Ultrasonic imaging device and method for displaying elastic parameters

Abstract

An ultrasonic imaging device and a method for displaying elastic parameters, comprising: acquiring ultrasonic echo data of a cardiac cycle of a target blood vessel (1'), and acquiring a target parameter trend graph for reflecting the cardiac cycle (2'); obtaining the pulse wave propagation velocities corresponding to the start time and the end time of the systolic phase within the cardiac cycle according to the ultrasonic echo data (3'); displaying the target parameter trend graph, the pulse wave propagation velocities corresponding to the start time and the end time of the systolic phase, and respectively marking the start time and the end time of the systolic phase corresponding to the pulse wave propagation velocity at corresponding positions on the target parameter trend graph (4'). Since the change trend of the target parameter in the target parameter trend graph reflects the cardiac cycle, and in combination with the start time and the end time of the systolic phase marked in the target parameter trend graph corresponding to the pulse wave propagation velocity, the displayed pulse wave propagation velocity can intuitively reflect the correlation between the pulse wave propagation velocities at the two times and the cardiac cycle.

Description

Technical Field

[0001] The present application relates to the field of medical devices, and particularly to an ultrasonic imaging device and a method for displaying elastic parameters. Background Art

[0002] The cardiac cycle refers to the process experienced by the cardiovascular system from the start of one heartbeat to the start of the next heartbeat. One cardiac cycle can be divided into eight phases. Blood pressure, blood vessel diameter, and blood vessel elasticity are all different in different phases, showing a periodic dynamic change, and the change trends are similar (such as Figure 1 ), and all three reach their peaks at the end of the rapid ejection phase and then gradually decline.

[0003] Vascular pulse wave imaging technology is an important means for clinical detection of vascular sclerosis. The pulse wave is a pulsed mechanical wave that pulsates radially and propagates axially on the blood vessel wall generated by the heart pumping blood (such as Figure 2 ). The pulse wave is specifically manifested as two vascular expansions generated when the left ventricle starts pumping blood (rapid ejection phase) and when the blood pumping ends (pre-diastolic phase) respectively. The two expansions are generally marked as the pulse waves of the early systolic (Begin of systole, BS) and the late systolic (End of systole, ES). The pulse wave will propagate along the artery from the proximal end to the distal end. And the pulse wave velocity (PWV) has been proven to be positively correlated with the arterial wall stiffness at that moment. The velocities of the two pulse waves will be recorded and provided to clinical staff for judging the degree of arterial sclerosis.

[0004] When the current vascular pulse wave imaging technology displays the propagation process of the pulse wave, it adopts a spatio-temporal map method independent of the traditional ultrasonic B-mode image ( Figure 3 ): the X-axis represents time, the Y-axis represents the horizontal position of the blood vessel, and the color represents the pulsation information of the blood vessel wall. At the same time, the magnitude of the pulse wave velocity is expressed in digital form. The defects of this display method are: the spatio-temporal map lacks intuitiveness in expressing time information and cannot well show the correlation between the occurrence period of the pulse wave and the corresponding phase. Summary of the Invention

[0005] The present application mainly provides an ultrasonic imaging device and a method for displaying elastic parameters, aiming to enhance the correlation between the elastic parameters and the cardiac cycle.

[0006] The first aspect of the present application provides a method for displaying elastic parameters, including:

[0007] Obtaining ultrasonic echo data of at least one cardiac cycle of a target blood vessel;

[0008] Generate a target parameter trend graph for reflecting the at least one cardiac cycle based on the ultrasonic echo data, or obtain a target parameter trend graph for reflecting the at least one cardiac cycle from an external device;

[0009] Obtain the pulse wave propagation velocity corresponding to the start moment of the systolic phase within the at least one cardiac cycle and the pulse wave propagation velocity corresponding to the end moment of the systolic phase within the at least one cardiac cycle based on the ultrasonic echo data;

[0010] Display the target parameter trend graph, the pulse wave propagation velocity corresponding to the start moment of the systolic phase, and the pulse wave propagation velocity corresponding to the end moment of the systolic phase on a display interface, and respectively mark the start moment of the systolic phase and the end moment of the systolic phase corresponding to the pulse wave propagation velocity at corresponding positions on the target parameter trend graph.

[0011] The second aspect of the present application provides a method for displaying elastic parameters, including:

[0012] Obtain ultrasonic echo data of at least one cardiac cycle of a target blood vessel;

[0013] Generate a target parameter trend graph for reflecting the at least one cardiac cycle based on the ultrasonic echo data, or obtain a target parameter trend graph for reflecting the at least one cardiac cycle from an external device;

[0014] Obtain the elastic parameter corresponding to the start moment of the systolic phase within the at least one cardiac cycle and the elastic parameter corresponding to the end moment of the systolic phase within the at least one cardiac cycle based on the ultrasonic echo data;

[0015] Display the target parameter trend graph, the elastic parameter corresponding to the start moment of the systolic phase, and the elastic parameter corresponding to the end moment of the systolic phase on a display interface, and respectively mark the start moment of the systolic phase and the end moment of the systolic phase corresponding to the elastic parameter at corresponding positions on the target parameter trend graph.

[0016] The third aspect of the present application provides an ultrasonic imaging device, including:

[0017] An ultrasonic probe;

[0018] A transmitting circuit for exciting the ultrasonic probe to emit ultrasonic waves to a target blood vessel;

[0019] A receiving circuit for controlling the ultrasonic probe to receive the echo of the ultrasonic wave returned from the detected blood vessel to obtain an echo signal;

[0020] A man-machine interaction device for performing visual output and obtaining user input;

[0021] A processor, configured to obtain ultrasonic echo data of at least one cardiac cycle of a target blood vessel; generate a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtain a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; obtain the pulse wave propagation velocity corresponding to the systolic start time within the at least one cardiac cycle and the pulse wave propagation velocity corresponding to the systolic end time within the at least one cardiac cycle according to the ultrasonic echo data; control a man-machine interaction device to display the target parameter trend graph, the pulse wave propagation velocity corresponding to the systolic start time, and the pulse wave propagation velocity corresponding to the systolic end time on a display interface, and respectively mark the systolic start time and the systolic end time corresponding to the pulse wave propagation velocity at corresponding positions on the target parameter trend graph.

[0022] The fourth aspect of the present application provides an ultrasonic imaging device, including:

[0023] An ultrasonic probe;

[0024] A transmitting circuit, configured to excite the ultrasonic probe to transmit ultrasonic waves to a target blood vessel;

[0025] A receiving circuit, configured to control the ultrasonic probe to receive the echo of the ultrasonic wave returned from the detected blood vessel and obtain an echo signal;

[0026] A man-machine interaction device, configured to perform visual output and obtain user input;

[0027] A processor, configured to obtain ultrasonic echo data of at least one cardiac cycle of a target blood vessel; generate a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtain a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; obtain the elasticity parameter corresponding to the systolic start time within the at least one cardiac cycle and the elasticity parameter corresponding to the systolic end time within the at least one cardiac cycle according to the ultrasonic echo data; control a man-machine interaction device to display the target parameter trend graph, the elasticity parameter corresponding to the systolic start time, and the elasticity parameter corresponding to the systolic end time on a display interface, and respectively mark the systolic start time and the systolic end time corresponding to the elasticity parameter at corresponding positions on the target parameter trend graph.

[0028] The fifth aspect of the present application provides an ultrasonic imaging device, including:

[0029] A memory, configured to store a program;

[0030] A processor, configured to execute the program to implement the method as described above.

[0031] According to the ultrasonic imaging device and the display method of elastic parameters of the above embodiments, obtain the ultrasonic echo data of at least one cardiac cycle of the target blood vessel and the target parameter trend graph for reflecting the at least one cardiac cycle; obtain the pulse wave propagation velocity corresponding to the start time of the systolic phase within the at least one cardiac cycle and the pulse wave propagation velocity corresponding to the end time of the systolic phase within the at least one cardiac cycle according to the ultrasonic echo data; display the target parameter trend graph, the pulse wave propagation velocity corresponding to the start time of the systolic phase and the pulse wave propagation velocity corresponding to the end time of the systolic phase on the display interface, and respectively mark the start time of the systolic phase and the end time of the systolic phase corresponding to the above pulse wave propagation velocity at the corresponding positions of the target parameter trend graph. Since the change trend of the target parameter in the target parameter trend graph reflects the cardiac cycle, combined with the start time of the systolic phase and the end time of the systolic phase marked in the target parameter trend graph corresponding to the pulse wave propagation velocity, and the displayed corresponding pulse wave propagation velocity, the correlation between the pulse wave propagation velocities corresponding to the two times and the cardiac cycle can be very intuitively reflected. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] Figure 1 It is a diagram showing the changes in blood vessel diameter and blood pressure within a single cardiac cycle;

[0033] Figure 2 It is a schematic diagram of pulse wave propagation;

[0034] Figure 3 It is a spatio-temporal diagram displayed by an existing ultrasonic imaging device;

[0035] Figure 4 It is a structural block diagram of an embodiment of the ultrasonic imaging device provided by the present invention;

[0036] Figure 5 It is a flowchart of an embodiment of the display method of elastic parameters provided by the present invention;

[0037] Figure 6 It is a flowchart of an embodiment of the display method of elastic parameters provided by the present invention;

[0038] Figure 7 It is a target parameter trend graph of an embodiment in the ultrasonic imaging device provided by the present invention. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0039] The present invention will be further described in detail below in conjunction with the specific embodiments and the accompanying drawings. Similar elements in different embodiments are denoted by related similar element numbers. In the following embodiments, many detailed descriptions are provided to enable a better understanding of the present application. However, those skilled in the art can easily recognize that some of the features can be omitted in different situations, or can be replaced by other elements, materials, or methods. In some cases, some operations related to the present application are not shown or described in the specification, which is to avoid overwhelming the core part of the present application with excessive descriptions. For those skilled in the art, it is not necessary to describe these related operations in detail, and they can fully understand the related operations based on the descriptions in the specification and the general technical knowledge in the art.

[0040] In addition, the features, operations, or characteristics described in the specification can be combined in any appropriate manner to form various embodiments. At the same time, the steps or actions in the method description can also be reordered or adjusted in an obvious manner by those skilled in the art. Therefore, the various sequences in the specification and the drawings are only for clearly describing a certain embodiment and do not mean that they are the necessary sequences, unless it is stated that a certain sequence must be followed.

[0041] The serial numbers assigned to the components herein, such as "first", "second", etc., are only used to distinguish the described objects and do not have any sequential or technical meanings. The terms "connection" and "coupling" used in the present application, unless otherwise specified, both include direct and indirect connection (coupling).

[0042] The ultrasonic imaging device and the method for displaying elastic parameters provided by the present application can be applied to the human body or various animals.

[0043] In view of the deficiencies of the current pulse wave imaging display mode, the present application proposes a new elastic parameter display scheme. On the one hand, by using a target parameter trend graph that can reflect the cardiac cycle, the correlation between the elastic parameters and the cardiac cycle is enhanced; on the other hand, the vascular elasticity at the target moment can also be evaluated. This will be described in detail through some embodiments below.

[0044] As Figure 4 shown, the ultrasonic imaging device provided by the present invention includes an ultrasonic probe 30, a transmitting / receiving circuit 40 (i.e., a transmitting circuit 410 and a receiving circuit 420), a beam synthesis module 50, an IQ demodulation module 60, a processor 20, a human-machine interaction device 70, and a memory 80.

[0045] The ultrasonic probe 30 includes a transducer (not shown in the figure) composed of a plurality of arrayed array elements. The plurality of array elements are arranged in a row to form a linear array, or arranged in a two-dimensional matrix to form a planar array. The plurality of array elements can also form a convex array. The array elements are used to transmit ultrasonic waves according to the excitation electrical signal, or convert the received ultrasonic waves into electrical signals. Therefore, each array element can be used to realize the mutual conversion between the electrical pulse signal and the ultrasonic wave, so as to transmit ultrasonic waves to the object to be imaged (such as the arterial blood vessel in this embodiment), and can also be used to receive the echo of the ultrasonic wave reflected by the tissue. During ultrasonic detection, the transmitting circuit 410 and the receiving circuit 420 can be used to control which array elements are used to transmit ultrasonic waves, which array elements are used to receive ultrasonic waves, or control the array elements to be used for transmitting ultrasonic waves or receiving the echo of ultrasonic waves in time slots. The array elements participating in ultrasonic wave transmission can be simultaneously excited by electrical signals to transmit ultrasonic waves simultaneously; or the array elements participating in ultrasonic wave transmission can also be excited by several electrical signals with a certain time interval to continuously transmit ultrasonic waves with a certain time interval.

[0046] The array elements are made of piezoelectric crystals, for example, and convert the electrical signal into an ultrasonic signal according to the transmission sequence transmitted by the transmitting circuit 410. According to the use, the ultrasonic signal can include one or more scanning pulses, one or more reference pulses, one or more push pulses and / or one or more Doppler pulses. According to the waveform of the wave, the ultrasonic signal includes focused waves, plane waves, divergent waves, etc.

[0047] The user selects a suitable position and angle by moving the ultrasonic probe 30 to transmit ultrasonic waves to the object to be imaged 10 and receive the echo of the ultrasonic wave returned by the object to be imaged 10, and outputs an ultrasonic echo signal. The ultrasonic echo signal is a channel analog electrical signal formed by taking the receiving array element as the channel, and it carries amplitude information, frequency information and time information.

[0048] The transmitting circuit 410 is used to generate a transmission sequence according to the control of the processor 20. The transmission sequence is used to control some or all of the plurality of array elements to transmit ultrasonic waves to the object to be imaged. The transmission sequence parameters include the positions of the array elements for transmission, the number of array elements, and the ultrasonic beam transmission parameters (such as amplitude, frequency, number of transmissions, transmission interval, transmission angle, waveform, focusing position, etc.). In some cases, the transmitting circuit 410 is also used to perform phase delay on the transmitted beam, so that different transmitting array elements transmit ultrasonic waves at different times, so that the transmitted ultrasonic beams can be focused in a predetermined region of interest. For different working modes, such as B-image mode, C-image mode and D-image mode (Doppler mode), the transmission sequence parameters may be different. After the echo signal is received by the receiving circuit 420 and processed by subsequent modules and corresponding algorithms, a B image reflecting the tissue anatomical structure, a C image reflecting the blood flow information, and a D image reflecting the Doppler spectrum image can be generated.

[0049] The receiving circuit 420 is configured to receive ultrasonic echo signals from the ultrasonic probe 30 and process the ultrasonic echo signals. The receiving circuit 420 may include one or more amplifiers, an analog-to-digital converter (ADC), etc. The amplifier is used to amplify the received echo signals after appropriate gain compensation. The amplifier samples the analog echo signals at predetermined time intervals to convert them into digitized echo signals. The digitized echo signals still retain amplitude information, frequency information, and phase information. The data output by the receiving circuit 420 can be output to the beamforming module 50 for processing or output to the memory 80 for storage.

[0050] The beamforming module 50 is connected to the receiving circuit 420 for performing beamforming processing such as corresponding delay and weighted summation on the echo signals. Since the distances from the ultrasonic receiving points in the tissue under test to the receiving array elements are different, the channel data of the same receiving point output by different receiving array elements have delay differences. Therefore, delay processing is required to align the phases and perform weighted summation on the different channel data of the same receiving point to obtain the ultrasonic image data after beamforming. The ultrasonic image data output by the beamforming module 50 is also called radio frequency data (RF data). The beamforming module 50 outputs the RF data to the IQ demodulation module 60. In some embodiments, the beamforming module 50 may also output the RF data to the memory 80 for caching or storage, or directly output the RF data to the processor 20 for image processing.

[0051] The beamforming module 50 can perform the above functions in a hardware, firmware, or software manner. For example, the beamforming module 50 may include a central controller circuit (CPU) capable of processing input data according to specific logic instructions, one or more microprocessing chips, or any other electronic component. When the beamforming module 50 is implemented in software, it can execute instructions stored on a tangible and non-transitory computer-readable medium (e.g., a memory) to perform beamforming calculations using any appropriate beamforming method. The beamforming module 50 can be integrated in the processor 20 or set separately, which is not limited in the present invention.

[0052] The IQ demodulation module 60 removes the signal carrier through IQ demodulation, extracts the tissue structure information contained in the signal, and filters out the noise. The signal obtained at this time is called the baseband signal (IQ data pair). The IQ demodulation module 60 outputs the IQ data pair to the processor 20 for image processing.

[0053] In some embodiments, the IQ demodulation module 60 also outputs the IQ data pair to the memory 80 for caching or storage so that the processor 20 can read the data from the memory 80 for subsequent image processing.

[0054] The IQ demodulation module 60 can also perform the above functions in the form of hardware, firmware, or software. In some embodiments, the IQ demodulation module 60 can also be integrated with the beamforming module 50 on a single chip.

[0055] The processor 20 is configured to be a central controller circuit (CPU), one or more microprocessors, a graphics controller circuit (GPU), or any other electronic component capable of processing input data according to specific logical instructions. It can control peripheral electronic components according to input instructions or predetermined instructions, or perform data reading and / or storage on the memory 80. It can also process input data by executing programs in the memory 80. For example, it can perform one or more processing operations on the acquired ultrasound data according to one or more working modes. The processing operations include, but are not limited to, adjusting or defining the form of ultrasonic waves emitted by the ultrasound probe 30, generating various image frames for subsequent display on the display of the human-machine interaction device 70, or adjusting or defining the content and form displayed on the display, or adjusting one or more image display settings (such as ultrasound images, interface components, positioning of regions of interest) displayed on the display.

[0056] When the echo signal is received, the acquired ultrasound data can be processed by the processor 20 in real time during scanning, or temporarily stored on the memory 80 and processed in a quasi-real-time manner in online or offline operations.

[0057] In this embodiment, the processor 20 controls the operation of the transmitting circuit 410 and the receiving circuit 420. For example, it controls the transmitting circuit 410 and the receiving circuit 420 to work alternately or simultaneously. The processor 20 can also determine a suitable working mode according to the user's selection or program settings, form a transmission sequence corresponding to the current working mode, and send the transmission sequence to the transmitting circuit 410 so that the transmitting circuit 410 can control the ultrasound probe 30 to emit ultrasonic waves using the appropriate transmission sequence.

[0058] The processor 20 is also used to process the ultrasound echo signal to generate a grayscale image of the signal strength change within the scanning range. This grayscale image reflects the anatomical structure inside the tissue and is called a B-image. The processor 20 can output the B-image to the display of the human-machine interaction device 70 for display.

[0059] The human-machine interaction device 70 is used for human-machine interaction, that is, receiving user input and outputting visual information. The user input it receives can be through a keyboard, operation buttons, mouse, trackball, touchpad, etc., or can also be through a touch screen integrated with the display. The visual information it outputs can be through a display.

[0060] Based on Figure 4 The ultrasound imaging device shown, the display method of its elastic parameters is as Figure 5As shown, it includes the following steps:

[0061] Step 1: Obtain ultrasonic echo data of at least one cardiac cycle of the target blood vessel. For example, the processor 20 controls the transmitting circuit 410 to excite the ultrasonic probe 30 to transmit ultrasonic waves to the target blood vessel 10. The ultrasonic probe 30 transmits ultrasonic waves to the detected blood vessel 10. The receiving circuit 420 controls the ultrasonic probe 30 to receive the echoes of the ultrasonic waves returned from the detected blood vessel to obtain echo signals. The echo signals are obtained from the ultrasonic probe 30 through the receiving circuit 420 and are processed (such as analog-to-digital conversion, beam synthesis, etc.) to obtain ultrasonic echo data including at least one cardiac cycle. Of course, in an optional embodiment, the processor 20 can also directly obtain the ultrasonic echo data from the memory 80, which will not be elaborated here. In this embodiment, the ultrasonic echo data is the data after beam synthesis of the ultrasonic echoes obtained with the blood vessels of the target object as the detection object.

[0062] Step 2: Generate a target parameter trend graph for reflecting at least one cardiac cycle according to the ultrasonic echo data, or obtain a target parameter trend graph for reflecting at least one cardiac cycle from an external device. The processor 20 can generate a target parameter trend graph for reflecting the cardiac cycle according to the ultrasonic echo data. The target parameter can be a pulsation parameter reflecting the pulsation of the blood vessel wall of the blood vessel (for example, in the radial direction), or the blood flow velocity in the blood vessel, or the blood pressure. These parameters can all be obtained through the ultrasonic echo data, and these parameters are all related to the cardiac pulsation, and their values change periodically with time, and the change period is the cardiac cycle. The ultrasonic imaging device can also include a communication interface (not shown in the figure) for communicating with an external device. The processor 20 can also directly obtain a target parameter trend graph for reflecting the cardiac cycle from the external device through the communication interface. The target parameter trend graph obtained from the external device can be the blood pressure or the trend graph of electrocardiogram parameters (electrocardiogram signals). The trend graphs of these parameters can all be obtained through conventional medical devices (such as monitors, blood pressure measuring instruments, etc.) or even wearable devices, and these parameters are all related to the cardiac pulsation, and their values change periodically with time, and the change period is the cardiac cycle.

[0063] Step 3: Obtain the elastic parameter corresponding to the start moment of the systolic period (which can also be called the early systolic period BS) within at least one cardiac cycle and the elastic parameter corresponding to the end moment of the systolic period (which can also be called the late systolic period ES) within at least one cardiac cycle according to the ultrasonic echo data. For example, the processor 20 can obtain the elastic parameter corresponding to the start moment of the systolic period within the at least one cardiac cycle and the elastic parameter corresponding to the end moment of the systolic period within the at least one cardiac cycle according to the ultrasonic echo data. The elastic parameter is a parameter reflecting the elasticity of the blood vessel, such as the pulse wave propagation velocity, Young's modulus or compliance.

[0064] Step 4: Display the target parameter trend graph, the elastic parameter corresponding to the start moment of the systolic phase, and the elastic parameter corresponding to the end moment of the systolic phase on the display interface, and mark the start moment of the systolic phase and the end moment of the systolic phase corresponding to the elastic parameter at the corresponding positions on the target parameter trend graph. 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 start moment of the systolic phase, and the elastic parameter corresponding to the end moment of the systolic phase on the display interface, and marks the start moment of the systolic phase and the end moment of the systolic phase corresponding to the elastic parameter at the corresponding positions on the target parameter trend graph. Since the change trend of the target parameter in the target parameter trend graph reflects the cardiac cycle, combining the start moment of the systolic phase and the end moment of the systolic phase marked on the target parameter trend graph corresponding to the elastic parameter, and the displayed corresponding elastic parameter, the correlation between the elastic parameters corresponding to the two moments and the cardiac cycle can be very intuitively reflected.

[0065] The above step 1 can obtain the ultrasonic echo data of the target blood vessel in a certain time period. The certain time period can be greater than or equal to one cardiac cycle, which can be set by the system default or freely adjusted by the user. When obtaining the ultrasonic echo data in a certain time period, it can continuously obtain the ultrasonic echo data of at least one cardiac cycle with one cardiac cycle as a unit, or can obtain the ultrasonic echo data of multiple cardiac cycles in segments. For example, in the case of real-time acquisition, the ultrasonic imaging device obtains the ultrasonic echo data in real time according to the echo signal obtained by the ultrasonic probe, and the real-time acquisition time is one or more cardiac cycles.

[0066] Of course, the present invention is not satisfied with this. A more detailed embodiment is provided below. The elastic parameter can be the pulse wave propagation velocity, Young's modulus or compliance. The following takes the elastic parameter as the pulse wave propagation velocity as an example for illustration. As Figure 6 shown, the display method of the pulse wave propagation velocity includes the following steps:

[0067] Step 1': Obtain the ultrasonic echo data of at least one cardiac cycle of the target blood vessel. For example, obtain the echo signal from the ultrasonic probe 30 through the receiving circuit 420, and after a certain processing, obtain the ultrasonic echo data including at least one cardiac cycle. The processor 20 obtains the ultrasonic echo data of at least one cardiac cycle of the target blood vessel. Another example is that the processor 20 obtains the ultrasonic echo data from the memory. See the specific steps of the above embodiment for details, and will not be elaborated here.

[0068] Step 2': Generate a target parameter trend graph for reflecting at least one cardiac cycle based on the ultrasonic echo data, or obtain a target parameter trend graph for reflecting at least one cardiac cycle from an external device. In this embodiment, taking the target parameter as a pulsation parameter reflecting the pulsation of the blood vessel wall (for example, in the radial direction) as an example for illustration. Under the action of cardiac pulsation, the blood vessel wall mainly pulsates along the radial direction of the blood vessel. The processor 20 obtains the pulsation parameters at each moment within the at least one cardiac cycle based on the ultrasonic echo data, and then generates a pulsation parameter trend graph. For example, the processor 20 obtains the displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel based on the ultrasonic echo data, and generates a target parameter trend graph based on the displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel.

[0069] Specifically, the processor 20 detects the positions of the blood vessel walls (the upper blood vessel wall and the lower blood vessel wall) in different frames within at least one cardiac cycle according to the ultrasonic echo data; calculates the radial displacements of each detection point arranged along the axial direction of the blood vessel on the blood vessel wall at different time points according to the positions of the blood vessel walls in different frames; and obtains the pulsation parameters of each detection point at different time points according to the radial displacements of each detection point on the blood vessel wall. The pulsation parameters can be the blood vessel diameter, the change speed of the blood vessel diameter, the change acceleration of the blood vessel diameter, the displacement of a single-sided blood vessel wall, the radial movement speed of a single-sided blood vessel wall, or the radial movement acceleration of a single-sided blood vessel wall, etc. Subtracting the radial displacement of the detection point on the upper blood vessel wall from the corresponding radial displacement of the detection point on the lower blood vessel wall, the change amount of the blood vessel diameter at this detection point can be obtained. By respectively taking the first-order and second-order derivatives of the radial displacement and the change amount of the blood vessel diameter in the time dimension, the radial speed, the radial acceleration, the change speed and the change acceleration of the blood vessel diameter, etc. can be obtained. That is, each parameter in the pulsation parameters can be obtained from the blood vessel diameter at different times, so this embodiment takes the blood vessel diameter as an example for illustration. Since the target parameter trend graph mainly reflects each phase of the cardiac cycle, a target parameter trend graph can be generated according to the blood vessel diameter corresponding to one of the detection points (taking the target parameter as the blood vessel diameter as an example, it is a blood vessel diameter change trend graph, as Figure 7 shown).

[0070] As described in the previous embodiment, in some embodiments, the processor 20 can also obtain a target parameter trend graph for reflecting the at least one cardiac cycle from an external device. The target parameter obtained from the external device only needs to be the same as the above ultrasonic echo data in time. The target parameter trend graph and the ultrasonic echo data can be collected in the same time period, which is convenient for subsequent correspondence of the two in time. The target parameter trend graph obtained from the external device can be a blood pressure trend graph, an electrocardiogram, etc.

[0071] Step 3': Obtain the pulse wave propagation velocity corresponding to the start moment of the systolic phase within at least one cardiac cycle and the pulse wave propagation velocity corresponding to the end moment of the systolic phase within at least one cardiac cycle based on the ultrasonic echo data. Specifically, through the method in Step 2', the pulsation parameters of each detection point (at least two points) on the blood vessel wall at different time points can be obtained, and the processor 20 obtains the propagation velocity of the pulse wave along the axial direction on the blood vessel wall according to the pulsation parameters of each detection point. For example, the processor 20 detects the first time when the pulsation parameters of each detection point reach the first predetermined threshold. The first predetermined threshold can be set according to user requirements. For example, for the pulse wave in the early systolic phase, the pulsation parameter can be selected as the radial displacement, and the first predetermined threshold can be the minimum value in the empirical values of the maximum radial displacement (corresponding to the wave peak), or 50% or more of the empirical value of the maximum radial displacement, etc. For the pulse wave in the late systolic phase, detect the first time when the pulsation parameters of each detection point are within the first predetermined threshold range and are the maximum value. By setting the maximum value of the first predetermined threshold range, the wave peak in the early systolic phase can be excluded, and by setting the minimum value of the first predetermined threshold range, the maximum value in the late systolic phase (the lower wave peak in the cardiac cycle) can be covered. Through the judgment of the maximum value (conventional mathematical method), the first time when the wave peak of the pulse wave reflecting the late systolic phase arrives can be obtained. This embodiment is described by taking the pulse wave in the early systolic phase as an example. The processor 20 obtains the propagation velocity of the pulse wave on the blood vessel wall in the ultrasonic image according to the positions of each detection point on the blood vessel axis and the first time corresponding to each detection point. Obtain the propagation velocity of the pulse wave at each detection point according to the positions of two adjacent detection points on the blood vessel axis and the difference in the first time corresponding to the two adjacent detection points. To improve the accuracy, multiple detection points are selected, and the more the better within the processing capacity range, to obtain the corresponding relationship between time and space of each detection point, and perform linear fitting on each point to obtain an oblique line, and the slope of this oblique line is the average propagation velocity of the pulse wave in the current cardiac cycle.

[0072] Since the positions of each detection point and the corresponding first time are both known, the pulse wave propagation velocity at the start (BS) and end (ES) of the systolic phase of the anterior arterial wall, the propagation velocity of any detection point on the blood vessel wall, the average propagation velocity of any segment, etc. can all be calculated by the above method. The pulse wave propagation velocity in this embodiment can be the pulse wave propagation velocity corresponding to the detection point or the average pulse wave propagation velocity of the entire blood vessel, as long as it can reflect the blood vessel elasticity.

[0073] The processor 20 can also generate corresponding ultrasonic images based on the ultrasonic echo data. For example, B imaging (two-dimensional or three-dimensional tissue gray-scale imaging) can be performed on the blood vessels of the target object, and M imaging and Doppler imaging can also be performed on the blood vessels of the target object. Doppler imaging can include, for example, tissue Doppler imaging (TDI) and tissue velocity imaging (TVI).

[0074] Step 4': Display the target parameter trend graph, the pulse wave propagation velocity corresponding to the start moment of the systolic phase, and the pulse wave propagation velocity corresponding to the end moment of the systolic phase on the display interface, and mark the start moment of the systolic phase and the end moment of the systolic phase corresponding to the pulse wave propagation velocity at the corresponding positions on the target parameter trend graph. Among them, the trend graph includes one of a curve graph, a line graph, a scatter graph, a histogram, a bar graph, and a box plot, as long as it can reflect the change trend of the target parameter over time. This embodiment will be described by taking the curve graph as an example. As Figure 7 shown, in the blood vessel diameter trend graph, it includes the change curve a of the diameter over time, the X-axis is time, and the Y-axis is the diameter. The eight phases of the cardiac cycle (not shown in the figure) can also be marked on the target parameter trend graph to facilitate the doctor to better grasp the change trend of the target parameter. The start moment of the systolic phase and the end moment of the systolic phase can be marked on the coordinate axis, or as Figure 7 shown, marked on the change curve a. The markings of the start moment of the systolic phase and the end moment of the systolic phase can be the same, or as Figure 7 shown as different. The specific marking method is not limited, as long as these two moments can be marked. Of course, it is better to highlight these two moments. The pulse wave propagation velocities corresponding to the start moment of the systolic phase and the end moment of the systolic phase can be displayed outside the target parameter trend graph and displayed on the same display interface as the target parameter trend graph; or as Figure 7 shown, display the pulse wave propagation velocity PWV corresponding to the start moment of the systolic phase at the adjacent position of the marked start moment of the systolic phase BS , mark the end moment of the systolic phase on the target parameter trend graph, and display the pulse wave propagation velocity PWV corresponding to the end moment of the systolic phase at the adjacent position of the marked end moment of the systolic phase ES . It can be seen that compared with the current spatio-temporal graph ( Figure 3 ), the diameter change curve a better shows each phase within a cardiac cycle. Marking the pulse wave propagation velocity on the curve can intuitively display the correlation between the pulse wave and the corresponding phase of the cardiac cycle.

[0075] The processor 20 can also display, through the human-computer interaction device 70, an ultrasonic image obtained based on the ultrasonic echo data on the display interface, so that the doctor can understand the state of the blood vessels through the ultrasonic image while viewing the target parameter trend graph.

[0076] It should be noted that within one cardiac cycle, the blood vessel diameter, blood pressure, and blood vessel elasticity all change dynamically, and the change trends are similar, that is, during systole, the blood pressure increases, the blood vessel diameter increases, and the blood vessel elasticity increases; during diastole, the blood pressure decreases, the blood vessel diameter decreases, and the blood vessel elasticity decreases. The pulse wave occurs only twice within one cardiac cycle and can only reflect the blood vessel elasticity at the occurrence moment. By combining blood pressure and pulse wave, or blood vessel diameter and pulse wave, the blood vessel elasticity at any moment within one cardiac cycle can be estimated. In this embodiment, the blood vessel diameter and pulse wave are taken as examples for illustration. The target parameter D at any moment within at least one of the above cardiac cycles can be obtained t , the target parameter D at the start moment of systole BS , and the target parameter D at the end moment of systole ES . Furthermore, the processor 20 calculates the pulse wave velocity PWV corresponding to any moment within at least one of the above cardiac cycles based on the target parameter D at any moment t , the target parameter D at the start moment of systole BS , the pulse wave velocity PWV corresponding to the start moment of systole BS , the target parameter D at the end moment of systole ES , and the pulse wave velocity PWV corresponding to the end moment of systole ES , and displays the pulse wave velocity PWV corresponding to any moment on the display interface of the human-computer interaction device 70 t . It can be seen that this application can also estimate the blood vessel elasticity at any moment within the cardiac cycle, which is beneficial for doctors to evaluate the elasticity of blood vessels at various locations. It should be noted that the target parameter D at any moment within at least one of the above cardiac cycles t can be selected by the user based on the target parameter trend graph, or the user can input the corresponding moment, and the processor 20 outputs the target parameter D at any moment based on the ultrasonic echo data t , or it can be a characteristic moment automatically determined by the system (such as the peak moment or valley moment of the target parameter within the cardiac cycle, etc.). t

[0077] Similarly, the pulse wave velocity PWV corresponding to any moment t can also be displayed on the target parameter trend graph, that is, mark any moment on the target parameter trend graph, and display the pulse wave velocity PWV corresponding to any moment at the adjacent position of the marked moment t . It is convenient for doctors to view.

[0078] ​Any of these moments includes at least one of: the moment determined according to the user's operation, the moment corresponding to the maximum value of the target parameter within the cardiac cycle, and the moment corresponding to the minimum value of the target parameter within the cardiac cycle. In this embodiment, any of these moments includes: the moment corresponding to the maximum value of the target parameter within the cardiac cycle and the moment corresponding to the minimum value of the target parameter within the cardiac cycle. Among them, the moment corresponding to the maximum value of the target parameter within the cardiac cycle and the moment corresponding to the minimum value of the target parameter within the cardiac cycle can be obtained through the trend curve in the target parameter trend graph. Of course, it can also be determined by the 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 it as the maximum value of the target parameter, and receives another point selected by the user on the trend curve and takes it as the minimum value of the target parameter. It can be seen that through the target parameter trend graph, the doctor can not only see the positions of the BS and ES moments in the cardiac cycle and the corresponding pulse wave propagation velocity, but also see the moments corresponding to the extreme values of the target parameter and the pulse wave propagation velocity, providing sufficient information for the doctor to evaluate vascular elasticity and the associated time.

[0079] In this embodiment, the pulse wave propagation velocity PWV at the target moment is calculated by the following formula t :

[0080]

[0081] D t is the target parameter at any moment, D BS is the target parameter at the start moment of systole, PWV BS is the pulse wave propagation velocity corresponding to the start moment of systole, D ES is the target parameter at the end moment of systole, PWV ES is the pulse wave propagation velocity corresponding to the end moment of systole.

[0082] For these two moments: the moment corresponding to the maximum value of the target parameter within the cardiac cycle and the moment corresponding to the minimum value of the target parameter within the cardiac cycle, referring to the above formula 1, the corresponding pulse wave propagation velocities PWV MAX 、PWV MIN are calculated by the following formula:

[0083]

[0084]

[0085] PWV MAX is the pulse wave propagation velocity corresponding to the moment corresponding to the maximum value of the target parameter within the cardiac cycle, D MAX is the maximum value of the target parameter within the cardiac cycle. PWV MIN is the pulse wave propagation velocity corresponding to the moment corresponding to the minimum value of the target parameter within the cardiac cycle, DMIN is the minimum value of the target parameter within the cardiac cycle.

[0086] The points on the trend curve in the target parameter trend graph are optional. If the user wants to know the pulse wave velocity at a certain moment, they can simply click on the point in the target parameter trend graph displayed on the display interface through the human-machine interaction device. The processor 20 receives the user's selection instruction through the human-machine interaction device, and can obtain any selected moment from the point corresponding to this instruction. According to the selected moment and the trend curve, the corresponding target parameter at the selected moment can be obtained, and thus the pulse wave velocity PWV corresponding to the selected moment can be obtained according to Formula 1. t , and is displayed in the target parameter trend graph. It can be seen that the above method can evaluate the vascular elasticity at any moment during the entire cardiac cycle, facilitating doctors to master the vascular elasticity information.

[0087] It should be noted that the target parameter trend graph can be obtained based on ultrasonic echo data, such as the blood vessel diameter change trend graph, the blood flow velocity change trend graph, etc.; the target parameter trend graph can also be directly obtained from external devices, such as the blood pressure change trend graph, the ECG change trend graph, etc. The relevant descriptions are the same as those in the foregoing embodiments and will not be elaborated here.

[0088] Since the Young's modulus and compliance can be calculated from the pulse wave velocity and the change in diameter, or from the pulse wave velocity and the change in blood pressure, in the embodiments where the elastic parameter is the Young's modulus or compliance, only one step of calculating the Young's modulus or compliance based on the pulse wave velocity and the change in diameter, or the pulse wave velocity and the change in blood pressure, needs to be added. In other words, the pulse wave velocity in the above embodiments can be replaced with the Young's modulus or compliance, and the other content remains unchanged. The same as the above embodiments, it will not be elaborated here.

[0089] Those skilled in the art can understand that all or part of the functions of the above-mentioned implementation manners can be implemented by means of hardware or by means of computer programs. When all or part of the functions in the above-mentioned implementation manners are implemented by means of computer programs, the program can be stored in a computer-readable storage medium. The storage medium may include: read-only memory, random access memory, magnetic disks, optical disks, hard disks, etc. The above functions can be realized by a computer executing this program. For example, the program is stored in the memory of the device. When the program in the memory is executed by the processor, all or part of the above functions can be realized. In addition, when all or part of the functions in the above-mentioned implementation manners are implemented by means of computer programs, the program can also be stored in storage media such as servers, other computers, magnetic disks, optical disks, flash drives or external hard drives, and saved to the memory of the local device by downloading or copying, or the system of the local device is updated. When the program in the memory is executed by the processor, all or part of the functions in the above-mentioned implementation manners can be realized.

[0090] This document has been described with reference to various exemplary embodiments. However, those skilled in the art will recognize that changes and modifications can be made to the exemplary embodiments without departing from the scope hereof. For example, the various operation steps and the components for performing the operation steps can be implemented in different ways according to a particular application or any number of cost functions associated with the operation of the system (e.g., one or more steps can be deleted, modified, or incorporated into other steps).

[0091] In addition, as will be understood by those skilled in the art, the principles herein can be embodied in a computer program product on a computer-readable storage medium that pre-loads computer-readable program code. Any tangible, non-transitory computer-readable storage medium can be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-ROM, DVD, Blu-ray discs, etc.), flash memory, and / or the like. These computer program instructions can be loaded onto a general-purpose computer, special-purpose computer, or other programmable data processing device to form a machine, such that the instructions executed on the computer or other programmable data processing device can generate a device for realizing the specified functions. These computer program instructions can also be stored in a computer-readable memory, which can direct the computer or other programmable data processing device to operate in a specific manner, so that the instructions stored in the computer-readable memory can form a manufactured article, including a device for realizing the specified functions. The computer program instructions can also be loaded onto a computer or other programmable data processing device, thereby performing a series of operation steps on the computer or other programmable device to generate a computer-implemented process, such that the instructions executed on the computer or other programmable device can provide steps for realizing the specified functions.

[0092] Although the principles of the present disclosure have been shown in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components that are particularly adapted to specific environments and operational requirements may be used without departing from the principles and scope of the present disclosure. The above modifications and other changes or alterations will be included within the scope of the present disclosure.

[0093] The foregoing detailed description has been presented with reference to various embodiments. However, those skilled in the art will recognize that various modifications and changes can be made without departing from the scope of the present disclosure. Accordingly, the present disclosure is to be considered in an illustrative rather than a restrictive sense, and all such modifications will be included within its scope. Similarly, advantages, other advantages, and solutions to problems of the various embodiments have been described above. However, benefits, advantages, solutions to problems, and any elements that produce these, or cause them to become more apparent, should not be construed as critical, required, or essential. As used herein, the term "comprising" and any other variants thereof are non-exclusive inclusions, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but also other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Additionally, the term "coupled" and any other variants thereof as used herein refer to physical connection, electrical connection, magnetic connection, optical connection, communication connection, functional connection, and / or any other connection.

[0094] 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 basic principles of the present invention. Accordingly, the scope of the present invention should be determined in accordance with the following claims.

Claims

1. A method for displaying elastic parameters, characterized in that, Including: Obtaining ultrasonic echo data of at least one cardiac cycle of a target blood vessel; Generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtaining a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; Obtaining the pulse wave propagation velocity corresponding to the start moment of the systolic phase and the pulse wave propagation velocity corresponding to the end moment of the systolic phase within the at least one cardiac cycle according to the ultrasonic echo data; Displaying the target parameter trend graph on a display interface, marking the start moment of the systolic phase on the target parameter trend graph, and displaying the pulse wave propagation velocity corresponding to the start moment of the systolic phase at an adjacent position of the mark, marking the end moment of the systolic phase on the target parameter trend graph, and displaying the pulse wave propagation velocity corresponding to the end moment of the systolic phase at an adjacent position of the mark.

2. The method according to claim 1, wherein The generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data includes: Obtaining displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel according to the ultrasonic echo data, and generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel.

3. The method according to claim 1, characterized in that Further including: Determine the target parameter D at any moment within the at least one cardiac cycle t , the target parameter D at the start moment of the systolic phase BS , and the target parameter D at the end moment of the systolic phase ES ; Based on the target parameter D at any of the said moments t , the target parameter D at the start moment of systole BS , the pulse wave velocity PWV corresponding to the start moment of systole BS , the target parameter D at the end moment of systole ES and the pulse wave velocity PWV corresponding to the end moment of systole ES , determine the pulse wave velocity PWV corresponding to any of the said moments t , and display the pulse wave velocity PWV corresponding to any of the said moments t .

4. The method according to claim 3, wherein Any moment includes at least one of a moment determined according to a user operation, a moment corresponding to the maximum value of the target parameter within the at least one cardiac cycle, and a moment corresponding to the minimum value of the target parameter within the at least one cardiac cycle.

5. The method according to claim 3, wherein The target parameter D at any of the said moments t , the target parameter D at the starting moment of systole BS , the pulse wave velocity PWV corresponding to the starting moment of systole BS , the target parameter D at the ending moment of systole ES and the pulse wave velocity PWV corresponding to the ending moment of systole ES , to determine the pulse wave velocity PWV corresponding to any of the said moments t , including: The pulse wave velocity PWV corresponding to any moment is calculated according to the following formula t :[[]]END]] 6. The method according to claim 3, wherein displaying the pulse wave velocity PWV corresponding to any moment t , comprising: Mark the any moment on the target parameter trend graph, and display the pulse wave velocity (PWV) corresponding to the any moment at an adjacent position of marking the any moment t .

7. The method according to any one of claims 1 to 6, characterized in that, The trend graph includes: a curve graph, a line graph, a scatter graph, a histogram, a bar graph or a box plot.

8. The method according to any one of claims 1 to 6, characterized in that, The target parameter includes: a pulsation parameter reflecting the pulsation of the blood vessel wall of the blood vessel, the velocity of blood flow in the blood vessel, blood pressure or electrocardiogram parameters.

9. The method according to claim 8, characterized in that, The pulsation parameter includes: blood vessel diameter, the change velocity of blood vessel diameter, the change acceleration of blood vessel diameter, the displacement of a unilateral blood vessel wall, the radial movement velocity of a unilateral blood vessel wall or the radial movement acceleration of a unilateral blood vessel wall.

10. A method for displaying elastic parameters, characterized in that, Including: Obtaining ultrasonic echo data of at least one cardiac cycle of a target blood vessel; Generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtaining a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; Obtaining an elastic parameter corresponding to the start moment of the systolic phase and an elastic parameter corresponding to the end moment of the systolic phase within the at least one cardiac cycle according to the ultrasonic echo data; Displaying the target parameter trend graph on a display interface, marking the start moment of the systolic phase on the target parameter trend graph, and displaying the elastic parameter corresponding to the start moment of the systolic phase at an adjacent position of the mark, marking the end moment of the systolic phase on the target parameter trend graph, and displaying the elastic parameter corresponding to the end moment of the systolic phase at an adjacent position of the mark.

11. The method according to claim 10, characterized in that, The elastic parameter includes: Young's modulus or compliance.

12. An ultrasonic imaging device, characterized in that, Including: An ultrasonic probe; A transmitting circuit for exciting the ultrasonic probe to emit ultrasonic waves towards the target blood vessel; A receiving circuit for controlling the ultrasonic probe to receive the echo of the returned ultrasonic waves and obtaining an echo signal; A human-computer interaction device for visual output and obtaining user input; A processor for obtaining ultrasonic echo data of at least one cardiac cycle of a target blood vessel; Generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtaining a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; Obtaining the pulse wave propagation velocity corresponding to the start moment of the systolic period and the pulse wave propagation velocity corresponding to the end moment of the systolic period within the at least one cardiac cycle according to the ultrasonic echo data; controlling the human-computer interaction device to display the target parameter trend graph on a display interface, marking the start moment of the systolic period on the target parameter trend graph, and displaying the pulse wave propagation velocity corresponding to the start moment of the systolic period at an adjacent position of the mark, marking the end moment of the systolic period on the target parameter trend graph, and displaying the pulse wave propagation velocity corresponding to the end moment of the systolic period at an adjacent position of the mark.

13. The ultrasonic imaging device according to claim 12, wherein The processor generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data includes: Obtaining displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel according to the ultrasonic echo data, and generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the displacement information of the upper blood vessel wall and / or the lower blood vessel wall of the blood vessel.

14. The ultrasonic imaging device according to claim 12, characterized in that, The processor is further configured to: Obtain the target parameter D at any moment within the at least one cardiac cycle t , the target parameter D at the start moment of the systolic phase BS , and the target parameter D at the end moment of the systolic phase ES ; Based on the target parameter D at any of the said moments t , the target parameter D at the start moment of systole BS , the pulse wave velocity PWV corresponding to the start moment of systole BS , the target parameter D at the end moment of systole ES and the pulse wave velocity PWV corresponding to the end moment of systole ES , determine the pulse wave velocity PWV corresponding to any of the said moments t , control the human-computer interaction device to display the pulse wave velocity PWV corresponding to any of the said moments on the display interface t .

15. The ultrasonic imaging device according to claim 14, characterized in that, The any moment includes at least one of a moment determined according to a user operation, a moment corresponding to the maximum value of the target parameter within the at least one cardiac cycle, and a moment corresponding to the minimum value of the target parameter within the at least one cardiac cycle.

16. The ultrasonic imaging device according to claim 14, characterized in that, The processor determines the target parameter D at any moment t , the target parameter D at the start moment of systole BS , the pulse wave velocity PWV corresponding to the start moment of systole BS , the target parameter D at the end moment of systole ES and the pulse wave velocity PWV corresponding to the end moment of systole ES , and determines the pulse wave velocity PWV corresponding to any moment t , including: The pulse wave velocity PWV at any moment is calculated according to the following formula t :[[]]END]] 17. The ultrasonic imaging device according to claim 14, characterized in that, The processor controls the human-computer interaction device to display the pulse wave velocity PWV corresponding to the target moment on the display interface t , including: Mark the arbitrary moment on the target parameter trend chart, and display the pulse wave velocity (PWV) corresponding to the arbitrary moment at an adjacent position to the marked arbitrary moment t .

18. The ultrasonic imaging device according to any one of claims 12 to 17, characterized in that, The trend graph includes: a line graph, a broken line graph, a scatter plot, a histogram, a bar graph or a box plot.

19. The ultrasonic imaging device according to any one of claims 12 to 17, characterized in that, The target parameter includes: a pulsation parameter reflecting the pulsation of the blood vessel wall of the blood vessel, the velocity of blood flow in the blood vessel, blood pressure or an electrocardiogram parameter.

20. The ultrasonic imaging device according to claim 19, wherein, The pulsation parameter includes: the blood vessel diameter, the change velocity of the blood vessel diameter, the change acceleration of the blood vessel diameter, the displacement of a unilateral blood vessel wall, the radial movement velocity of a unilateral blood vessel wall or the radial movement acceleration of a unilateral blood vessel wall.

21. An ultrasonic imaging device, characterized in that, Comprising: An ultrasonic probe; A transmitting circuit for exciting the ultrasonic probe to transmit ultrasonic waves to a target blood vessel; A receiving circuit for controlling the ultrasonic probe to receive the echo of the returned ultrasonic waves and obtaining an echo signal; A human-computer interaction device for visual output and obtaining user input; A processor for obtaining ultrasonic echo data of at least one cardiac cycle of a target blood vessel; Generating a target parameter trend graph for reflecting the at least one cardiac cycle according to the ultrasonic echo data, or obtaining a target parameter trend graph for reflecting the at least one cardiac cycle from an external device; Obtain the elastic parameter corresponding to the start time of systole within the at least one cardiac cycle and the elastic parameter corresponding to the end time of systole within the at least one cardiac cycle according to the ultrasonic echo data; control the human-computer interaction device to display the target parameter trend graph on the display interface, mark the start time of systole on the target parameter trend graph, and display the elastic parameter corresponding to the start time of systole at an adjacent position to the mark, mark the end time of systole on the target parameter trend graph, and display the elastic parameter corresponding to the end time of systole at an adjacent position to the mark.

22. The ultrasonic imaging device according to claim 21, characterized in that, The elastic parameter includes: Young's modulus or compliance.

23. An ultrasonic imaging device, characterized in that, Comprising: A memory for storing programs; A processor for executing the program to implement the method according to any one of claims 1-11.

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