Ultrasonic equipment and heart evaluation device

Abstract

The invention discloses ultrasonic equipment and a heart evaluation device, and is applied to the technical field of ultrasound. A transmitting and receiving control circuit; the processor is used for performing a strain imaging mode on a first cardiac muscle tissue of the target heart so as to obtain at least one strain elastic parameter of the first cardiac muscle tissue in a cardiac cycle; performing a shear wave imaging mode on a second cardiac muscle tissue of the target heart to obtain a shear wave elastic parameter of the second cardiac muscle tissue; and obtaining a heart performance quantitative evaluation result according to the at least one strain elastic parameter and the shear wave elastic parameter, wherein the heart performance quantitative evaluation result is used for representing the contraction performance and / or diastolic performance of the target heart. Quantitative evaluation is comprehensively performed from the deformation dimension and the elastic dimension of the myocardial tissue, so that the contraction performance and the relaxation performance of the heart are comprehensively and intuitively evaluated.

Description

Technical Field

[0001] This application relates to the field of ultrasonic technology, specifically to an ultrasonic device. Background Technology

[0002] As one of the most vital organs in the human body, monitoring the heart's systolic and diastolic functions has significant clinical value. The gold standard for assessing cardiac systolic and diastolic function is typically measured via cardiac catheterization, which involves measuring the pressure-volume loop within the heart chambers. However, this invasive procedure carries considerable difficulty and risk. Ultrasound, as a non-invasive, safe, and convenient examination method, can be used to assess cardiac systolic and diastolic function.

[0003] Current technologies utilize ultrasound equipment equipped with cardiac strain imaging based on two- or three-dimensional speckle tracking technology. Specifically, this strain imaging function can acquire the heart's strain elastic parameters and be used to assess the heart's systolic and diastolic functions. However, there are still some shortcomings in assessing cardiac systolic and diastolic functions based on strain elastic parameters, resulting in inaccurate assessments. Therefore, new technical solutions are needed. Summary of the Invention

[0004] The main technical problem this application addresses is the inaccurate assessment of cardiac systolic and diastolic function.

[0005] According to a first aspect, one embodiment provides an ultrasonic device, comprising:

[0006] An ultrasound probe is used to emit ultrasound waves into a region of interest within a target tissue and to receive the echoes of the ultrasound waves to obtain ultrasound echo signals.

[0007] A transmitting and receiving control circuit is used to control the ultrasonic probe to transmit ultrasonic waves toward the region of interest and to receive the echoes of the ultrasonic waves.

[0008] Processor, used for:

[0009] In response to a first imaging command, strain imaging mode is applied to the first myocardial tissue of the target heart to obtain at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle.

[0010] In response to the second imaging command, the second myocardial tissue of the target heart is subjected to shear wave imaging mode to obtain the shear wave elastic parameters of the second myocardial tissue;

[0011] A quantitative assessment of cardiac performance is obtained based on the at least one strain elastic parameter and the shear wave elastic parameter, and the quantitative assessment of cardiac performance is used to characterize the systolic and / or diastolic performance of the target heart.

[0012] In some embodiments, the strain imaging pattern of the first myocardial tissue of the target heart includes:

[0013] A first ultrasound image is acquired, the first ultrasound image being used to reflect the tissue structure of the target heart, and the first myocardial tissue of the target heart is determined based on the first ultrasound image;

[0014] A first set of ultrasound images over a period of time is acquired, the first set of ultrasound images including multiple frames of the first ultrasound images, and at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the first set of ultrasound images.

[0015] In some embodiments, the shear wave imaging pattern of the second myocardial tissue of the target heart includes:

[0016] A second ultrasound image is acquired, which reflects the tissue structure of the target heart, and the second myocardial tissue of the target heart is determined based on the second ultrasound image; wherein, the first ultrasound image and the second ultrasound image satisfy a preset cross-sectional matching degree;

[0017] The shear wave generated by the second myocardial tissue is detected, and the shear wave elastic parameters of the second myocardial tissue are obtained based on the detection results.

[0018] In some embodiments, the ultrasound device further includes a display component for outputting visualization information; the processor is also configured to acquire a strain analysis curve of the first myocardial tissue obtained based on the strain imaging mode, and to acquire a shear wave propagation space-time map of the second myocardial tissue obtained based on the shear wave imaging mode; and to control the display component to display the strain analysis curve and the shear wave propagation space-time map on the same screen.

[0019] In some embodiments, at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the first set of ultrasound images, including:

[0020] Obtain the target first ultrasound image from the first ultrasound image set that corresponds to the start time of the cardiac cycle;

[0021] Based on the first ultrasound image of the target heart, the myocardial pericardium of the left atrium is obtained, and the strain value of the myocardial pericardium of the left atrium during the systolic phase is calculated by subtracting the strain value during the diastolic phase based on the first ultrasound image set to obtain the left atrial reserve strain parameter value; and / or, based on the first ultrasound image of the target heart, the myocardial pericardium of the right atrium is obtained, and the strain value of the myocardial pericardium of the right atrium during the systolic phase is calculated by subtracting the strain value during the diastolic phase based on the first ultrasound image set to obtain the right atrial reserve strain parameter value;

[0022] And / or,

[0023] Based on the first ultrasound image of the target heart, the myocardial envelope of the left ventricular wall is obtained; the strain rate curve of the myocardial envelope of the left ventricular wall during the cardiac cycle is calculated based on the first ultrasound image set; the pressure change curve of the left ventricular cavity during the cardiac cycle is obtained; the pressure-strain curve of the left ventricle during the cardiac cycle is obtained based on the strain rate curve of the left ventricular wall and the pressure change curve of the left ventricular cavity; and the myocardial work index is obtained based on the area under the closed curve of the pressure-strain curve; and / or, based on the first ultrasound image of the target heart, the myocardial envelope of the right ventricular wall is obtained; the strain rate curve of the right ventricular wall myocardial envelope during the cardiac cycle is calculated based on the first ultrasound image set; the pressure change curve of the right ventricular cavity during the cardiac cycle is obtained; the pressure-strain curve of the right ventricle during the cardiac cycle is obtained based on the strain rate curve of the right ventricular wall and the pressure change curve of the right ventricular cavity; and the myocardial work index is obtained based on the area under the closed curve of the pressure-strain curve.

[0024] In some embodiments, when the at least one strain elastic parameter is the left atrial reserve strain parameter and / or the right atrial reserve strain parameter, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the at least one strain elastic parameter is the myocardial work index of the left ventricle and / or the myocardial work index of the right ventricle, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

[0025] In some embodiments, the shear wave elastic parameters of the second myocardial tissue are obtained based on the detection results, including:

[0026] Shear waves generated by the second myocardial tissue of the target heart are detected to obtain shear wave motion information of the second myocardial tissue. Based on the shear wave motion information, spatiotemporal motion information on the shear wave propagation path is obtained. Based on the spatiotemporal motion information, the shear wave propagation wavefront at a preset time within the cardiac cycle is obtained to obtain the shear wave elastic parameters at the preset time.

[0027] In some embodiments, when detecting shear waves generated by the second myocardial tissue based on acoustic radiation force, the shear wave elastic parameters are obtained at the diastolic and / or systolic moments within the cardiac cycle; when detecting shear waves generated by the second myocardial tissue itself, the shear wave elastic parameters are obtained at the mitral valve closure moment and / or aortic valve closure moment of the target heart.

[0028] In some embodiments, when the shear wave elastic parameter corresponds to the diastolic time or the mitral valve closure time, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the shear wave elastic parameter corresponds to the systolic time or the aortic valve closure time, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

[0029] In some embodiments, the second myocardial tissue is myocardial tissue of the left ventricular wall and / or myocardial tissue of the right ventricular wall; and / or, the shear wave elastic parameters are shear elastic modulus and / or shear wave velocity.

[0030] In some embodiments, the first imaging command and the second imaging command may be the same command or different commands;

[0031] When the first imaging command and the second imaging command are the same command, a third ultrasound image is acquired. The third ultrasound image is used to reflect the tissue structure of the target heart. The first myocardial tissue and the second myocardial tissue of the target heart are determined based on the third ultrasound image.

[0032] A third set of ultrasound images over a period of time is acquired, the third set of ultrasound images including multiple frames of the third ultrasound images, and at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the third set of ultrasound images.

[0033] The shear wave generated by the second myocardial tissue is detected, and the shear wave elastic parameters of the second myocardial tissue are obtained based on the detection results.

[0034] In some embodiments, quantitative values ​​of the at least one strain elastic parameter and the shear wave elastic parameter are obtained, and calculations are performed using a preset formula to obtain a quantitative score of cardiac performance. The quantitative assessment result of cardiac performance is then obtained based on the quantitative score of cardiac performance.

[0035] According to a second aspect, one embodiment provides an ultrasonic device, comprising:

[0036] An ultrasound probe is used to emit ultrasound waves into a region of interest within a target tissue and to receive the echoes of the ultrasound waves to obtain ultrasound echo signals.

[0037] A transmitting and receiving control circuit is used to control the ultrasonic probe to transmit ultrasonic waves toward the region of interest and to receive the echoes of the ultrasonic waves.

[0038] Processor, used for:

[0039] The ultrasound probe is controlled to emit a first ultrasound wave toward the first myocardial tissue of the target heart and receive the echo of the first ultrasound wave to obtain a first ultrasound echo signal. Based on the first ultrasound echo signal, a first ultrasound image set over a period of time is obtained. The first ultrasound image set includes multiple frames of the first ultrasound image. The first ultrasound image is used to reflect the tissue structure of the target heart. Based on the first ultrasound image set, at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained.

[0040] The ultrasound probe is controlled to emit a second ultrasound wave for detecting shear waves into the second myocardial tissue of the target heart, and the echo of the second ultrasound wave is received to obtain a second ultrasound echo signal. Based on the second ultrasound echo signal, the shear wave elastic parameters of the second myocardial tissue are obtained.

[0041] The at least one strain elastic parameter and the shear wave elastic parameter are used to obtain a quantitative assessment result of cardiac performance, which is used to characterize the systolic and / or diastolic performance of the target heart.

[0042] In some embodiments, when the at least one strain elastic parameter is a left atrial reserve strain parameter and / or a right atrial reserve strain parameter, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the at least one strain elastic parameter is a myocardial work index of the left ventricular wall and / or a myocardial work index of the right ventricular wall, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

[0043] In some embodiments, the second myocardial tissue is a second myocardial tissue, and when detecting shear waves generated by the second myocardial tissue based on acoustic radiation force, the shear wave elastic parameters are obtained at the diastolic and / or systolic times during the cardiac cycle; when detecting shear waves generated by the second myocardial tissue itself, the shear wave elastic parameters are obtained at the mitral valve closure time and / or aortic valve closure time of the target heart.

[0044] According to a third aspect, one embodiment provides a cardiac assessment device, comprising:

[0045] Display components are used to display visual information;

[0046] A memory for storing imaging results of a target heart in various imaging modes; wherein the imaging results include at least one strain elastic parameter of the first myocardial tissue of the target heart during the cardiac cycle in strain imaging mode, and shear wave elastic parameters of the second myocardial tissue of the target heart in shear wave imaging mode.

[0047] Processor, used for:

[0048] Obtain from the memory at least one strain elastic parameter of the first myocardial tissue of the target heart during the cardiac cycle and the shear wave elastic parameter of the second myocardial tissue of the target heart;

[0049] A quantitative assessment of cardiac performance is obtained based on the at least one strain elastic parameter and the shear wave elastic parameter, and the quantitative assessment of cardiac performance is used to characterize the systolic and / or diastolic performance of the target heart.

[0050] According to the ultrasound equipment and cardiac assessment device of the above embodiments, strain elastic parameters can be used to qualitatively analyze the relative deformation state of myocardial tissue to reflect the systolic and diastolic functions of the heart, while shear wave elastic parameters can be used to quantitatively assess the elastic properties of myocardial tissue itself to reflect the systolic and diastolic functions of the heart. Therefore, when assessing the systolic and diastolic functions of the heart, combining strain elastic parameters and shear wave elastic parameters can comprehensively assess the deformation and elasticity dimensions of myocardial tissue. Furthermore, both strain elastic parameters and shear wave elastic parameters are quantitative parameters, allowing for quantitative assessment of the heart, thus enabling a comprehensive and intuitive evaluation of the heart's systolic and diastolic performance. Attached Figure Description

[0051] Figure 1 This is a schematic diagram of the structure of an ultrasonic device according to one embodiment;

[0052] Figure 2 This is a schematic diagram showing the strain elastic parameters of one embodiment;

[0053] Figure 3 This is a schematic diagram showing the strain elastic parameters of another embodiment;

[0054] Figure 4 This is a schematic diagram showing the elastic parameters of a shear wave according to one embodiment;

[0055] Figure 5 This is a schematic diagram showing the strain elastic parameters and shear wave elastic parameters of one embodiment;

[0056] Figure 6 This is a schematic diagram showing the strain elastic parameters and shear wave elastic parameters of another embodiment;

[0057] Figure 7 This is a schematic diagram of the structure of a cardiac assessment device according to one embodiment. Detailed Implementation

[0058] The present application will now be described in further detail with reference to specific embodiments and accompanying drawings. Similar elements in different embodiments are referred to by related similar element reference numerals. In the following embodiments, many details are described to facilitate a better understanding of the present application. However, those skilled in the art will readily recognize that some features may be omitted in different situations, or may be replaced by other elements, materials, or methods. In some cases, certain operations related to the present application are not shown or described in the specification. This is to avoid obscuring the core parts of the present application with excessive description. For those skilled in the art, detailed description of these related operations is not necessary; the relevant operations can be fully understood based on the description in the specification and general technical knowledge in the art.

[0059] Furthermore, the features, operations, or characteristics described in the specification can be combined in any suitable manner to form various embodiments. At the same time, the steps or actions in the method description can be rearranged or adjusted in a manner obvious to those skilled in the art. Therefore, the various orders in the specification and drawings are only for the clear description of a particular embodiment and do not imply a necessary order, unless otherwise stated that a particular order must be followed.

[0060] The serial numbers assigned to components in this document, such as "first" and "second," are used only to distinguish the described objects and have no sequential or technical meaning. The terms "connection" and "linkage" used in this application, unless otherwise specified, include both direct and indirect connections (linkages).

[0061] In some embodiments of this application, at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on strain imaging of the first myocardial tissue of the target heart. This strain elastic parameter can be used to qualitatively analyze the relative deformation state of the myocardial tissue to reflect the heart's systolic and diastolic functions. Shear wave elastic parameters of the second myocardial tissue are obtained based on shear wave imaging of the second myocardial tissue of the target heart. These shear wave elastic parameters can be used to quantitatively assess the elastic properties of the myocardial tissue itself to reflect the heart's systolic and diastolic functions. Since combining strain elastic parameters and shear wave elastic parameters allows for a comprehensive assessment of both the deformation and elasticity dimensions of the myocardial tissue when evaluating the heart's systolic and diastolic functions, and since both are quantitative parameters, they can be used for quantitative assessment of the heart. Therefore, a comprehensive and intuitive assessment of the heart's systolic and diastolic performance is possible.

[0062] Some embodiments provide an ultrasonic device; please refer to [the relevant documentation]. Figure 1 The ultrasonic device includes an ultrasonic probe 10, a transmission and reception control circuit, a processor 20, a human-computer interaction device 70, and a memory 80, which will be described in detail below.

[0063] An ultrasound probe 10 is used to emit ultrasound waves toward a region of interest within a target tissue and to receive the echoes of the ultrasound waves to obtain ultrasound echo signals. The ultrasound probe 10 includes a transducer (not shown) composed of multiple array elements arranged in an array. Each array element is used to emit ultrasound waves according to an excitation electrical signal, or to convert received ultrasound waves into electrical signals. Therefore, each array element can be used to achieve the mutual conversion between electrical pulse signals and ultrasound waves, thereby enabling the emission of ultrasound waves toward the biological tissue of the scanned object, and it can also be used to receive the echoes of ultrasound waves reflected back from the tissue.

[0064] The transmitting and receiving control circuit is used to control the ultrasonic probe 10 to transmit ultrasonic waves and receive the echoes of ultrasonic waves, and to obtain ultrasonic echo signals. The transmitting and receiving control circuit may include a transmitting circuit 30 and a receiving circuit 40. The transmitting circuit 30 is used to excite the ultrasonic probe 10 to transmit ultrasonic waves toward the scanned object according to the control of the processor 20. The receiving circuit 40 is used to receive the echoes of ultrasonic waves returned from the scanned object through the ultrasonic probe 10 to obtain ultrasonic echo signals, and can also process the ultrasonic echo signals.

[0065] The human-computer interaction device 70 is used for human-computer interaction, such as outputting visual information and receiving user input. It may include an input component and a display component, wherein the input component is used to receive user input, and may be a keyboard, operation buttons, mouse, trackball, touchpad, etc., or may be a touch screen integrated with the display; the display component is used to output visual information, and may be a display, touch display, screen, touch screen, etc.

[0066] The memory 80 is used to store various types of data.

[0067] Please refer to Figure 1 The ultrasound equipment may also include a beamforming module 50 and an IQ demodulation module 60.

[0068] The beamforming module 50 is signal-connected to the receiving circuit 40 and is used to perform beamforming processing on the echo signal, including delay and weighted summation. Because the distance from the ultrasonic receiving point in the tested tissue to the receiving array elements varies, the channel data of the same receiving point output by different receiving array elements has delay differences, requiring delay processing to align the phases. Weighted summation of the different channel data of the same receiving point is then performed to obtain the beamformed ultrasonic image data. The ultrasonic image data output by the beamforming module 50 is also called radio frequency (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.

[0069] The beamforming module 50 can perform the above functions using hardware, firmware, or software. The beamforming module 50 can be integrated into the processor 20 or configured separately; this invention does not impose any limitations on this.

[0070] The IQ demodulation module 60 removes the signal carrier through IQ demodulation, extracts the tissue structure information contained in the signal, and filters to remove 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. In some embodiments, the IQ demodulation module 60 also outputs the IQ data pair to the memory 80 for buffering or storage, so that the processor 20 can read the data from the memory 80 for subsequent image processing.

[0071] The IQ demodulation module 60 can also perform the above functions in hardware, firmware, or software. Similarly, the IQ demodulation module 60 can be integrated into the processor 20 or set up separately; this invention does not impose any limitations on this.

[0072] The processor 20 is configured to process input data according to specific logic instructions. It is a central controller circuit (CPU), one or more microprocessors 20, a graphics controller circuit (GPU), or any other electronic component. It can control peripheral electronic components according to input instructions or predetermined instructions, or perform data reading and / or saving 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 operating modes. The processing operations include, but are not limited to, adjusting or limiting the form of ultrasound waves emitted by the ultrasound probe 10, generating various image frames for display on the display of the human-machine interface device 70, or adjusting or limiting the content and form displayed on the display, or adjusting one or more image display settings displayed on the display (e.g., ultrasound images, interface components, locating regions of interest).

[0073] When an echo signal is received, the acquired ultrasound data can be processed in real time by the processor 20 during the scan, or it can be temporarily stored in the memory 80 and processed in a near real-time manner during online or offline operation.

[0074] In this embodiment, the processor 20 controls the operation of the transmitting circuit 30 and the receiving circuit 40, for example, controlling the transmitting circuit 30 and the receiving circuit 40 to operate alternately or simultaneously. The processor 20 can also determine a suitable operating mode according to the user's selection or the program settings, form a transmission sequence corresponding to the current operating mode, and send the transmission sequence to the transmitting circuit 30 so that the transmitting circuit 30 can use the appropriate transmission sequence to control the ultrasonic probe 10 to emit ultrasonic waves.

[0075] In some embodiments, the processor 20 controls the ultrasound probe to transmit ultrasound waves to the target tissue and receive the echoes of the ultrasound waves through the transmit and receive control circuit according to the transmit and receive parameters, thereby obtaining ultrasound echo signals, and processes the ultrasound echo signals according to the imaging parameters to obtain an ultrasound image of the target tissue.

[0076] In some embodiments, the transmit and receive parameters include parameters for the transmit sequence and parameters for the receive sequence. The transmit sequence parameters include the number of array elements used for transmitting and ultrasonic wave transmission parameters (e.g., pulse amplitude, transmit voltage, transmit frequency, number of waves emitted, transmit interval, transmit angle, transmit waveform, transmit aperture, linear density, dot density, and / or focal position, etc.). The receive sequence is used to control the reception of some or all of the ultrasonic waves from the multiple array elements after they have passed through the tissue. The receive sequence parameters include the number of array elements used for receiving and the echo reception parameters (e.g., reception angle, depth, etc.). The ultrasonic wave parameters in the transmit sequence and the echo parameters in the receive sequence may differ depending on the intended use of the ultrasonic echo or the image generated by the ultrasonic echo.

[0077] In some embodiments, the imaging parameters include parameters for signal processing and image processing of the ultrasonic echo signal received by the ultrasonic probe 10 by the processor 20. Signal processing refers to one or more steps of processing the ultrasonic echo signal / channel echo data in the signal domain, such as analog-to-digital conversion, signal demodulation, amplification, filtering, downsampling, and / or beamforming. Image processing refers to one or more steps of processing the signal-processed ultrasonic image data in the image domain, such as modulus extraction, logarithmic compression, grayscale transformation, and / or other unlisted image processing. Furthermore, image processing can also be image algorithm processing of the generated ultrasonic image.

[0078] The above is a brief description of ultrasound equipment. The following is a detailed explanation of the process of using ultrasound equipment to assess cardiac performance. Specifically, in the process of assessing cardiac performance, it is necessary to obtain the strain elastic parameters and shear wave elastic parameters of the myocardial tissue of the target heart using ultrasound equipment.

[0079] Please refer to Figure 2 and 3 In response to a first imaging command, the processor 20 performs strain imaging on the first myocardial tissue of the target heart to obtain at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle.

[0080] In some embodiments, the processor responds to a first imaging command to control an ultrasound probe to emit ultrasound waves toward the first myocardial tissue of the target heart and receives the echo of the ultrasound waves, obtaining a first ultrasound echo signal. A corresponding first ultrasound image is then acquired based on this first ultrasound echo signal. This first ultrasound image reflects the tissue structure of the target heart; for example, it can be acquired in the B (brightness) mode of the ultrasound device. Based on the first ultrasound image, the first myocardial tissue of the target heart can be determined. In some embodiments, the first ultrasound image may also be acquired through other means, such as historical storage within the ultrasound device.

[0081] The processor acquires a first set of ultrasound images over a period of time, including multiple frames of first ultrasound images, wherein this period of time is longer than one cardiac cycle of the target heart. Based on the first set of ultrasound images, changes in the first myocardial tissue within the cardiac cycle can be obtained, and at least one strain elastic parameter within the cardiac cycle can be acquired. In some embodiments, the processor may first acquire the target first ultrasound image from the first set of ultrasound images corresponding to the start time of the cardiac cycle. The start time of the cardiac cycle can be determined based on signals characterizing the cardiac cycle. For example, each cardiac cycle 92 of the target heart can be automatically determined based on ECG signal 91 (electrocardiogram signal), thereby automatically determining the start time of the cardiac cycle. Alternatively, the cardiac cycle and its various phases can be determined based on PCG signal (heart sound signal). In some embodiments, the target first ultrasound image may also be manually determined based on user selection.

[0082] Please refer to Figure 2 In some embodiments, the processor acquires the myocardial envelope of the left atrium of the target heart based on the target first ultrasound image, i.e., the first myocardial tissue is the myocardial envelope of the left atrium. In some embodiments, the user can operate on the target first ultrasound image based on a human-computer interaction device, and the processor acquires the myocardial envelope of the left atrium manually traced by the user. In some embodiments, the processor can also automatically identify the myocardial envelope of the left atrium based on the target first ultrasound image, for example, by automatically identifying the myocardial envelope of the left atrium based on a trained neural network model. In some embodiments, the myocardial envelope of the atrium can also be acquired by combining automatic identification with manual tracing, for example, by performing manual tracing on the basis of automatic identification.

[0083] The processor obtains the strain curve 95 of the myocardial envelope of the left atrium during the cardiac cycle based on the first set of ultrasound images. In some embodiments, when obtaining the myocardial envelope of the left atrium of the target heart based on the target first ultrasound image, the myocardial envelope of the left atrium in other first ultrasound images can be obtained based on two / three-dimensional speckle tracking technology. Then, the strain curve is obtained based on the relative strain values ​​of the myocardial envelope between the various first ultrasound images, and the strain curve is used to characterize the strain change of the myocardial envelope of the left atrium during the cardiac cycle. For example, using the myocardial envelope corresponding to the target first ultrasound image as the initial reference object, the relative strain values ​​of the myocardial envelope between other first ultrasound images and the target first ultrasound image are used as the strain values ​​of the corresponding other first ultrasound images. The relative strain values ​​can be calculated based on existing technology, such as calculating the relative position change of the myocardial envelope to obtain the corresponding relative strain values, which will not be elaborated here.

[0084] In some embodiments, the processor calculates the left atrial reserve strain parameter (LASr) by subtracting the diastolic strain value from the systolic strain value of the left atrial myocardial envelope during the cardiac cycle based on the strain curve. The systolic and diastolic phases represent the extreme strain values ​​of the heart, respectively; therefore, the difference between these two strain values ​​can effectively reflect the overall strain performance of the heart. In some embodiments, the systolic strain value can be selected as the peak strain value during systole, such as the strain value at end-systole. In some embodiments, the diastolic strain value can be selected as the peak strain value during diastole, such as the strain value at end-diastole. In some embodiments, the ECG signal can also be used to determine various phases of the cardiac cycle, such as end-systole and end-diastole. In this embodiment, the left atrial reserve strain parameter value has proven to have important evaluative value in heart failure with left ventricular diastolic dysfunction and preserved ejection fraction, and therefore can be used to describe the myocardial diastolic state.

[0085] In some embodiments, the first myocardial tissue can also be the myocardial envelope of the right atrium. That is, the myocardial envelope of the right atrium of the target heart can be obtained based on the first ultrasound image of the target heart, and the strain value of the myocardial envelope of the right atrium during the systolic phase minus the strain value during the diastolic phase can be calculated based on the set of first ultrasound images to obtain the right atrial reserve strain parameter value. The specific process corresponds to the process of calculating the left atrial reserve strain parameter value, and will not be described in detail here.

[0086] In some embodiments, when obtaining the left atrial reserve strain parameter value, the strain imaging described above can be performed under selected cardiac chamber sections, including but not limited to the parasternal long-axis section PLAX, the four-chamber section A4C, the two-chamber section A2C, and the apical three-chamber / long-axis section ALAX. In some embodiments, the above-mentioned sections can also be used when obtaining the right atrial reserve strain parameter value, or other suitable sections can also be used.

[0087] The above describes the process by which the processor obtains the left atrial reserve strain parameter value or the right atrial reserve strain parameter value based on the first set of ultrasound images. The processor can also obtain other strain elastic parameters based on the first set of ultrasound images, as explained in detail below.

[0088] Please refer to Figure 3 In some embodiments, the processor acquires the myocardial envelope of the left ventricular wall of the target heart based on the first ultrasound image of the target heart; that is, the first myocardial tissue is the myocardial envelope of the left ventricular wall. The acquisition of the myocardial envelope of the left ventricular wall can be based on automatic identification, manual tracing, or a combination of both; details will not be elaborated further here.

[0089] In some embodiments, the processor calculates a strain rate curve of the myocardial envelope of the left ventricular wall during the cardiac cycle based on a first set of ultrasound images. In some embodiments, the strain rate curve can be obtained based on the relative strain rates of the myocardial envelope between the various first ultrasound images. For example, the myocardial envelope corresponding to a target first ultrasound image can be used as an initial reference, and then the strain values ​​of the myocardial envelopes corresponding to other first ultrasound images, as well as the strain rate between those strain values ​​and the strain values ​​of the myocardial envelopes corresponding to the target first ultrasound image, can be calculated.

[0090] Furthermore, while acquiring the strain rate curve, the processor also needs to simultaneously acquire the pressure change curve within the left ventricular cavity during the cardiac cycle. In some embodiments, the systolic and diastolic blood pressure values ​​of the artery blood pressure of the subject to which the target heart belongs can be measured, for example, the brachial artery blood pressure of the subject can be measured. The processor then acquires the measured blood pressure during the cardiac cycle. Since this blood pressure can be used to characterize the pressure in the left ventricular cavity, the pressure change curve of the left ventricular cavity during the cardiac cycle can be obtained based on the measured blood pressure. The cardiac cycle corresponding to the pressure change curve can be adjusted based on the opening and closing times of the heart valves (mitral valve, aortic valve) to meet the standard cardiac cycle. The opening and closing of the heart valves can be determined based on grayscale ultrasound images or blood flow Doppler, for example, based on a first set of ultrasound images, or based on electrocardiogram signals.

[0091] The processor then obtains the pressure-strain curve 94 of the left ventricle during the cardiac cycle based on the strain rate curve of the left ventricular wall and the pressure change curve of the left ventricular cavity. This pressure-strain curve 94 is two-dimensionally distributed over a complete cardiac cycle and is used to characterize the strain changes of the myocardial envelope of the left ventricular wall and the pressure changes of the left ventricular cavity. The area under the closed curve of this pressure-strain curve can be used to obtain the myocardial work index. (Referencing...) Figure 3The pressure-strain curve 94 shows the strain rate on the horizontal axis and the pressure value (LVP) on the vertical axis. In this embodiment, the myocardial work index overcomes the afterload dependence of ejection fraction and left ventricular strain, thus enabling a more accurate reflection of myocardial contractile performance and can be used to describe the myocardial contractile state.

[0092] In some embodiments, the processor can acquire the myocardial envelope of the right ventricular wall of the target heart based on the first ultrasound image of the target heart, that is, the first myocardial tissue is the myocardial envelope of the right ventricular wall. At this time, the strain rate curve of the myocardial envelope of the right ventricular wall during the cardiac cycle is calculated based on the first ultrasound image set; the pressure change curve of the right ventricular cavity during the cardiac cycle is acquired; the pressure-strain curve of the right ventricle during the cardiac cycle is obtained based on the strain rate curve of the right ventricular wall and the pressure change curve of the right ventricular cavity; and the myocardial work index is obtained based on the area of ​​the closed curve of the pressure-strain curve. The specific process corresponds to the process of obtaining the myocardial work index based on the myocardial envelope of the left ventricular wall, and will not be described in detail here.

[0093] The above describes the process of obtaining strain elastic parameters using ultrasonic equipment. The following section provides a detailed explanation of the process of obtaining shear wave elastic parameters using ultrasonic equipment.

[0094] Please refer to Figure 4 The processor responds to the second imaging command and performs shear wave imaging on the second myocardial tissue of the target heart to obtain the shear wave elastic parameters of the second myocardial tissue.

[0095] In some embodiments, the processor responds to a second imaging command to control the ultrasound probe to emit ultrasound waves toward the second myocardial tissue of the target heart and receives the echo of the ultrasound waves to obtain an ultrasound echo signal. A corresponding ultrasound image is then acquired based on the ultrasound echo signal. This ultrasound image reflects the tissue structure of the target heart, wherein the second myocardial tissue of the target heart can be determined based on the ultrasound image. In some embodiments, the ultrasound image may also be historically stored in the ultrasound device.

[0096] In some embodiments, the processor also responds to a second imaging command by controlling the ultrasound probe to detect the emission of a second ultrasound wave towards the second myocardial tissue of the target heart for detecting shear waves, and receives the echo of the second ultrasound wave to obtain a second ultrasound echo signal as the detection result of the shear wave, and obtains the shear wave elastic parameters of the second myocardial tissue based on the second ultrasound echo signal. In some embodiments, since the propagation speed of shear waves is on the order of meters per second and the propagation distance in the myocardial wall is short, it will end propagating in a relatively short time. Generally, a high frame rate transmission scanning scheme is required to capture the propagation process of shear waves. Therefore, the second ultrasound wave is usually a high frame rate ultrasound signal, for example, a frame rate greater than 500 Hz.

[0097] In some embodiments, the processor controls an ultrasound probe to detect shear waves generated by the second myocardial tissue of the target heart, so as to obtain shear wave motion information of the second myocardial tissue based on the second ultrasound echo signal, obtain spatiotemporal motion information on the shear wave propagation path based on the shear wave motion information, and obtain the shear wave propagation wavefront at a preset time within the cardiac cycle based on the spatiotemporal motion information, so as to obtain the shear wave elastic parameters at the preset time. Please refer to [reference needed]. Figure 4 The corresponding spatiotemporal motion information can be obtained from the shear wave propagation spatiotemporal map 93 generated based on the second ultrasound echo signal. In some embodiments, shear wave elastic parameters are used to characterize the quantitative mechanical parameters of myocardial tissue, including shear elastic modulus and shear wave velocity. In some embodiments, the cardiac cycle and different moments of the cardiac cycle can be determined based on the electrocardiogram signal 91, thereby obtaining the shear wave elastic parameters of the second myocardial tissue at different moments of the cardiac cycle.

[0098] In some embodiments, the shear wave generated by the second myocardial tissue can be externally excited, for example, by acoustic radiation force causing the second myocardial tissue to generate a shear wave. In some embodiments, the shear wave generated by the second myocardial tissue can also be spontaneous, for example, generated by the second myocardial tissue itself. In some embodiments, when the shear wave is externally excited, a focused acoustic beam can be alternately used in the region of interest to generate acoustic radiation force at the location of the second myocardial tissue, and a high frame rate emission scanning strategy can be used to detect tissue motion information. This can be achieved by excitation and detection of the shear wave only at a preset time, or by maintaining a fixed frequency of excitation but only detecting the shear wave at a preset time. In some embodiments, when the shear wave is generated by the second myocardial tissue itself, a high frame rate emission scanning strategy can be used only in the region of interest to detect tissue motion information.

[0099] In some embodiments, when determining the preset time, when detecting shear waves generated by the second myocardial tissue based on acoustic radiation force, the processor acquires shear wave elastic parameters at the diastolic and / or systolic times within the cardiac cycle. For example, it can acquire the shear wave elastic parameters corresponding to the end-diastolic time or the end-systolic time. In some embodiments, when detecting shear waves generated by the second myocardial tissue itself, the processor acquires the shear wave elastic parameters at the mitral valve closure time and / or aortic valve closure time of the target heart. The mitral valve closure time (MVC) and / or aortic valve closure time (AVC) can be determined based on grayscale ultrasound images or blood flow Doppler, for example, based on a first set of ultrasound images, or based on electrocardiogram signals. In some embodiments, the second myocardial tissue can be myocardial tissue from the left ventricular wall or myocardial tissue from the right ventricular wall.

[0100] In some embodiments, when acquiring a high-frame-rate second ultrasound echo signal, motion information of the second myocardial tissue is extracted using techniques including, but not limited to, autocorrelation. This motion information includes displacement, velocity, acceleration, etc., for example, through a user-defined measurement region. This region can be a manually traced potential shear wave propagation path, or the processor can automatically identify and analyze the shear wave motion information at the location of the second myocardial tissue. Automatic identification and tracing can also be combined with editing and modification of the user's manual tracing to obtain spatiotemporal motion information along the potential shear wave propagation path. In some embodiments, the processor can also support multiple tracing operations on the spatial location of the same second myocardial tissue and / or its neighboring myocardium in a single examination, and independently complete the subsequent parameter calculation process for each tracing line. Finally, statistical analysis results of the spatiotemporal motion information from multiple tracings are obtained, including but not limited to median, mean, and variance, thereby improving the accuracy of shear wave propagation velocity estimation based on multiple calculations.

[0101] The above describes the process of obtaining shear wave elastic parameters using ultrasonic equipment. The following section provides a detailed explanation of the process for obtaining shear wave elastic parameters and strain elastic parameters using ultrasonic equipment.

[0102] In some embodiments, the first imaging command and the second imaging command may be the same command or different commands. Therefore, the strain imaging mode and the shear wave imaging mode can be performed simultaneously or in a sequential order.

[0103] In some embodiments, when the first imaging command and the second imaging command are the same command, the ultrasound device can simultaneously perform strain imaging mode and shear wave imaging mode based on multimodal mode. For example, the processor can control the ultrasound probe to alternately emit the first ultrasound wave and the second ultrasound wave, and acquire a third ultrasound image based on the echo of the first ultrasound wave. The third ultrasound image is used to reflect the tissue structure of the target heart. Therefore, the first myocardial tissue and the second myocardial tissue of the target heart are determined based on the third ultrasound image.

[0104] The processor acquires a third set of ultrasound images over a period of time. The third set of ultrasound images includes multiple frames of third ultrasound images. Based on the third set of ultrasound images, at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained. The specific process can be referred to the process of obtaining strain elastic parameters described above, and will not be repeated here.

[0105] The processor detects the shear wave generated by the second myocardial tissue based on the second ultrasound, obtains the detection result based on the echo of the second ultrasound, and obtains the shear wave elastic parameters of the second myocardial tissue based on the detection result. The specific process can be referred to the above process of obtaining the shear wave elastic parameters, and will not be repeated here.

[0106] In some embodiments, when the first imaging command and the second imaging command are different commands, the ultrasound device can sequentially perform strain imaging mode and shear wave imaging mode. The strain imaging mode can be performed first and then the shear wave imaging mode can be performed, or the shear wave imaging mode can be performed first and then the strain imaging mode can be performed. The following example illustrates the case of performing strain imaging mode first.

[0107] The processor controls the strain imaging mode to complete the strain imaging of the first myocardial tissue location and obtain the strain results, including strain curve analysis and the strain elastic parameters corresponding to the strain curve analysis.

[0108] The processor freezes the strain results of the current strain imaging mode and, in response to the user's operation of the duplex button, controls the display component to simultaneously display the first ultrasound image of the strain imaging mode, the strain results, and the second ultrasound image of the shear wave imaging mode, preparing for the shear wave elastography procedure. Furthermore, to ensure that the strain imaging mode and the shear wave imaging mode perform analysis on the same cardiac chamber section as much as possible, a section matching degree prompt is provided to ensure that the section matching degree of the first ultrasound image of the strain imaging mode and the second ultrasound image of the shear wave imaging mode meets preset requirements, i.e., the sections of the first and second ultrasound images are similar.

[0109] The processor controls the shear wave imaging mode to complete the shear wave imaging of the second myocardial tissue location and obtain the shear wave results, including the shear wave propagation space-time map, which is a map representing the space-time motion information.

[0110] Please refer to Figure 5 and Figure 6 In some embodiments, the processor can also fuse and analyze and display shear wave results and strain results, for example, to obtain quantitative assessment results of cardiac performance and control the display component to display them on the same screen. For example, the processor is also used to acquire the strain analysis curve of a first myocardial tissue obtained based on the strain imaging mode, which may include a strain curve or a strain rate curve, and to acquire the shear wave propagation space-time map of a second myocardial tissue obtained based on the shear wave imaging mode. Then, the processor controls the display component to display the strain analysis curve and the shear wave propagation space-time map on the same screen, allowing the user to analyze the corresponding strain analysis curve and shear wave propagation space-time map on the same screen. For example, the elastic parameters obtained by different imaging functions are displayed independently in their respective functional interfaces. For example, the strain imaging function displays the strain results at the corresponding myocardial tissue location in the strain function window, and the shear wave results are displayed in the shear wave function window.

[0111] In some embodiments, the fusion analysis and display of the above shear wave results and strain results can be performed online on an ultrasonic device.

[0112] In some embodiments, the fusion analysis and display of the shear wave and strain results can be performed offline in the cardiac assessment device. For example, after completing strain imaging and shear wave imaging modes, the ultrasound device outputs and stores corresponding reports, which include shear wave and strain results. The cardiac assessment device can then obtain the shear wave and strain results based on the reports, perform fusion analysis and display, thereby completing the fusion analysis and calculation of the two elastic parameters offline, and finally outputting and displaying the parameter fusion results.

[0113] The above describes the process of obtaining shear wave elastic parameters and strain elastic parameters using ultrasound equipment. The following describes the process of obtaining quantitative assessment results of cardiac performance.

[0114] The processor obtains a quantitative assessment of cardiac performance based on at least one strain elastic parameter and a shear wave elastic parameter. The quantitative assessment of cardiac performance is used to characterize the systolic and / or diastolic performance of the target heart.

[0115] In some embodiments, the processor acquires quantitative values ​​of at least one strain elastic parameter and a shear wave elastic parameter, and performs calculations using a preset formula to obtain a quantitative score of cardiac performance, and obtains a quantitative assessment result of cardiac performance based on the quantitative score of cardiac performance.

[0116] In some embodiments, a preset formula is used to represent the weight between the quantitative values ​​of at least one strain elastic parameter and the quantitative values ​​of the shear wave elastic parameter. The initial value of this weight can be set based on preliminary clinical trials or experience, and subsequent convergence optimization can be achieved through multiple data collections and physician evaluations. Thus, a quantitative score of cardiac performance is obtained based on the preset formula and the quantitative values ​​of each parameter. In some embodiments, the preset formula may also represent the calculation process for each quantitative value, thereby obtaining a quantitative score of cardiac performance based on the calculation results of each quantitative value.

[0117] In some embodiments, when at least one strain elastic parameter is a left atrial reserve strain parameter and / or a right atrial reserve strain parameter, the quantitative assessment results of cardiac performance are used to characterize the diastolic performance of the target heart. In some embodiments, when at least one strain elastic parameter is a left ventricular myocardial work index and / or a right ventricular myocardial work index, the quantitative assessment results of cardiac performance are used to characterize the systolic performance of the target heart.

[0118] In some embodiments, when the shear wave elastic parameter corresponds to the diastolic time or the mitral valve closure time, the quantitative assessment results of cardiac performance are used to characterize the diastolic performance of the target heart. In some embodiments, when the shear wave elastic parameter corresponds to the systolic time or the aortic valve closure time, the quantitative assessment results of cardiac performance are used to characterize the systolic performance of the target heart.

[0119] In some embodiments, the diastolic performance score of the target heart can be calculated based on the left atrial reserve strain parameters and / or right atrial reserve strain parameters, as well as the shear wave elastic parameters corresponding to the diastolic time or the mitral valve closure time. Figure 5 As shown, the diastolic performance score P dia The value is 20.62. In some embodiments, the systolic performance score of the target heart can be calculated based on the myocardial work index of the left ventricle and / or the myocardial work index of the right ventricle, and the shear wave elastic parameters corresponding to the systolic time or the aortic valve closure time, for example... Figure 6 As shown, the shrinkage performance score is P. sys 971.12.

[0120] In some embodiments, the display component may also display diastolic performance scores, systolic performance scores, and quantitative cardiac performance scores, for example, displayed below shear wave results or strain results, representing the diastolic and systolic functions of the current myocardial segment, respectively.

[0121] In some embodiments, the processor can also classify diastolic performance scores, systolic performance scores, and quantitative cardiac performance scores, for example, based on clinical data and physician diagnostic analysis. In some embodiments, to provide intuitive feedback on cardiac function status, such as indicating normal / abnormal or abnormal levels, the processor can also provide a classification reference for the current performance score based on standard classifications, such as displaying a "Normal" indicator for normal performance. In some embodiments, the classification can include multiple levels, such as Level 1 and Level 2, with different levels corresponding to different scores.

[0122] The above is an explanation of ultrasound equipment and the process of using ultrasound equipment for online quantitative assessment of cardiac performance.

[0123] Some embodiments provide a cardiac assessment device that can acquire imaging results in various imaging modes, including shear wave results and strain results. For example, in strain imaging mode, it acquires at least one strain elastic parameter of the first myocardial tissue of the target heart during the cardiac cycle, and in shear wave imaging mode, the shear wave elastic parameter of the second myocardial tissue of the target heart. The device then performs fusion analysis and display based on the shear wave results and strain results. Therefore, the cardiac assessment device can perform offline quantitative assessment of cardiac performance.

[0124] Please refer to Figure 7In some embodiments, the cardiac assessment device includes a display component 110, a memory 120, and a processor 130. The display component is used to display visual information, the memory is used to store imaging results of the target heart in various imaging modes, and the processor is used to control the display component and the memory, as well as to control the fusion analysis and display of shear wave results and strain results. The specific process is the same as described in the above embodiments and will not be repeated here.

[0125] Those skilled in the art will understand that all or part of the functions of the various methods in the above embodiments can be implemented by hardware or by computer programs. When all or part of the functions in the above embodiments are implemented by computer programs, the program can be stored in a computer-readable storage medium, which may include: read-only memory, random access memory, disk, optical disk, hard disk, etc., and the program is executed by a computer to achieve the above functions. For example, the program can be stored in the memory of a device, and when the program in the memory is executed by the processor, all or part of the above functions can be achieved. In addition, when all or part of the functions in the above embodiments are implemented by computer programs, the program can also be stored in a server, another computer, disk, optical disk, flash drive, or external hard drive, etc., and can be downloaded or copied to the memory of a local device, or the system of the local device can be updated. When the program in the memory is executed by the processor, all or part of the functions in the above embodiments can be achieved.

[0126] The above examples illustrate this application only to aid understanding and are not intended to limit its scope. Those skilled in the art to which this application pertains can make various simple deductions, modifications, or substitutions based on the ideas presented.

Claims

1. An ultrasonic device, characterized in that, include: An ultrasound probe is used to emit ultrasound waves into a region of interest within a target tissue and to receive the echoes of the ultrasound waves to obtain ultrasound echo signals. A transmitting and receiving control circuit is used to control the ultrasonic probe to transmit ultrasonic waves toward the region of interest and to receive the echoes of the ultrasonic waves. Processor, used for: In response to a first imaging command, strain imaging mode is applied to the first myocardial tissue of the target heart to obtain at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle. In response to the second imaging command, the second myocardial tissue of the target heart is subjected to shear wave imaging mode to obtain the shear wave elastic parameters of the second myocardial tissue; A quantitative assessment of cardiac performance is obtained based on the at least one strain elastic parameter and the shear wave elastic parameter, and the quantitative assessment of cardiac performance is used to characterize the systolic and / or diastolic performance of the target heart.

2. The ultrasonic device as described in claim 1, characterized in that, The strain imaging mode for the first myocardial tissue of the target heart includes: A first ultrasound image is acquired, the first ultrasound image being used to reflect the tissue structure of the target heart, and the first myocardial tissue of the target heart is determined based on the first ultrasound image; A first set of ultrasound images over a period of time is acquired, the first set of ultrasound images including multiple frames of the first ultrasound images, and at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the first set of ultrasound images.

3. The ultrasonic device as described in claim 2, characterized in that, The shear wave imaging mode for the second myocardial tissue of the target heart includes: A second ultrasound image is acquired, which reflects the tissue structure of the target heart, and the second myocardial tissue of the target heart is determined based on the second ultrasound image; wherein, the first ultrasound image and the second ultrasound image satisfy a preset cross-sectional matching degree; The shear wave generated by the second myocardial tissue is detected, and the shear wave elastic parameters of the second myocardial tissue are obtained based on the detection results.

4. The ultrasonic device as described in claim 3, characterized in that, It also includes a display component for outputting visualization information; the processor is further configured to acquire the strain analysis curve of the first myocardial tissue obtained based on the strain imaging mode, and to acquire the shear wave propagation space-time map of the second myocardial tissue obtained based on the shear wave imaging mode; and to control the display component to display the strain analysis curve and the shear wave propagation space-time map on the same screen.

5. The ultrasonic device as described in claim 2, characterized in that, At least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the first set of ultrasound images, including: Obtain the target first ultrasound image from the first ultrasound image set that corresponds to the start time of the cardiac cycle; Based on the first ultrasound image of the target heart, the myocardial pericardium of the left atrium is obtained, and the strain value of the myocardial pericardium of the left atrium during the systolic phase is calculated by subtracting the strain value during the diastolic phase based on the first ultrasound image set to obtain the left atrial reserve strain parameter value; and / or, based on the first ultrasound image of the target heart, the myocardial pericardium of the right atrium is obtained, and the strain value of the myocardial pericardium of the right atrium during the systolic phase is calculated by subtracting the strain value during the diastolic phase based on the first ultrasound image set to obtain the right atrial reserve strain parameter value; And / or, Based on the first ultrasound image of the target heart, the myocardial envelope of the left ventricular wall is obtained; the strain rate curve of the myocardial envelope of the left ventricular wall during the cardiac cycle is calculated based on the first ultrasound image set; the pressure change curve of the left ventricular cavity during the cardiac cycle is obtained; the pressure-strain curve of the left ventricle during the cardiac cycle is obtained based on the strain rate curve of the left ventricular wall and the pressure change curve of the left ventricular cavity; and the myocardial work index is obtained based on the area under the closed curve of the pressure-strain curve; and / or, based on the first ultrasound image of the target heart, the myocardial envelope of the right ventricular wall is obtained; the strain rate curve of the right ventricular wall myocardial envelope during the cardiac cycle is calculated based on the first ultrasound image set; the pressure change curve of the right ventricular cavity during the cardiac cycle is obtained; the pressure-strain curve of the right ventricle during the cardiac cycle is obtained based on the strain rate curve of the right ventricular wall and the pressure change curve of the right ventricular cavity; and the myocardial work index is obtained based on the area under the closed curve of the pressure-strain curve.

6. The ultrasonic device as described in claim 5, characterized in that, When the at least one strain elastic parameter is the left atrial reserve strain parameter and / or the right atrial reserve strain parameter, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the at least one strain elastic parameter is the myocardial work index of the left ventricle and / or the myocardial work index of the right ventricle, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

7. The ultrasonic device as described in claim 3, characterized in that, Based on the detection results, the shear wave elastic parameters of the second myocardial tissue were obtained, including: Shear waves generated by the second myocardial tissue of the target heart are detected to obtain shear wave motion information of the second myocardial tissue. Based on the shear wave motion information, spatiotemporal motion information on the shear wave propagation path is obtained. Based on the spatiotemporal motion information, the shear wave propagation wavefront at a preset time within the cardiac cycle is obtained to obtain the shear wave elastic parameters at the preset time.

8. The ultrasonic device as described in claim 7, characterized in that, When detecting shear waves generated by the second myocardial tissue based on acoustic radiation force, the shear wave elastic parameters are obtained at the diastolic and / or systolic times during the cardiac cycle; when detecting shear waves generated by the second myocardial tissue itself, the shear wave elastic parameters are obtained at the mitral valve closure time and / or aortic valve closure time of the target heart.

9. The ultrasonic device as described in claim 8, characterized in that, When the shear wave elastic parameter corresponds to the diastolic time or the mitral valve closure time, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the shear wave elastic parameter corresponds to the systolic time or the aortic valve closure time, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

10. The ultrasonic device as described in claim 7, characterized in that, The second myocardial tissue is myocardial tissue of the left ventricular wall and / or myocardial tissue of the right ventricular wall; and / or, the shear wave elastic parameters are shear elastic modulus and / or shear wave velocity.

11. The ultrasonic device as described in claim 1, characterized in that, The first imaging command and the second imaging command may be the same command or different commands; When the first imaging command and the second imaging command are the same command, a third ultrasound image is acquired. The third ultrasound image is used to reflect the tissue structure of the target heart. The first myocardial tissue and the second myocardial tissue of the target heart are determined based on the third ultrasound image. A third set of ultrasound images over a period of time is acquired, the third set of ultrasound images including multiple frames of the third ultrasound images, and at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained based on the third set of ultrasound images. The shear wave generated by the second myocardial tissue is detected, and the shear wave elastic parameters of the second myocardial tissue are obtained based on the detection results.

12. The ultrasonic device as described in claim 1, characterized in that, The quantitative values ​​of at least one strain elastic parameter and the quantitative value of the shear wave elastic parameter are obtained, and a preset formula is used to calculate the cardiac performance quantitative score. The cardiac performance quantitative assessment result is obtained based on the cardiac performance quantitative score.

13. An ultrasonic device, characterized in that, include: An ultrasound probe is used to emit ultrasound waves into a region of interest within a target tissue and to receive the echoes of the ultrasound waves to obtain ultrasound echo signals. A transmitting and receiving control circuit is used to control the ultrasonic probe to transmit ultrasonic waves toward the region of interest and to receive the echoes of the ultrasonic waves. Processor, used for: The ultrasound probe is controlled to emit a first ultrasound wave toward the first myocardial tissue of the target heart and receive the echo of the first ultrasound wave to obtain a first ultrasound echo signal. Based on the first ultrasound echo signal, a first ultrasound image set over a period of time is obtained. The first ultrasound image set includes multiple frames of the first ultrasound image. The first ultrasound image is used to reflect the tissue structure of the target heart. Based on the first ultrasound image set, at least one strain elastic parameter of the first myocardial tissue during the cardiac cycle is obtained. The ultrasound probe is controlled to emit a second ultrasound wave for detecting shear waves into the second myocardial tissue of the target heart, and the echo of the second ultrasound wave is received to obtain a second ultrasound echo signal. Based on the second ultrasound echo signal, the shear wave elastic parameters of the second myocardial tissue are obtained. The at least one strain elastic parameter and the shear wave elastic parameter are used to obtain a quantitative assessment result of cardiac performance, which is used to characterize the systolic and / or diastolic performance of the target heart.

14. The ultrasonic device as described in claim 13, characterized in that, When the at least one strain elastic parameter is the left atrial reserve strain parameter and / or the right atrial reserve strain parameter, the quantitative assessment result of cardiac performance is used to characterize the diastolic performance of the target heart; when the at least one strain elastic parameter is the myocardial work index of the left ventricular wall and / or the myocardial work index of the right ventricular wall, the quantitative assessment result of cardiac performance is used to characterize the systolic performance of the target heart.

15. The ultrasonic device as described in claim 13, characterized in that, The second myocardial tissue is a second myocardial tissue. When detecting the shear wave generated by the second myocardial tissue based on acoustic radiation force, the shear wave elastic parameters are obtained at the diastolic and / or systolic times during the cardiac cycle. When detecting the shear wave generated by the second myocardial tissue itself, the shear wave elastic parameters are obtained at the mitral valve closure time and / or aortic valve closure time of the target heart.

16. A cardiac assessment device, characterized in that, include: Display components are used to display visual information; A memory for storing imaging results of a target heart in various imaging modes; wherein the imaging results include at least one strain elastic parameter of the first myocardial tissue of the target heart during the cardiac cycle in strain imaging mode, and shear wave elastic parameters of the second myocardial tissue of the target heart in shear wave imaging mode. Processor, used for: Obtain from the memory at least one strain elastic parameter of the first myocardial tissue of the target heart during the cardiac cycle and the shear wave elastic parameter of the second myocardial tissue of the target heart; A quantitative assessment of cardiac performance is obtained based on the at least one strain elastic parameter and the shear wave elastic parameter, and the quantitative assessment of cardiac performance is used to characterize the systolic and / or diastolic performance of the target heart.

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