moment corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively.
The ultrasound imaging device of claim 13, wherein the processor generating a target parameter trend map for embodying the at least one cardiac cycle from the ultrasound echo data comprises:

and obtaining displacement information of the upper tube wall and/or the lower tube wall of the blood vessel according to the ultrasonic echo data, and generating a target parameter trend graph for representing the at least one cardiac cycle according to the displacement information of the upper tube wall and/or the lower tube wall of the blood vessel.
The ultrasonic imaging apparatus according to claim 13 or 14, wherein the processor displays the pulse wave propagation speed corresponding to the systolic start time and the pulse wave propagation speed corresponding to the systolic end time on a display interface of the human-computer interaction device, and marks the systolic start time and the systolic end time corresponding to the pulse wave propagation speed on corresponding positions of the target parameter trend graph respectively, and comprises:

marking the systolic starting time on the target parameter trend graph, displaying the pulse wave propagation speed corresponding to the systolic starting time at the adjacent marked position, marking the systolic ending time on the target parameter trend graph, and displaying the pulse wave propagation speed corresponding to the systolic ending time at the adjacent marked position.
The ultrasound imaging apparatus of claim 13 or 14, wherein the processor is further configured to:

obtaining a target parameter D at any time in the at least one cardiac cycle _t Target parameter D of the start of the systolic phase _BS And a target parameter D at the end of the systolic period _ES ；

According to the target parameter D at any moment _t Target parameter D of the start of the systolic phase _BS Pulse wave propagation velocity PWV corresponding to the systolic period start time _BS Target parameter D at the end of the systolic period _ES And pulse wave propagation velocity PWV corresponding to the end time of systole _ES Determining the pulse wave propagation velocity PWV corresponding to any time _t Controlling the human-computer interaction device to display the pulse wave propagation speed PWV corresponding to any moment on a display interface _t 。
The ultrasound imaging apparatus of claim 16, wherein the any one time instant comprises: and at least one of the time determined according to the operation of the user, the time corresponding to the maximum value of the target parameter in the at least one cardiac cycle and the time corresponding to the minimum value of the target parameter in the at least one cardiac cycle.
The ultrasound imaging apparatus of claim 16, wherein the processor is based on the target parameter D at any one time instant _t Target parameter D of the start of the systolic phase _BS Pulse wave propagation velocity PWV corresponding to systolic period start time _BS Target parameter D of the end of the systolic phase _ES And pulse wave propagation velocity PWV corresponding to the end time of systole _ES Determining the pulse wave propagation velocity PWV corresponding to any time _t The method comprises the following steps:

calculating the pulse wave propagation velocity PWV at any moment according to the following formula _t ：
The ultrasonic imaging apparatus of claim 16, wherein the processor controls the human-computer interaction device to display the pulse wave propagation velocity PWV corresponding to the target moment on the display interface _t The method comprises the following steps:

marking any moment on the target parameter trend graph, and displaying the pulse wave propagation speed PWV corresponding to any moment at the position adjacent to the marked moment _t 。
The ultrasound imaging apparatus of any of claims 13 to 19, wherein the trend graph comprises: a graph, a line graph, a scatter plot, a histogram, a bar graph, or a box plot.
The ultrasound imaging apparatus of any of claims 13 to 19, wherein the target parameters include: a pulsation parameter reflecting pulsation of a blood vessel wall of the blood vessel, a velocity of blood flow in the blood vessel, blood pressure, or an electrocardiographic parameter.
The ultrasonic imaging device of claim 21, wherein the beating parameters comprise: the method comprises the following steps of (1) vessel diameter, change speed of the vessel diameter, change acceleration of the vessel diameter, displacement of a unilateral vessel wall, radial movement speed of the unilateral vessel wall or radial movement acceleration of the unilateral vessel wall.
An ultrasound imaging apparatus, comprising:

an ultrasonic probe;

the transmitting circuit is used for exciting the ultrasonic probe to transmit ultrasonic waves to a target blood vessel;

the receiving circuit is used for controlling the ultrasonic probe to receive the echo of the returned ultrasonic wave to obtain an echo signal;

the human-computer interaction device is used for performing visual output and acquiring the input of a user;

a processor for acquiring ultrasound echo data of at least one cardiac cycle of a target vessel; generating a target parameter trend map for representing the at least one cardiac cycle according to the ultrasonic echo data, or acquiring the target parameter trend map for representing the at least one cardiac cycle from an external device; obtaining an elastic parameter corresponding to a systolic starting time in the at least one cardiac cycle and an elastic parameter corresponding to a systolic ending time in the at least one cardiac cycle according to the ultrasonic echo data; and controlling a human-computer interaction device to display the target parameter trend graph, the elastic parameters corresponding to the contraction period starting time and the elastic parameters corresponding to the contraction period ending time on a display interface, and marking the contraction period starting time and the contraction period ending time corresponding to the elastic parameters on corresponding positions of the target parameter trend graph respectively.
The ultrasound imaging device of claim 23, wherein the elasticity parameters comprise: pulse wave propagation velocity, young's modulus, or compliance.
An ultrasound imaging apparatus, comprising:

a memory for storing a program;

a processor for executing the program to implement the method of any one of claims 1-12.