An ultrasonic imaging method and an ultrasonic imaging system for the heart

Abstract

The present invention provides a method and a system for ultrasonic imaging of the heart, belonging to the field of ultrasonic imaging. In view of the problem that the physiological movement of the heart itself poses challenges to elastography, the heart is first imaged to obtain an ultrasonic image, and then the myocardium is identified from the ultrasonic image and the position of the myocardium (such as the myocardial segment to be observed) is tracked to obtain the real-time position of the myocardium. On this basis, elastography is carried out. Further, considering that the chamber structures such as the atrium and ventricle of the heart will affect the propagation of shear waves, acoustic radiation force is applied to the myocardium to be observed (such as its geometric center or center of gravity) based on the real-time position of the myocardium to generate shear waves, so as to ensure the effectiveness of shear wave generation and sufficient signal-to-noise ratio.

Description

Technical Field

[0001] The present invention relates to the field of ultrasonic imaging, and particularly to an ultrasonic imaging method and an ultrasonic imaging system for the heart. Background Art

[0002] The evaluation of myocardial tissue fibrosis has great clinical value. The current clinical gold standard is myocardial biopsy, but myocardial biopsy is invasive, has a high technical difficulty, and has the risk of intraoperative complications, so its clinical use is limited. Therefore, evaluating myocardial tissue fibrosis by imaging means becomes an option. The existing imaging means for evaluating myocardial tissue fibrosis mainly rely on cardiac magnetic resonance imaging. However, cardiac magnetic resonance imaging has its inherent drawbacks, such as slow imaging, high cost, and is not applicable to all patient groups (for example, patients with kidney disease cannot undergo cardiac contrast magnetic resonance examination). Therefore, there is a lack of an efficient and safe imaging means in clinical practice for screening and judging the degree of myocardial fibrosis in patients during routine clinical examinations.

[0003] Shear wave elastography, as an emerging elastography technology in ultrasonic imaging, has proven its effectiveness in application fields such as the liver and superficial tissues, especially its application value in the grading diagnosis of liver fibrosis. Compared with organs such as the liver, due to the physiological movement of the heart itself, that is, the heart continuously contracts and relaxes, this brings difficulties to the elastography of the heart. Summary of the Invention

[0004] To solve the above problems, an ultrasonic imaging method and an ultrasonic imaging system for the heart are described in detail below.

[0005] According to a first aspect, in one embodiment, an ultrasonic imaging method for the heart is provided, including:

[0006] Performing real-time ultrasonic scanning on a target tissue including the heart through an ultrasonic probe to obtain an ultrasonic image of the heart, and displaying the ultrasonic image in a first area in real time;

[0007] Identifying the section type of the displayed ultrasonic image based on a preset section type recognition model to obtain a section type recognition result, and displaying the section type recognition result in the first area;

[0008] Judging whether the currently displayed ultrasonic image meets the requirements according to the section type recognition result. If it meets the requirements, identifying each myocardium included in the currently displayed ultrasonic image of the heart based on a preset myocardium recognition model, and marking it in the ultrasonic image;

[0009] Tracking the positions of the identified myocardiums as the ultrasonic image displayed in the first area is updated;

[0010] Determining the target myocardium;

[0011] In the first elastography mode: at multiple moments that meet the conditions, according to the real-time position of the target myocardium at the corresponding moment, control the ultrasonic probe to apply acoustic radiation force to the target myocardium to generate shear waves multiple times; perform ultrasonic observation on each generated shear wave through the ultrasonic probe to perform shear wave imaging on the target myocardium and generate a color elastogram of the target myocardium;

[0012] In the second elastography mode: at multiple moments that meet the conditions, at the real-time position of the target myocardium at the corresponding moment, perform ultrasonic observation on the shear waves generated by the spontaneous physiological phenomena of the heart through the ultrasonic probe to perform shear wave imaging on the target myocardium and generate a color elastogram of the target myocardium;

[0013] Overlay and display the color elastogram of the target myocardium on the ultrasonic image. When the generated color elastogram is updated, the displayed color elastogram is also updated accordingly.

[0014] In one embodiment, the ultrasonic imaging method of the heart further includes a third elastography mode. In the third elastography mode:

[0015] At multiple moments that meet the conditions, according to the real-time position of the target myocardium at the corresponding moment, control the ultrasonic probe to apply acoustic radiation force to the target myocardium to generate shear waves multiple times; perform ultrasonic observation on each generated shear wave through the ultrasonic probe to perform shear wave imaging on the target myocardium and generate a first color elastogram of the target myocardium;

[0016] At multiple moments that meet the conditions, at the real-time position of the target myocardium at the corresponding moment, perform ultrasonic observation on the shear waves generated by the spontaneous physiological phenomena of the heart through the ultrasonic probe to perform shear wave imaging on the target myocardium and generate a second color elastogram of the target myocardium;

[0017] Generate a color elastogram of the target myocardium based on the first color elastogram and the second color elastogram of the target myocardium.

[0018] In one embodiment, the ultrasonic imaging method of the heart further includes:

[0019] After determining the target myocardium, select an elastography mode that matches the type of the target myocardium from multiple elastography modes as the current elastography mode; and / or,

[0020] Select an elastography mode that matches the section type of the current ultrasonic image from multiple elastography modes as the current elastography mode according to the section type recognition result.

[0021] In one embodiment, determining whether the currently displayed ultrasound image meets the requirements according to the cross-section type recognition result includes: determining whether the currently displayed ultrasound image is of the first cross-section type according to the cross-section type recognition result, and if so, it meets the requirements;

[0022] When the ultrasound image is of the first cross-section type, after performing elastography based on the current elastography mode, further determine the second cross-section type to be scanned next based on the target myocardium, and prompt the user to move or rotate the ultrasound probe; as the ultrasound probe moves, when the cross-section type recognition model recognizes the displayed ultrasound image as the second cross-section type, prompt the user to stop the movement of the ultrasound probe; and perform elastography based on the current elastography mode when the ultrasound image is of the second cross-section type.

[0023] In one embodiment, determining the target myocardium includes:

[0024] According to the cross-section type recognition result, display a cross-section schematic diagram corresponding to the cross-section type of the ultrasound image in the first area, and mark the myocardium corresponding to the cross-section type on the cross-section schematic diagram;

[0025] In response to a selection instruction for the myocardium marked on the cross-section schematic diagram, determine the selected myocardium as the target myocardium.

[0026] In one embodiment, in the first elastography mode: further mark the trigger position of the shear wave on the cross-section schematic diagram; in the second elastography mode: further mark the mechanism and / or position of the shear wave generated by the spontaneous physiological phenomenon of the heart on the cross-section schematic diagram.

[0027] In one embodiment, the multiple moments that meet the conditions include: the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart; or, the moment when the mitral valve closes and the moment when the aortic valve closes.

[0028] According to a second aspect, an embodiment provides an ultrasound imaging method for the heart, including:

[0029] Perform real-time ultrasound scanning on a target tissue including the heart through an ultrasound probe to obtain an ultrasound image of the heart, and display the ultrasound image in real time in a first area;

[0030] Based on a preset cross-section type recognition model, perform cross-section type recognition on the displayed ultrasound image to obtain a cross-section type recognition result, and display the cross-section type recognition result in the first area;

[0031] Based on the recognition result of the cross-section type, determine whether the currently displayed ultrasound image is of the first cross-section type. If so, identify the myocardium corresponding to the cross-section type of the ultrasound image included in the currently displayed ultrasound image based on a preset myocardium recognition model, and mark and display the shape and position of the recognized myocardium in the currently displayed ultrasound image by superimposing a contour rendering marker;

[0032] As the ultrasound image displayed in the first region is updated, perform position tracking on the recognized myocardium, and update the contour rendering marker superimposed on the ultrasound image based on the position tracking result;

[0033] Display a first cross-section schematic diagram corresponding to the first cross-section type in the first region, and mark the myocardium corresponding to the first cross-section type on the first cross-section schematic diagram;

[0034] In response to a selection instruction for the myocardium marked on the first cross-section schematic diagram, determine the target myocardium;

[0035] When the ultrasound image is of the first cross-section type: Obtain the real-time cardiac cycle phase of the heart, and control the ultrasound probe to apply acoustic radiation force to the target myocardium to generate shear waves multiple times according to the real-time position of the target myocardium at the corresponding moment, where the corresponding moment is the moment corresponding to each of the multiple cardiac cycle phases that meet the conditions within each cardiac cycle;

[0036] Based on the target myocardium, determine the second cross-section type to be scanned next, and prompt the user to move or rotate the ultrasound probe; As the ultrasound probe moves, when the displayed ultrasound image is recognized as the second cross-section type based on the cross-section type recognition model, prompt the user to stop the movement of the ultrasound probe;

[0037] When the ultrasound image is of the second cross-section type: Identify the target myocardium from the ultrasound image, and perform position tracking on the recognized target myocardium as the ultrasound image displayed in the first region is updated; Obtain the real-time cardiac cycle phase of the heart, and control the ultrasound probe to apply acoustic radiation force to the target myocardium to generate shear waves multiple times according to the real-time position of the target myocardium at the corresponding moment, where the corresponding moment is the moment corresponding to each of the multiple cardiac cycle phases that meet the conditions within each cardiac cycle;

[0038] Perform ultrasonic observation on each generated shear wave through the ultrasound probe to perform shear wave imaging on the target myocardium and generate a color elasticity image of the target myocardium;

[0039] Superimpose and display the color elasticity image of the target myocardium on the ultrasound image, and when the generated color elasticity image is updated, the displayed color elasticity image is also updated accordingly.

[0040] In one embodiment, the obtaining of the real-time cardiac phase includes: obtaining a first type of physiological signal of the heart; the first type of physiological signal includes an electrocardiogram signal and / or a heart sound signal; and identifying the cardiac phase according to a phase recognition model.

[0041] In one embodiment, the multiple cardiac phases that meet the conditions include: the cardiac phase corresponding to the end-diastolic phase of the heart and the cardiac phase corresponding to the end-systolic phase of the heart.

[0042] According to a third aspect, an embodiment provides a method for ultrasonic imaging of the heart, including:

[0043] Performing real-time ultrasonic scanning on a target tissue including the heart through an ultrasonic probe to obtain an ultrasonic image of the heart, and displaying the ultrasonic image in a first area in real time;

[0044] Identifying the section type of the displayed ultrasonic image based on a preset section type recognition model to obtain a section type recognition result, and displaying the section type recognition result in the first area;

[0045] Judging whether the currently displayed ultrasonic image meets the requirements according to the section type recognition result. If it meets the requirements, identifying each myocardium included in the currently displayed ultrasonic image of the heart based on a preset myocardium recognition model, and marking it in the ultrasonic image;

[0046] Tracking the position of the identified myocardium as the ultrasonic image displayed in the first area is updated;

[0047] Determining the target myocardium;

[0048] Controlling the ultrasonic probe to apply acoustic radiation force to the target myocardium at multiple moments that meet the conditions according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times;

[0049] Observing the ultrasonic waves of each generated shear wave through the ultrasonic probe to perform shear wave imaging on the target myocardium and generate a color elasticity image of the target myocardium;

[0050] Overlaying and displaying the color elasticity image of the target myocardium on the ultrasonic image. When the generated color elasticity image is updated, the displayed color elasticity image is also updated accordingly.

[0051] In one embodiment, the determining of the target myocardium includes at least one of the following:

[0052] Displaying a section schematic diagram corresponding to the section type of the ultrasonic image in the first area according to the section type recognition result, and marking the myocardium corresponding to the section type on the section schematic diagram; in response to a selection instruction for the myocardium marked on the section schematic diagram, determining the selected myocardium as the target myocardium;

[0053] In response to a selection instruction for the myocardium on the ultrasonic image, the selected myocardium is determined as the target myocardium;

[0054] Generate and display elastic region options, where the elastic region options include at least two of an upper region option, a lower region option, a left region option, a right region option, and an all-region option; in response to a selection instruction from the user for the elastic region options, the myocardium associated with the selected elastic region is determined as the target myocardium; where the myocardium associated with the upper region option is the myocardium in the upper region of the ultrasonic image of the current section type, the myocardium associated with the lower region option is the myocardium in the lower region of the ultrasonic image of the current section type, the myocardium associated with the left region option is the myocardium in the left region of the ultrasonic image of the current section type, the myocardium associated with the right region option is the myocardium in the right region of the ultrasonic image of the current section type, and the myocardium associated with the all-region option is the myocardium in the entire region of the ultrasonic image of the current section type.

[0055] In one embodiment, the multiple moments that meet the conditions include: the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart.

[0056] According to a fourth aspect, an embodiment provides an ultrasonic imaging system, including an ultrasonic probe, a transceiver control circuit, a processor, and a display;

[0057] The ultrasonic probe is used to emit ultrasonic waves to a target tissue and receive echo signals of the ultrasonic waves; the transceiver control circuit is used to control the ultrasonic probe to perform the emission of ultrasonic waves and the reception of echo signals of the ultrasonic waves; the processor is used to process the echo signals to generate an ultrasonic image; the display is used to display the ultrasonic image;

[0058] The processor is further used to execute the method described in any of the embodiments herein.

[0059] Based on the ultrasonic imaging method and ultrasonic imaging system of the heart according to the above embodiments, for the problem that the physiological movement of the heart itself poses challenges to elastography, first, an ultrasonic image of the heart is obtained through imaging, and then the myocardium is identified from the ultrasonic image and the position of the myocardium (such as the myocardial segment to be observed) is tracked to obtain the real-time position of the myocardium. On this basis, elastography is performed; further, considering that the heart has chamber structures such as the atrium and ventricle that will affect the propagation of shear waves, acoustic radiation force is applied to the myocardium to be observed (such as its geometric center or center of gravity) based on the real-time position of the myocardium to generate shear waves, thereby ensuring the effectiveness of shear wave generation and sufficient signal-to-noise ratio. Description of the Drawings

[0060] Figure 1Schematic structural diagram of an ultrasonic imaging system according to an embodiment;

[0061] Figure 2 Schematic display diagram of identifying each myocardial muscle included in the heart in an ultrasonic image according to an embodiment;

[0062] Figure 3 Example of superimposing a color elasticity image on an ultrasonic image according to an embodiment;

[0063] Figure 4 Example of superimposing a color elasticity image on an ultrasonic image according to an embodiment;

[0064] Figure 5 Flowchart of an ultrasonic imaging method for the heart according to an embodiment;

[0065] Figure 6 Flowchart of an ultrasonic imaging method for the heart according to an embodiment. Detailed implementation manners

[0066] The present invention will be further described in detail below in conjunction with the accompanying drawings through specific implementation manners. Similar elements in different implementation manners adopt related similar element numbers. In the following implementation manners, 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 to avoid submerging the core part of the present application in 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 general technical knowledge in the art.

[0067] In addition, the features, operations, or characteristics described in the specification can be combined in any appropriate manner to form various implementation manners. 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 drawings are only for clearly describing a certain embodiment and do not mean a necessary sequence unless it is stated that a certain sequence must be followed.

[0068] 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 meaning. And the "connection" and "coupling" mentioned in the present application, unless otherwise specified, both include direct and indirect connection (coupling).

[0069] Current medical ultrasonic elastography techniques mainly include two types: pressure elastography and shear wave elastography. Pressure elastography has been developed for the longest time and has the most mature technology, but it has relatively high requirements for the operator's technique. Pressure elastography mainly generates a certain deformation by pressing the tissue with a probe. The probe emits ultrasonic waves and receives echo information to calculate and image parameters related to tissue elasticity such as the strain amount and strain rate of the tissue, so as to reflect the elastic differences between different tissues. Since strain parameters such as the strain amount and strain rate are very sensitive to pressure, in the pressure elastography technique, the pressure applied to the tissue by the probe needs to be kept as uniform and stable as possible, which poses relatively high requirements for the operator's technique. The shear wave elastography technique mainly generates shear waves inside the tissue by means of acoustic radiation and detects or calculates its propagation parameters (such as propagation speed). Since the elasticity degree (or softness and hardness degree) of the tissue affects the propagation parameters of the shear wave, the propagation parameters of the shear wave can reflect the elastic differences (or softness and hardness degree) of the tissue, that is, the detected propagation parameters can be used for elastography. Since it no longer depends on the operator to apply specific pressure to the tissue like pressure elastography, the shear wave elastography has made great progress in terms of stability and repeatability.

[0070] Due to the physiological movement of the heart itself, that is, the heart continuously contracts and relaxes, the target tissue to be observed in the heart (such as a certain segment of myocardium) will also move together, which brings challenges to elastography; in addition, due to the chamber structures such as the atrium and ventricle in the heart, if these chamber structures happen to be located in the propagation path of the shear wave from the wave source to the target tissue to be observed, the shear wave will be greatly attenuated, and even when the shear wave propagates to the target tissue to be observed, it no longer has the observation conditions. Considering these problems, the applicant proposes an elastography scheme based on ultrasonic technology for the heart. For the problem that the physiological movement of the heart itself brings challenges to elastography, first, an ultrasonic image of the heart is obtained, and then the myocardium is identified from the ultrasonic image and the position of the myocardium (such as the myocardium segment to be observed) is tracked to obtain the real-time position of the myocardium. On this basis, elastography is carried out. And in order to further reduce the influence of the diastolic and systolic of the heart on elastography, the time point suitable for elastography can be determined based on the cardiac cycle formed by the diastolic and systolic of the heart; further, considering that the chamber structures such as the atrium and ventricle in the heart will affect the propagation of the shear wave, acoustic radiation force is applied to the myocardium to be observed (such as its geometric center or center of gravity) based on the real-time position of the myocardium to generate a shear wave, so as to ensure the effectiveness of shear wave generation and sufficient signal-to-noise ratio. The following is a specific description.

[0071] Please refer to Figure 1, the ultrasonic imaging system 100 of some embodiments includes an ultrasonic probe 10, a transceiver control circuit 20, a processor 30, and a display 40. Each component will be described below.

[0072] In some embodiments, the ultrasonic probe 10 is configured to transmit ultrasonic waves and receive echo signals of the ultrasonic waves (i.e., ultrasonic echoes or ultrasonic echo signals). In some specific embodiments, the ultrasonic probe 10 includes a plurality of array elements, which are used to realize the mutual conversion between electrical pulse signals and ultrasonic waves, so as to transmit ultrasonic waves to a target tissue (such as a tissue containing the heart) and receive the ultrasonic echoes reflected by the tissue, so as to obtain the echo signals of the ultrasonic waves. In some embodiments, the plurality of array elements included in the ultrasonic probe 10 can be arranged in a row to form a linear array. In some embodiments, the plurality of array elements included in the ultrasonic probe 10 are arranged in a two-dimensional matrix to form a planar array. The array elements are, for example, piezoelectric crystals, which convert electrical signals into ultrasonic signals according to the transmission sequence transmitted by the transceiver control circuit 20. According to the application, the transmitted ultrasonic waves (ultrasonic signals) may 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 signals include focused waves, plane waves, and divergent waves. The array elements are used to transmit ultrasonic waves according to the excitation electrical signals, or convert the received ultrasonic waves into electrical signals. Therefore, each array element can be used to realize the mutual conversion between electrical pulse signals and ultrasonic waves, so as to transmit ultrasonic waves to the target tissue and can also be used to receive the echo signals of the ultrasonic waves reflected by the tissue. During ultrasonic detection, the transceiver control circuit 20 can be used to control which array elements are used to transmit ultrasonic beams (transmitting array elements), which array elements are used to receive ultrasonic beams (receiving array elements), or control the array elements to be used for transmitting ultrasonic waves or receiving the echo signals of ultrasonic waves in time slots. The array elements participating in the transmission of ultrasonic waves can be simultaneously excited by electrical signals, so as to transmit ultrasonic waves simultaneously; or the array elements participating in the transmission of ultrasonic waves can also be excited by a plurality of electrical signals with a certain time interval, so as to continuously transmit ultrasonic waves with a certain time interval. If the smallest processing area for receiving and reflecting ultrasonic waves in the target tissue is called the position point in the tissue, then after the ultrasonic waves reach each position point in the target tissue, different reflections will occur due to the different acoustic impedances of the tissues at different position points. The reflected ultrasonic waves are picked up by the receiving array elements, and each receiving array element may receive the ultrasonic echoes (ultrasonic echoes) from multiple position points. The ultrasonic echoes from different position points received by each receiving array element form different channel echo data. For a certain receiving array element, the distances from it to different position points in the target tissue are different. Therefore, the arrival times of the ultrasonic echoes reflected by each position point at this array element are also different. The corresponding relationship between the ultrasonic echoes and the position points can be identified according to the arrival time of the ultrasonic echoes at this array element.

[0073] The transceiver control circuit 20 is used to control the ultrasonic probe 10 to perform the transmission of ultrasonic waves and the reception of ultrasonic echoes. For example, on the one hand, the transceiver control circuit 20 is used to control the ultrasonic probe 10 to transmit ultrasonic waves to the target tissue, and on the other hand, it is used to control the ultrasonic probe 10 to receive the ultrasonic echoes reflected by the tissue. In some specific embodiments, the transceiver control circuit 20 is used to generate a transmission sequence and a reception sequence, and output them to the ultrasonic probe 10. The transmission sequence is used to control some or all of the multiple array elements in the ultrasonic probe 10 to transmit ultrasonic waves to the target tissue. The parameters of the transmission sequence include the number of array elements for transmission and ultrasonic wave transmission parameters (such as pulse amplitude, transmission voltage, transmission frequency, number of wave transmissions, transmission interval, transmission angle, transmission waveform, transmission aperture, line density, dot density, and / or focal position, etc.). The reception sequence is used to control some or all of the multiple array elements to receive the echoes of ultrasonic waves after passing through the tissue. The parameters of the reception sequence include the number of array elements for reception and the echo reception parameters (such as reception angle, depth, etc.). Depending on the different uses of the ultrasonic echoes or the different images generated based on the ultrasonic echoes, the ultrasonic parameters in the transmission sequence and the echo parameters in the reception sequence are also different.

[0074] The processor 30 is used to process the ultrasonic echo signal received by the ultrasonic probe 10 (i.e., the echo signal of the ultrasonic wave), for example, perform one or more processes on the echo signal / channel echo data of the ultrasonic wave, such as analog-to-digital conversion, signal demodulation, amplification, filtering, downsampling, beam synthesis, modulus extraction, logarithmic compression, and / or grayscale transformation, etc. By processing the ultrasonic echo signal, the processor 30 can finally obtain an ultrasonic image for display on the display 40. The processor 30 in some embodiments includes, but is not limited to, a central processing unit (CPU), a microcontroller unit (MCU), a field-programmable gate array (FPGA), and a digital signal processing (DSP), etc., which are devices used to interpret computer instructions and process data in computer software. In some embodiments, the processor 30 is used to execute each computer application program in the non-transitory computer-readable storage medium, thereby implementing the corresponding method.

[0075] The display 40 can be used to display information, such as the parameters and images calculated by the processor 30, etc. Those skilled in the art should understand that in some embodiments, the ultrasonic imaging system itself may not integrate a display module, but connect to a computer device (such as a computer), and display information through the display module (such as a display screen) of the computer device.

[0076] The above is some description of the ultrasonic imaging system 100.

[0077] There are multiple methods to generate shear waves in a target area (such as the target myocardium mentioned in this text). For example, a special pulse (such as an acoustic radiation force impulse, ARFI) is emitted from an ultrasonic probe 10 to the target area to generate shear waves in the target area. When generating shear waves in the target area by acoustic radiation force impulses, the acoustic radiation force impulses can be focused or non-focused. Specifically, when the acoustic radiation force impulses are strongly focused, the wave sources of the generated shear waves are more concentrated; when weakly focused, the generation range of the shear waves is wider. And within the generation range of the shear waves, it can be approximately regarded that multiple shear wave point sources propagate from multiple starting points; in addition, the range can also be broadened by directly generating shear waves at multiple different positions. Taking acoustic radiation force impulses as an example, by emitting acoustic radiation force impulses multiple times and focusing on different regions respectively, the propagation of shear waves starting from different positions can be generated.

[0078] This application proposes one or more elastography modes for ultrasonic imaging of the heart, especially elastography, such as any one, any two, or all three of the first elastography mode, the second elastography mode, and the third elastography mode mentioned in this text. The following will be described in combination with the imaging process.

[0079] (I) Ultrasonic imaging of the heart

[0080] In some embodiments, the processor 30 controls the transceiver control circuit 20 to perform real-time ultrasonic scanning of the target tissue containing the heart through the ultrasonic probe 10 to obtain an ultrasonic image of the heart, and the processor 30 controls the display 40 to display the ultrasonic image in the first area in real time; for example, the ultrasonic probe 10 performs real-time ultrasonic wave emission and echo signal reception on the target tissue containing the heart, the processor 30 generates an ultrasonic image of the heart based on the echo signal, and the display 40 displays the real-time ultrasonic image in the first area. In some examples, the ultrasonic image can be a B image.

[0081] (II) Identification of section types

[0082] In some embodiments, the processor 30 identifies the section type of the displayed ultrasonic image based on a preset section type identification model, obtains the section type identification result, and controls the display 40 to display the section type identification result in the first area.

[0083] The section types of the ultrasonic images of the heart include, for example, but are not limited to, the parasternal long-axis section type, the parasternal short-axis section type, the apical long-axis section type, the apical short-axis section type, etc. Ultrasonic images of different section types of the heart can observe the organizational structure of the heart from different section angles.

[0084] The section type recognition model can be constructed based on traditional section type recognition algorithms. For example, for the ultrasonic image to be recognized, the image features in the image are extracted. The image features can be anatomical structure features in the ultrasonic image, and then the section type of the ultrasonic image is judged based on the image features. The section type recognition model mentioned in this article can also be an artificial intelligence model, such as an artificial intelligence model constructed by using an artificial neural network. The artificial intelligence model is trained by constructing a training set. The samples in the training set are ultrasonic images of the heart, and the labels of the samples can be the section types manually marked.

[0085] (III) Recognition and tracking of myocardium

[0086] The processor 30 judges whether the currently displayed ultrasonic image meets the requirements according to the section type recognition result. For example, it judges whether the currently displayed ultrasonic image belongs to the expected section type. If it meets the requirements, the processor 30 recognizes each myocardium included in the currently displayed ultrasonic image of the heart based on a preset myocardium recognition model and marks it in the ultrasonic image. In some examples, the processor 30 recognizes the myocardium corresponding to the section type of the currently displayed ultrasonic image of the heart based on a preset myocardium recognition model.

[0087] The myocardial segments of the heart are usually defined according to the segment division of the left ventricular myocardium. This division helps doctors accurately identify and evaluate different parts of the heart in echocardiography or other imaging techniques. There are multiple models for the segment division of the left ventricular myocardium, and the most commonly used ones are the 16-segment model and the 17-segment model. For example, taking the 16-segment model as an example, it divides the left ventricular myocardium into three myocardial rings, namely the basal ring, the middle ring, and the apical ring. The height of each ring is 1 / 3 of the left ventricular length. The basal ring includes the basal segment of the anterior wall, the basal segment of the anterior septum, the basal segment of the inferior septum, the basal segment of the inferior wall, the basal segment of the inferior lateral wall, and the basal segment of the anterior lateral wall, a total of 6 segments (or types of myocardium). The middle ring includes the middle segment of the anterior wall, the middle segment of the anterior septum, the middle segment of the inferior septum, the middle segment of the inferior wall, the middle segment of the inferior lateral wall, and the middle segment of the anterior lateral wall, also 6 segments (or types of myocardium). The apical ring includes the apical segment of the anterior wall, the apical segment of the septum, the apical segment of the inferior wall, and the apical segment of the lateral wall, a total of 4 segments (or types of myocardium).

[0088] The myocardium recognition model can be constructed based on traditional recognition algorithms. For example, for the ultrasonic image to be recognized, it is segmented to extract the features representing the tissue structure in the image, so as to realize the recognition of the myocardium. The myocardium recognition model mentioned in this article can also be an artificial intelligence model, such as an artificial intelligence model constructed by using an artificial neural network. The artificial intelligence model is trained by constructing a training set. The samples in the training set are ultrasonic images of the heart, and the labels of the samples can be the positions, types, etc. of the myocardium manually marked.

[0089] As the ultrasound image displayed in the first region is updated, the processor 30 performs position tracking on the identified myocardium. There are various ways for the processor 30 to implement the position tracking of the myocardium. For example, the processor 30 can use the speckle tracking technique based on the B-image to achieve it. The speckle tracking technique based on the B-image is to track the position of the same ultrasound speckle in the B-image, so as to determine the position change relationship of the corresponding myocardium. When the movement displacement and deformation of the tissue corresponding to the myocardium are small, it can be approximately considered that the speckle pattern of the tissue remains fixed. Therefore, the movement tracking of the specific tissue can be achieved by tracking the movement of the specific speckle in the B-mode ultrasound image.

[0090] In some embodiments, the processor 30 controls the display 40 to mark the identified myocardium in the ultrasound image. For example, the processor 30 marks and displays the shape and position of the identified myocardium in the currently displayed ultrasound image by superimposing a contour marking. It can be understood that as the ultrasound image displayed in the first region is updated, as described above, the processor 30 will also perform position tracking on the identified myocardium. Therefore, it can also update the contour marking superimposed on the ultrasound image based on the position tracking result.

[0091] (IV) Determining the target myocardium

[0092] In some embodiments, the processor 30 determines the target myocardium, which is the myocardium to be subjected to elastography. The following describes how to determine the target myocardium.

[0093] In some embodiments, the processor 30 displays a sectional view diagram corresponding to the sectional type of the ultrasound image in the first region according to the sectional type recognition result, and marks the myocardium corresponding to the sectional type on the sectional view diagram; in response to a selection instruction for the myocardium marked on the sectional view diagram, the processor 30 determines the selected myocardium as the target myocardium.

[0094] In some embodiments, in response to a selection instruction for the myocardium on the ultrasound image, the processor 30 determines the selected myocardium as the target myocardium.

[0095] In some embodiments, the processor 30 generates elastic region options and controls the display 40 to display the generated elastic region options, where the elastic region options include at least two of an upper region option, a lower region option, a left region option, a right region option, and an all-region option; in response to a user's selection instruction for the elastic region options, the processor 30 determines the myocardium associated with the selected elastic region as the target myocardium; wherein the myocardium associated with the upper region option is the myocardium in the upper region of the ultrasonic image of the current section type, the myocardium associated with the lower region option is the myocardium in the lower region of the ultrasonic image of the current section type, the myocardium associated with the left region option is the myocardium in the left region of the ultrasonic image of the current section type, the myocardium associated with the right region option is the myocardium in the right region of the ultrasonic image of the current section type, and the myocardium associated with the all-region option is the myocardium in the all-region of the ultrasonic image of the current section type. It can be understood that for the division of the upper region, lower region, left region, and right region of the ultrasonic image, a center point can be first determined in the ultrasonic image, and then a parallel line can be made based on the center point to divide the upper region and the lower region, and a vertical line can be made based on the center point to divide the left region and the right region.

[0096] The target myocardium can be one or more, which is determined based on the user's imaging requirements.

[0097] (5) Perform elastography on the target myocardium

[0098] This application proposes one or more elastography modes for ultrasonic imaging of the heart, especially elastography.

[0099] In some embodiments, in the first elastography mode: the processor 30 controls the ultrasonic probe 10 to apply acoustic radiation force to the target myocardium at multiple moments that meet the conditions according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times; the processor 30 observes the shear waves generated each time through the ultrasonic probe 10 to perform shear wave imaging on the target myocardium and generate a color elastogram of the target myocardium.

[0100] In the first elastography mode, the acoustic radiation force is applied to the target myocardium through the real-time position of the target myocardium, which can greatly reduce the influence of the movement of the heart itself on the target myocardium during elastography. At the same time, selecting multiple moments that meet the conditions for elastography further reduces the influence of the contraction and relaxation of the heart itself on the target myocardium during elastography.

[0101] In the above elastic imaging mode, there are also moments that meet the conditions. In some embodiments, multiple moments that meet the conditions include: the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart. An implementation process can be as follows: The processor 30 acquires the real-time cardiac cycle phase of the heart, for example, acquires the first type of physiological signal of the heart, and the first type of physiological signal includes an electrocardiogram signal and / or a heart sound signal; the processor 30 identifies the cardiac cycle phase according to the phase recognition model, so as to determine multiple moments that meet the conditions, such as the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart, etc.

[0102] In addition, in some embodiments, these moments that meet the conditions are related to the cardiac cycle phase, and elastic imaging can be performed at least twice within one cardiac cycle.

[0103] In some embodiments, multiple moments that meet the conditions under the first elastic imaging include: the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart.

[0104] In some embodiments, in the first elastic imaging mode, the processor 30 also marks the trigger position of the shear wave on the sectional schematic diagram to prompt the user.

[0105] In some embodiments, in the second elastic imaging mode: at multiple moments that meet the conditions, the processor 30 performs ultrasonic observation on the shear wave generated by the spontaneous physiological phenomenon of the heart at the real-time position of the target myocardium at the corresponding moment through the ultrasonic probe 10, so as to perform shear wave imaging on the target myocardium and generate a color elastic image of the target myocardium.

[0106] In the second elastic imaging mode, selecting multiple moments that meet the conditions for elastic imaging can reduce the influence of the contraction and relaxation of the heart itself on the target myocardium during elastic imaging; at the same time, instead of generating shear waves based on acoustic radiation force, shear waves generated by the spontaneous physiological phenomenon of the heart are utilized, so that the ultrasonic probe 10 does not have to spend time and power applying acoustic radiation force to the target myocardium, but can focus on emitting ultrasonic waves for observing shear waves to the target myocardium and receiving the corresponding echo signals based on the real-time position of the target myocardium, achieving targeted observation.

[0107] In the second elastic imaging mode and the third elastic imaging mode in this article, shear waves generated by the spontaneous physiological phenomenon of the heart are mentioned. Such spontaneous physiological phenomena of the heart are, for example, valve closure, atrial contraction, etc. Taking valve closure as an example, it can be understood that elastic imaging of the myocardium near the valve is relatively accurate. Therefore, this elastic imaging mode can be adopted when the target myocardium is the myocardium near the valve.

[0108] In the above elastography modes, there are also moments that meet the conditions. In some embodiments, multiple moments that meet the conditions include: the mitral valve closing moment and the aortic valve closing moment. An implementation process can be as follows: The processor 30 obtains the real-time cardiac cycle phase of the heart, for example, obtains the first type of physiological signal of the heart, and the first type of physiological signal includes an electrocardiogram signal and / or a heart sound signal; the processor 30 identifies the cardiac cycle phase according to the phase recognition model, thereby determining multiple moments that meet the conditions, such as the mitral valve closing moment and the aortic valve closing moment, etc.

[0109] In addition, in some embodiments, these moments that meet the conditions are related to the cardiac cycle phase, and elastography can be performed at least twice within one cardiac cycle.

[0110] In some embodiments, multiple moments that meet the conditions under the second elastography include: the mitral valve closing moment and the aortic valve closing moment.

[0111] In some embodiments, under the second elastography mode: The processor 30 also marks the mechanism and / or position of the shear wave generated by the spontaneous physiological phenomenon of the heart on the sectional schematic diagram to prompt the user.

[0112] In some embodiments, under the third elastography mode: The processor 30 controls the ultrasound probe 10 to apply acoustic radiation force to the target myocardium at multiple moments that meet the conditions to generate shear waves multiple times according to the real-time position of the target myocardium at the corresponding moments; the processor 30 observes the shear waves generated each time through the ultrasound probe 10 to perform shear wave imaging on the target myocardium and generate the first color elastogram of the target myocardium; and, the processor 30 observes the shear waves generated by the spontaneous physiological phenomenon of the heart through the ultrasound probe 10 at the real-time position of the target myocardium at multiple moments that meet the conditions to perform shear wave imaging on the target myocardium and generate the second color elastogram of the target myocardium; the processor 30 generates the color elastogram of the target myocardium based on the first color elastogram and the second color elastogram of the target myocardium.

[0113] It can be seen that the third elastography mode is essentially a hybrid elastography that combines the first elastography mode and the second elastography mode. Since the first elastography mode and the second elastography mode are respectively elastographies based on shear waves generated for different reasons, they are essentially used to qualitatively or quantitatively evaluate the elastic parameters of the target myocardium from two different perspectives. Therefore, the final color elastogram can be obtained by performing weighted calculation based on the color elastograms generated by the two. When performing the weighted calculation, the weight coefficient can vary according to the type of the target myocardium.

[0114] In some embodiments, the multiple moments that meet the conditions and involve applying acoustic radiation force in the third elastography mode include: the moment corresponding to the end-diastolic phase of the heart and the moment corresponding to the end-systolic phase of the heart.

[0115] In some embodiments, the multiple moments that meet the conditions and involve ultrasonic observation of shear waves generated by the spontaneous physiological phenomena of the heart through the ultrasonic probe 10 include: the mitral valve closing moment and the aortic valve closing moment.

[0116] In any of the above elastography modes, after generating the color elastogram of the target myocardium, the processor 30 superimposes and displays the color elastogram of the target myocardium on the ultrasonic image. When the generated color elastogram is updated, the displayed color elastogram is also updated accordingly.

[0117] In addition, the processor 30 can also calculate the shear wave velocity, elasticity value, etc. of the target myocardium by performing ultrasonic observation on the shear wave; it also supports local measurement and statistical analysis (such as mean, maximum / minimum value, standard deviation, etc.) of the elastography region after the ultrasonic image is frozen.

[0118] In any of the above elastography modes, after performing elastography based on the current elastography mode under an ultrasonic image of a certain section type, another section type to be scanned next can be determined based on the target myocardium, and elastography on the target myocardium can continue based on the previous elastography mode under the ultrasonic image of this other section type. This is because ultrasonic images of different section types can observe the myocardium from different angles. Therefore, this application also considers observing the shear waves of the myocardium from different angles to obtain more information about the elastic parameters of the myocardium.

[0119] Therefore, in some embodiments, after performing elastography based on the current elastography mode when the ultrasonic image is of the first section type - the ultrasonic image of the first section type can be the ultrasonic image that meets the requirements mentioned in this article; the processor 30 also determines the second section type to be scanned next based on the target myocardium and prompts the user to move or rotate the ultrasonic probe 10; as the ultrasonic probe moves, when the displayed ultrasonic image is recognized as the second section type based on the section type recognition model, the processor 30 generates information for prompting the user to stop the movement of the ultrasonic probe; and when the ultrasonic image is of the second section type, the processor 30 controls the performance of elastography based on the current elastography mode (that is, the elastography mode when performing elastography in the case where the ultrasonic image was of the first section type before).

[0120] In addition, multiple cross-section types can be pre-associated with the target myocardium. After scanning one cross-section type, the next cross-section type can be scanned continuously until all the cross-section types associated with the valves of the target myocardium are scanned. In some embodiments, when ultrasonic images of each cross-section type of the target myocardium are obtained, elastography is performed based on the same elastography mode. In some embodiments, when ultrasonic images of each cross-section type of the target myocardium are obtained, the elastography mode can also be re-selected or determined based on the cross-section type of the ultrasonic image, which will be continued to be mentioned below.

[0121] In some embodiments including multiple elastography modes, the user can manually select the current elastography mode.

[0122] In some embodiments including multiple elastography modes, the processor 30 can also automatically determine the current elastography mode.

[0123] Different types of myocardium are suitable for different elastography modes, and the elastography modes corresponding to each type of myocardium can be preset. When the product is implemented, all elastography modes can be performed on each type of myocardium. For the same type of myocardium (i.e., the same segment of myocardium), the color elastography images obtained under various elastographies are compared to determine the elastography mode matched by this type of myocardium. When comparing the color elastography images of the myocardium obtained under various elastographies, the image quality of these color elastography images can be calculated. The image quality can include but is not limited to sharpness, contrast, signal-to-noise ratio, etc. The elastography mode corresponding to the color elastography image with the best image quality is determined as the elastography mode matched by this type of myocardium.

[0124] Therefore, in some embodiments, after the target myocardium is determined, the processor 30 selects an elastography mode matched by the type of the target myocardium from multiple elastography modes as the current elastography mode.

[0125] In addition, ultrasonic images of different cross-section types can observe the organizational structure of the heart from different angles. Therefore, different cross-section types of ultrasonic images also respectively correspond to the types of myocardium that can be better observed on their images. Therefore, the elastography mode is also determined based on the cross-section type of the ultrasonic image. In some embodiments, the processor 30 selects an elastography mode matched by the cross-section type of the current ultrasonic image from multiple elastography modes as the current elastography mode.

[0126] It should be noted that this article mentions generating shear waves based on acoustic radiation force for elastography and using shear waves generated by spontaneous physiological phenomena of the heart for elastography. Although the methods or principles of generating shear waves are different, the method of observing shear waves with ultrasonic waves through the ultrasonic probe 10 can be the same or different. This application does not limit this, and in the implementation process, the existing method of observing shear waves with ultrasonic waves can be directly adopted.

[0127] Figure 2 As an example of identifying each myocardial muscle contained in the heart in the ultrasonic image and marking it in the ultrasonic image, a contour shape mark with a yellow dotted line is superimposed on the ultrasonic image to mark and display the myocardial muscle; a sectional view schematic diagram is displayed in the upper left corner of the ultrasonic image, where PLAX indicates that the sectional type is the parasternal long-axis section; in addition, a physiological signal of a section of the heart is displayed below the ultrasonic image.

[0128] Figure 3 and Figure 4 Two examples of superimposing a color elastogram on the ultrasonic image are shown, where ES represents the moment of aortic closure and ED represents the moment of mitral valve closure.

[0129] Please refer to Figure 5 , in some embodiments, an ultrasonic imaging method 101 for the heart is also disclosed, including the following steps:

[0130] Step 110: Perform real-time scanning and imaging on a target tissue containing the heart.

[0131] In some embodiments, in step 110, the ultrasonic probe 10 performs real-time ultrasonic scanning on the target tissue containing the heart to obtain an ultrasonic image of the heart, and the ultrasonic image is displayed in real time in the first area. In some examples, the ultrasonic image can be a B image.

[0132] Step 120: Identify the sectional type of the ultrasonic image.

[0133] In some embodiments, in step 120, based on a preset sectional type recognition model, the displayed ultrasonic image is recognized for the sectional type to obtain a sectional type recognition result, and the display 40 is controlled to display the sectional type recognition result in the first area.

[0134] The section type recognition model can be constructed based on traditional section type recognition algorithms. For example, for the ultrasonic image to be recognized, image features in the image are extracted. The image features can be anatomical structure features in the ultrasonic image, and then the section type of the ultrasonic image is determined based on the image features. The section type recognition model mentioned in this article can also be an artificial intelligence model, such as an artificial intelligence model constructed using an artificial neural network. The artificial intelligence model is trained by constructing a training set. The samples in the training set are ultrasonic images of the heart, and the labels of the samples can be the manually annotated section types.

[0135] Step 130: Identify the myocardium in the ultrasonic image.

[0136] In some embodiments, step 130 determines whether the currently displayed ultrasonic image meets the requirements according to the section type recognition result. For example, it is determined whether the currently displayed ultrasonic image belongs to the expected section type. If it meets the requirements, each myocardium included in the heart in the currently displayed ultrasonic image is identified based on a preset myocardium recognition model and marked in the ultrasonic image. In some examples, step 130 identifies the myocardium corresponding to the section type of the currently displayed ultrasonic image in the heart in the currently displayed ultrasonic image based on a preset myocardium recognition model.

[0137] The myocardium recognition model can be constructed based on traditional recognition algorithms. For example, for the ultrasonic image to be recognized, the features representing the tissue structure in the image are segmented to achieve the recognition of the myocardium. The myocardium recognition model mentioned in this article can also be an artificial intelligence model, such as an artificial intelligence model constructed using an artificial neural network. The artificial intelligence model is trained by constructing a training set. The samples in the training set are ultrasonic images of the heart, and the labels of the samples can be the manually annotated positions, types, etc. of the myocardium.

[0138] Step 140: Track the positions of the myocardium recognized in the ultrasonic image.

[0139] In some embodiments, as the ultrasonic image displayed in the first region is updated, step 140: Track the positions of the recognized myocardium. There are various ways to achieve the position tracking of the myocardium in step 140. For example, step 140: can be implemented using the speckle tracking technique based on the B-image. The speckle tracking technique based on the B-image is to track the position of the same ultrasonic speckle in the B-image to determine the position change relationship of the corresponding myocardium. When the movement displacement and deformation of the tissue corresponding to the myocardium are small, it can be approximately considered that the speckle pattern of the tissue remains fixed. Therefore, the movement tracking of the specific tissue can be achieved by tracking the movement of the specific speckle in the B-mode ultrasound image.

[0140] In some embodiments, in step 140, the identified myocardium is marked in the ultrasound image. For example, the processor 30 marks and displays the shape and position of the identified myocardium in the currently displayed ultrasound image by superimposing a contour shape marker. It can be understood that as the ultrasound image displayed in the first region is updated, as described above, step 140 also performs position tracking on the identified myocardium. Therefore, the contour shape marker superimposed on the ultrasound image can also be updated based on the position tracking result.

[0141] Step 150: Determine the target myocardium.

[0142] The target myocardium is the myocardium to be subjected to elastography. The method for determining the target myocardium will be described below.

[0143] In some embodiments, in step 150, according to the cross-section type recognition result, a cross-section schematic diagram corresponding to the cross-section type of the ultrasound image is displayed in the first region, and the myocardium corresponding to the cross-section type is marked on the cross-section schematic diagram; in response to a selection instruction for the myocardium marked on the cross-section schematic diagram, step 150 determines the selected myocardium as the target myocardium.

[0144] In some embodiments, in response to a selection instruction for the myocardium on the ultrasound image, step 150 determines the selected myocardium as the target myocardium.

[0145] In some embodiments, step 150 generates and displays an elastography region option, and the elastography region option includes at least two of an upper region option, a lower region option, a left region option, a right region option, and an all-region option; in response to a selection instruction from the user for the elastography region option, the myocardium associated with the selected elastography region is determined as the target myocardium; wherein the myocardium associated with the upper region option is the myocardium in the upper region of the ultrasound image of the current cross-section type, the myocardium associated with the lower region option is the myocardium in the lower region of the ultrasound image of the current cross-section type, the myocardium associated with the left region option is the myocardium in the left region of the ultrasound image of the current cross-section type, the myocardium associated with the right region option is the myocardium in the right region of the ultrasound image of the current cross-section type, and the myocardium associated with the all-region option is the myocardium in the entire region of the ultrasound image of the current cross-section type.

[0146] The target myocardium can be one or more, which is determined based on the imaging requirements of the user.

[0147] Step 160: Perform elastography on the target myocardium.

[0148] The present application proposes one or more elastography modes for cardiac ultrasound imaging, especially elastography.

[0149] In some embodiments, in the first elastography mode: Step 160 controls the ultrasound probe 10 to apply acoustic radiation force to the target myocardium at multiple moments that meet the conditions according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times; Step 160 performs ultrasonic observation on each generated shear wave through the ultrasound probe 10 to perform shear wave imaging on the target myocardium and generate a color elastogram of the target myocardium.

[0150] In the first elastography mode, the acoustic radiation force is applied to the target myocardium based on the real-time position of the target myocardium, which can greatly reduce the influence of the heart's own movement on the target myocardium during elastography. At the same time, selecting multiple moments that meet the conditions for elastography further reduces the influence of the heart's own contraction and relaxation on the target myocardium during elastography.

[0151] In the above elastography mode, it also involves moments that meet the conditions. In some embodiments, the multiple moments that meet the conditions include: the moments corresponding to the end-diastolic phase of the heart and the moments corresponding to the end-systolic phase of the heart. One implementation process can be: The processor 30 obtains the real-time cardiac cycle phase of the heart, for example, obtains the first type of physiological signal of the heart, and the first type of physiological signal includes an electrocardiogram signal and / or a heart sound signal; the processor 30 identifies the cardiac cycle phase according to the phase recognition model to determine the multiple moments that meet the conditions, such as the moments corresponding to the end-diastolic phase of the heart and the moments corresponding to the end-systolic phase of the heart, etc.

[0152] In addition, in some embodiments, these moments that meet the conditions are related to the cardiac cycle phase, and elastography can be performed at least twice within one cardiac cycle.

[0153] In some embodiments, the multiple moments that meet the conditions in the first elastography include: the moments corresponding to the end-diastolic phase of the heart and the moments corresponding to the end-systolic phase of the heart.

[0154] In some embodiments, in the first elastography mode, Step 160 also marks the trigger position of the shear wave on the sectional schematic diagram to prompt the user.

[0155] In some embodiments, in the second elastography mode: Step 160 performs ultrasonic observation on the shear waves generated by the spontaneous physiological phenomena of the heart at the real-time positions of the target myocardium at multiple moments that meet the conditions through the ultrasound probe 10 to perform shear wave imaging on the target myocardium and generate a color elastogram of the target myocardium.

[0156] In the second elastography mode, multiple moments that meet the conditions are selected for elastography, which can reduce the influence of the contraction and relaxation of the heart itself on the target myocardium during elastography. At the same time, instead of generating shear waves based on acoustic radiation force, shear waves generated by the spontaneous physiological phenomena of the heart are utilized. As a result, the ultrasonic probe 10 does not need to spend time and power applying acoustic radiation force to the target myocardium, but can focus on emitting ultrasonic waves for observing shear waves and receiving corresponding echo signals based on the real-time position of the target myocardium, achieving targeted observation.

[0157] In the second and third elastography modes described in this article, shear waves generated by the spontaneous physiological phenomena of the heart are mentioned. Such spontaneous physiological phenomena of the heart are, for example, valve closure, atrial contraction, etc. Taking valve closure as an example, it can be understood that elastography of the myocardium near the valve is relatively accurate. Therefore, this elastography mode can be adopted when the target myocardium is the myocardium near the valve.

[0158] In the above elastography mode, moments that meet the conditions are also involved. In some embodiments, the multiple moments that meet the conditions include: the mitral valve closure moment and the aortic valve closure moment. An implementation process can be: Step 160 obtains the real-time cardiac cycle phase of the heart, for example, obtains the first type of physiological signals of the heart, and the first type of physiological signals includes electrocardiogram signals and / or heart sound signals; the processor 30 identifies the cardiac cycle phase according to the phase recognition model, thereby determining the multiple moments that meet the conditions, such as the mitral valve closure moment and the aortic valve closure moment, etc.

[0159] In addition, in some embodiments, these moments that meet the conditions are related to the cardiac cycle phase, and elastography can be performed at least twice within one cardiac cycle.

[0160] In some embodiments, the multiple moments that meet the conditions in the second elastography include: the mitral valve closure moment and the aortic valve closure moment.

[0161] In some embodiments, in the second elastography mode: Step 160 also marks the mechanism and / or position of the shear wave generated by the spontaneous physiological phenomena of the heart on the sectional schematic diagram to prompt the user.

[0162] In some embodiments, in the third elastography mode: Step 160 controls the ultrasound probe 10 to apply acoustic radiation force to the target myocardium at multiple moments that meet the conditions according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times; Step 160 performs ultrasonic observation on the shear waves generated each time through the ultrasound probe 10 to perform shear wave imaging on the target myocardium and generate a first color elastogram of the target myocardium; and, Step 160 performs ultrasonic observation on the shear waves generated by the spontaneous physiological phenomena of the heart at the real-time position of the target myocardium at multiple moments that meet the conditions through the ultrasound probe 10 to perform shear wave imaging on the target myocardium and generate a second color elastogram of the target myocardium; The processor 30 generates a color elastogram of the target myocardium based on the first color elastogram and the second color elastogram of the target myocardium.

[0163] It can be seen that the third elastography mode is essentially a hybrid elastography that combines the first elastography mode and the second elastography mode. Since the first elastography mode and the second elastography mode are respectively elastographies based on shear waves generated for different reasons, they are essentially evaluating the elastic parameters of the target myocardium qualitatively or quantitatively from two different perspectives. Therefore, the final color elastogram can be obtained by performing weighted calculation based on the color elastograms generated by the two. When performing the weighted calculation, the weight coefficient can vary with the type of the target myocardium.

[0164] In some embodiments, the multiple moments that meet the conditions for applying acoustic radiation force in the third elastography mode include: the moments corresponding to the end-diastolic phase of the heart and the moments corresponding to the end-systolic phase of the heart.

[0165] In some embodiments, the multiple moments that meet the conditions for performing ultrasonic observation on the shear waves generated by the spontaneous physiological phenomena of the heart through the ultrasound probe 10 include: the moment when the mitral valve closes and the moment when the aortic valve closes.

[0166] In any of the above elastography modes, after generating the color elastogram of the target myocardium, Step 160 superimposes and displays the color elastogram of the target myocardium on the ultrasound image. When the generated color elastogram is updated, the displayed color elastogram is also updated accordingly.

[0167] In any of the above elastography modes, after elastography is performed based on the current elastography mode under an ultrasonic image of a certain section type, another section type to be scanned next can be determined based on the target myocardium, and elastography of the target myocardium can continue to be performed based on the previous elastography mode under the ultrasonic image of this other section type. This is because ultrasonic images of different section types can observe the myocardium from different angles. Therefore, this application also considers observing the shear wave of the myocardium from different angles to obtain more information about the elastic parameters of the myocardium.

[0168] Therefore, in some embodiments, after elastography is performed based on the current elastography mode when the ultrasonic image is of the first section type - the ultrasonic image of the first section type can be the ultrasonic image meeting the requirements mentioned in this article; step 160 also determines the second section type to be scanned next based on the target myocardium and prompts the user to move or rotate the ultrasonic probe 10; as the ultrasonic probe moves, when the displayed ultrasonic image is recognized as the second section type based on the section type recognition model, step 160 generates information for prompting the user to stop the movement of the ultrasonic probe; and when the ultrasonic image is of the second section type, step 160 controls elastography to be performed based on the current elastography mode (that is, the elastography mode when elastography was performed in the case where the ultrasonic image was of the first section type before).

[0169] In addition, multiple section types can be pre-associated with the target myocardium. After scanning one section type, the next section type is scanned continuously until all section types associated with the target myocardium are scanned; in some embodiments, when ultrasonic images of each section type of the target myocardium are obtained, elastography is performed based on the same elastography mode; in some embodiments, when ultrasonic images of each section type of the target myocardium are obtained, the elastography mode can also be reselected or determined based on the section type of the ultrasonic image, which will be continued to be mentioned below.

[0170] In some embodiments including multiple elastography modes, the user can manually select the current elastography mode.

[0171] In some embodiments including multiple elastography modes, the current elastography mode can also be automatically determined. Therefore, please refer to Figure 6, the ultrasonic imaging method 101 of the heart in some embodiments further includes step 170: automatically selecting the current elastography mode. For example, after determining the target myocardium, step 170 selects an elastography mode that matches the type of the target myocardium from a variety of elastography modes as the current elastography mode according to the type of the target myocardium; for another example, step 170 selects an elastography mode that matches the section type of the current ultrasonic image from a variety of elastography modes as the current elastography mode according to the section type recognition result. After determining the current elastography mode in step 170, step 160 performs elastography on the target myocardium based on the determined elastography mode.

[0172] This document is 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 of this document. For example, various operating steps and the components used to perform the operating steps can be implemented in different ways according to a specific 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).

[0173] In the above embodiments, it can be implemented in whole or in part by software, hardware, firmware, or any combination thereof. Additionally, as understood by those skilled in the art, the principles herein can be reflected in a computer program product on a computer-readable storage medium that is preloaded with 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, Blue Ray disks, etc.), flash memory, and / or the like. These computer program instructions can be loaded onto a general-purpose computer, a special-purpose computer, or other programmable data processing devices to form a machine, such that the instructions executed on the computer or other programmable data processing devices can generate a device that implements 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 devices to operate in a specific manner, so that the instructions stored in the computer-readable memory can form a manufactured article, including the implementation device that implements the specified functions. The computer program instructions can also be loaded onto the computer or other programmable data processing devices, thereby performing a series of operating steps on the computer or other programmable devices to generate a computer-implemented process, such that the instructions executed on the computer or other programmable devices can provide the steps for implementing the specified functions.

[0174] While the principles of the present disclosure have been shown in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components, which 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.

[0175] The foregoing detailed description has been described 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, the 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 any element that makes them more explicit, should not be construed as critical, required, or essential. As used herein, the term "comprising" and any other variant 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 variant thereof as used herein refers to a physical connection, an electrical connection, a magnetic connection, an optical connection, a communication connection, a functional connection, and / or any other connection.

[0176] 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. Thus, the scope of the present invention should be determined solely by the claims.

Claims

1. A method for ultrasonic imaging of the heart, characterized in that: include: Performing a real-time ultrasonic scan on a target tissue including a heart by using an ultrasonic probe to obtain an ultrasonic image of the heart, and displaying the ultrasonic image in real time in the first area; Identify the section type of the displayed ultrasound image based on a preset section type identification model to obtain a section type identification result, and display the section type identification result in the first area; Determine whether the currently displayed ultrasound image meets the requirements according to the section type recognition result; if so, identify each myocardium contained in the currently displayed ultrasound image based on a preset myocardium recognition model and mark it in the ultrasound image; As the ultrasound image displayed in the first area is updated, the position of the identified myocardium is tracked; Identify the target myocardium; In the first elastic imaging mode: at multiple moments when conditions are met, the ultrasonic probe is controlled to apply acoustic radiation force to the target myocardium according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times; the shear waves generated each time are ultrasonically observed by the ultrasonic probe to perform shear wave imaging on the target myocardium, and a color elastic image of the target myocardium is generated; In the second elastic imaging mode: at a plurality of moments satisfying the conditions, ultrasonic observation is performed on the shear waves generated by the spontaneous physiological phenomenon of the heart at the real-time position of the target myocardium at the corresponding moments by means of an ultrasonic probe, so as to perform shear wave imaging on the target myocardium and generate a color elastic image of the target myocardium; The color elastic image of the target myocardium is superimposed and displayed on the ultrasound image, and when the generated color elastic image is updated, the displayed color elastic image is also updated accordingly.

2. The method for ultrasonic cardiac imaging according to claim 1, wherein: Also included is a third elastic imaging mode, in which: At multiple moments when the conditions are met, the ultrasound probe is controlled to apply acoustic radiation force to the target myocardium according to the real-time position of the target myocardium at the corresponding moments to generate shear waves multiple times; the shear waves generated each time are ultrasonically observed by the ultrasound probe to perform shear wave imaging of the target myocardium, thereby generating a first color elastic image of the target myocardium; At multiple moments when the conditions are met, ultrasonic observation is performed on the shear waves generated by the spontaneous physiological phenomenon of the heart at the real-time position of the target myocardium at the corresponding moments by using an ultrasonic probe to perform shear wave imaging on the target myocardium and generate a second color elastic image of the target myocardium; A color elasticity image of the target myocardium is generated based on the first color elasticity image and the second color elasticity image of the target myocardium.

3. The cardiac ultrasonic imaging method according to claim 1 or 2, characterized in that: Also includes: After determining the target myocardium, selecting an elastic imaging mode that matches the type of the target myocardium from a plurality of elastic imaging modes as the current elastic imaging mode according to the type of the target myocardium; and / or, An elastic imaging mode that matches the slice type of the current ultrasound image is selected from a plurality of elastic imaging modes according to the slice type recognition result as the current elastic imaging mode.

4. The method for ultrasonic cardiac imaging according to claim 1 or 2, characterized in that: The step of judging whether the currently displayed ultrasound image meets the requirements according to the section type recognition result includes: judging whether the currently displayed ultrasound image is of the first section type according to the section type recognition result, and if so, the image meets the requirements; After performing elastic imaging based on the current elastic imaging mode when the ultrasound image is of the first section type, the second section type to be scanned next is determined based on the target myocardium, and the user is prompted to move or rotate the ultrasound probe; as the ultrasound probe moves, when the displayed ultrasound image is identified as the second section type based on the section type recognition model, the user is prompted to stop the movement of the ultrasound probe; and elastic imaging is performed based on the current elastic imaging mode when the ultrasound image is of the second section type.

5. The cardiac ultrasonic imaging method according to claim 1 or 2, characterized in that: The step of determining the target myocardium comprises: Displaying a section schematic diagram corresponding to the section type of the ultrasound image in the first region according to the section type recognition result, and marking the myocardium corresponding to the section type on the section schematic diagram; In response to an instruction to select a myocardium marked on the schematic cross-sectional view, the selected myocardium is determined as a target myocardium.

6. The method for ultrasonic cardiac imaging according to claim 5, wherein: In the first elastic imaging mode: the triggering position of the shear wave is also marked on the cut-plane diagram; in the second elastic imaging mode: the mechanism and / or position of the shear wave generated by the spontaneous physiological phenomenon of the heart is also marked on the cut-plane diagram.

7. The cardiac ultrasonic imaging method according to claim 1 or 2, characterized in that: The multiple moments satisfying the conditions include: a moment corresponding to the end of cardiac diastole and a moment corresponding to the end of cardiac systole; or a mitral valve closure moment and aorta closure moment.

8. A method for ultrasonic imaging of the heart, characterized in that: include: Performing a real-time ultrasonic scan on a target tissue including a heart by using an ultrasonic probe to obtain an ultrasonic image of the heart, and displaying the ultrasonic image in real time in the first area; Identify the section type of the displayed ultrasound image based on a preset section type identification model to obtain a section type identification result, and display the section type identification result in the first area; Determining whether the currently displayed ultrasound image is of the first section type according to the section type recognition result, and if so, identifying the myocardium corresponding to the section type of the ultrasound image contained in the currently displayed ultrasound image based on a preset myocardial recognition model, and marking and displaying the shape and position of the identified myocardium in the currently displayed ultrasound image by superimposing a contour shape mark; As the ultrasound image displayed in the first area is updated, the position of the identified myocardium is tracked, and the contour shape mark superimposed on the ultrasound image is updated based on the position tracking result; Displaying a first section schematic diagram corresponding to a first section type in the first region, and marking the myocardium corresponding to the first section type on the first section schematic diagram; In response to a selection instruction for the myocardium marked on the first section schematic diagram, determining a target myocardium; In the case where the ultrasound image is of the first section type: obtaining the real-time cardiac phase of the heart, controlling the ultrasound probe to apply acoustic radiation force to the target myocardium according to the real-time position of the target myocardium at the corresponding time to generate shear waves multiple times, and the corresponding time is the time corresponding to multiple cardiac phases that meet the conditions in each cardiac cycle; Determine a second section type to be scanned next based on the target myocardium, and prompt the user to move or rotate the ultrasound probe; as the ultrasound probe moves, when the displayed ultrasound image is identified as the second section type based on the section type recognition model, prompt the user to stop moving the ultrasound probe; In the case where the ultrasound image is of the second section type: identifying the target myocardium from the ultrasound image, and tracking the position of the identified target myocardium as the ultrasound image displayed in the first area is updated; acquiring the real-time cardiac phase of the heart, and controlling the ultrasound probe to apply acoustic radiation force to the target myocardium according to the real-time position of the target myocardium at the corresponding moment to generate shear waves multiple times, wherein the corresponding moment is the moment corresponding to multiple cardiac phases that meet the conditions in each cardiac cycle; Performing ultrasonic observation on the shear wave generated each time by using an ultrasonic probe to perform shear wave imaging on the target myocardium and generate a color elastic image of the target myocardium; The color elastic image of the target myocardium is superimposed and displayed on the ultrasound image, and when the generated color elastic image is updated, the displayed color elastic image is also updated accordingly.

9. The method for ultrasonic cardiac imaging according to claim 8, wherein: The method of acquiring the real-time cardiac phase of the heart includes: acquiring a first type of physiological signal of the heart; the first type of physiological signal includes an electrocardiogram signal and / or a heart sound signal; and obtaining the cardiac phase according to a phase recognition model.

10. The cardiac ultrasonic imaging method according to claim 8 or 9, characterized in that: The plurality of cardiac phases satisfying the conditions include: a cardiac phase corresponding to the end of cardiac diastole and a cardiac phase corresponding to the end of cardiac systole.

11. A method for ultrasonic imaging of the heart, characterized in that: include: Performing a real-time ultrasonic scan on a target tissue including a heart by using an ultrasonic probe to obtain an ultrasonic image of the heart, and displaying the ultrasonic image in real time in the first area; Identify the section type of the displayed ultrasound image based on a preset section type identification model to obtain a section type identification result, and display the section type identification result in the first area; Determine whether the currently displayed ultrasound image meets the requirements according to the section type recognition result; if so, identify each myocardium contained in the currently displayed ultrasound image based on a preset myocardium recognition model and mark it in the ultrasound image; As the ultrasound image displayed in the first area is updated, the position of the identified myocardium is tracked; Identify the target myocardium; At multiple moments when the conditions are met, according to the real-time position of the target myocardium at the corresponding moments, the ultrasonic probe is controlled to apply acoustic radiation force to the target myocardium to generate shear waves multiple times; Performing ultrasonic observation on the shear wave generated each time by using an ultrasonic probe to perform shear wave imaging on the target myocardium and generate a color elastic image of the target myocardium; The color elastic image of the target myocardium is superimposed and displayed on the ultrasound image, and when the generated color elastic image is updated, the displayed color elastic image is also updated accordingly.

12. The method for ultrasonic cardiac imaging according to claim 11, wherein: Determining the target myocardium includes at least one of the following: Displaying a section schematic diagram corresponding to the section type of the ultrasound image in the first region according to the section type recognition result, and marking the myocardium corresponding to the section type on the section schematic diagram; In response to a selection instruction for a myocardium marked on the cross-sectional schematic diagram, determining the selected myocardium as a target myocardium; In response to an instruction to select a myocardium on the ultrasound image, determining the selected myocardium as a target myocardium; generating and displaying elastic region options, wherein the elastic region options include at least two of an upper region option, a lower region option, a left region option, a right region option, and an all region option; in response to a user's selection instruction for the elastic region option, determining the myocardium associated with the selected elastic region as a target myocardium; The myocardium associated with the upper area option is the myocardium in the upper area of ​​the ultrasound image of the current section type, the myocardium associated with the lower area option is the myocardium in the lower area of ​​the ultrasound image of the current section type, the myocardium associated with the left area option is the myocardium in the left area of ​​the ultrasound image of the current section type, the myocardium associated with the right area option is the myocardium in the right area of ​​the ultrasound image of the current section type, and the myocardium associated with the all area option is the myocardium in all areas of the ultrasound image of the current section type.

13. The cardiac ultrasound imaging method according to claim 11, characterized in that: The multiple moments satisfying the conditions include: a moment corresponding to the end of cardiac diastole and a moment corresponding to the end of cardiac systole.

14. An ultrasonic imaging system, characterized in that: It includes an ultrasound probe, a transceiver control circuit, a processor and a display; The ultrasonic probe is used to transmit ultrasonic waves to the target tissue and receive echo signals of the ultrasonic waves; the transceiver control circuit is used to control the ultrasonic probe to transmit ultrasonic waves and receive echo signals of ultrasonic waves; the processor is used to process the echo signals to generate ultrasonic images; and the display is used to display the ultrasonic images; The processor is further configured to execute the method for ultrasonic imaging of the heart as claimed in any one of claims 1 to 13.

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