Tissue ultrasonic imaging system and method and tissue mechanical property parameter measuring method

Abstract

The invention provides a tissue ultrasonic imaging system and method and a tissue mechanical property measuring method. The method comprises the steps that a waveform signal corresponding to mechanical movement of target tissue is obtained; determining an initial signal segment of which the waveform is matched with a standard waveform corresponding to a preset physiological event in the waveform signal; when the initial signal segment meets the condition about the signal credibility, the ultrasonic probe is controlled to conduct ultrasonic imaging on the target tissue at the moment. According to the method, a characteristic waveform signal generated by mechanical movement of a target tissue is captured in real time, an ultrasonic probe is triggered to collect ultrasonic imaging data of the target tissue when the characteristic waveform signal meets a credibility condition, it is ensured that the collection time of ultrasonic imaging is synchronous with the time phase generated by spontaneous mechanical waves of the target tissue, and the time sequence deviation problem is avoided; more reliable tissue mechanical property data are provided for clinic; in addition, collection is triggered only when conditions are met, redundant storage of invalid data is avoided, and the system load is reduced.

Description

Technical Field

[0001] The present invention relates to the field of medical imaging, and in particular to a tissue ultrasonic imaging system and method, and a tissue mechanical characteristic parameter measurement method. Background Art

[0002] In the field of biological tissue mechanical property assessment, cardiovascular tissue mechanical property parameters (such as stiffness) have been found to be associated with various cardiovascular diseases, such as myocardial hypertrophy, hypertension, and myocardial fibrosis. Existing technologies typically use a continuous acquisition mode to acquire tissue mechanical property data to cover the dynamic changes of the target tissue.

[0003] However, while this continuous acquisition mode can record the complete cycle of tissue activity, due to the temporal nature of physiological motion, the data of actual diagnostic value is often concentrated only within the brief time window triggered by specific physiological events, such as critical phases such as valve closure or additional blood pumping due to atrial contraction. This continuous acquisition method can result in the generation of a large amount of redundant data, which not only increases the load on the storage system and the computational burden of subsequent data processing, but also causes key signals that truly reflect the mechanical properties of tissues to be submerged in the massive data, affecting the efficiency and accuracy of subsequent analysis and reducing overall work efficiency.

[0004] Therefore, how to effectively reduce the generation of redundant data and lower the storage load while ensuring the accuracy of tissue mechanics data has become a technical problem that needs to be solved urgently in this field. Summary of the Invention

[0005] One of the purposes of the present invention is to provide a tissue ultrasound imaging method to solve the technical problem that the existing technology continuously collects tissue ultrasound imaging data during the physiological activity cycle, which easily generates a large amount of redundant data and has a large storage load.

[0006] In order to achieve one of the above-mentioned purposes of the invention, the present invention provides a tissue ultrasound imaging method, including: obtaining a waveform signal corresponding to the mechanical movement of the target tissue; determining an initial signal segment in the waveform signal whose waveform matches the standard waveform corresponding to a preset physiological event; when the initial signal segment meets the conditions regarding signal credibility, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment.

[0007] As a further improvement of one embodiment of the present invention, the obtaining of the waveform signal corresponding to the mechanical movement of the target tissue includes: simultaneously obtaining the waveform signals of the electrocardiogram, the valve pulse Doppler spectrum and the tissue dynamic strain rate curve; the determining of the initial signal segment in which the waveform in the waveform signal matches the standard waveform corresponding to the preset physiological event includes: comparing the waveform signal of the electrocardiogram with the first standard waveform corresponding to the first physiological event, comparing the waveform signal of the valve pulse Doppler spectrum with the second standard waveform corresponding to the second physiological event, and comparing the dynamic strain rate curve of the tissue with the third standard waveform corresponding to the third physiological event; determining the waveform signal that meets any one of the first physiological event, the second physiological event and the third physiological event as the initial signal segment.

[0008] As a further improvement of an embodiment of the present invention, when the initial signal segment meets the conditions regarding signal credibility, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment includes: obtaining a standard waveform of a preset physiological event matching the corresponding initial signal segment; when the waveform similarity between the standard waveform and the initial signal segment is greater than a preset threshold, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at the moment corresponding to the initial signal segment.

[0009] As a further improvement of an embodiment of the present invention, obtaining a waveform signal corresponding to the mechanical movement of the target tissue includes: obtaining an electrocardiogram; determining an initial signal segment in which the waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: determining a positive waveform with the largest amplitude within a physiological activity cycle based on the waveform signal of the electrocardiogram; when the waveform similarity between the positive waveform and the first standard waveform meets a first threshold, determining that the signal segment containing the positive waveform is the initial signal segment corresponding to the first physiological event.

[0010] As a further improvement of an embodiment of the present invention, before the initial signal segment meets the conditions regarding signal credibility, the method further includes: based on the first standard waveform, determining a corresponding first score according to at least one of the amplitude, duration and waveform steepness of the initial signal segment corresponding to the first physiological event; when the initial signal segment meets the conditions regarding signal credibility, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment, including: when the first score is greater than the first standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at the moment corresponding to the initial signal segment.

[0011] As a further improvement of one embodiment of the present invention, obtaining a waveform signal corresponding to the mechanical movement of the target tissue includes: obtaining a valve pulse Doppler spectrum; determining an initial signal segment in which the waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: determining a spectral artifact based on the valve pulse Doppler spectrum; and when the waveform similarity between the spectral artifact and the second standard waveform meets a second threshold, determining that the signal segment containing the spectral artifact is the initial signal segment corresponding to the second physiological event.

[0012] As a further improvement of an embodiment of the present invention, before the initial signal segment meets the conditions regarding signal credibility, the method further includes: based on a second standard waveform, determining a corresponding second score according to at least one of the brightness information and the duration of the initial signal segment corresponding to the second physiological event; when the initial signal segment meets the conditions regarding signal credibility, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment, including: when the second score is greater than the second standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at the moment corresponding to the initial signal segment.

[0013] As a further improvement of one embodiment of the present invention, obtaining a waveform signal corresponding to the mechanical movement of the target tissue includes: obtaining a dynamic strain rate curve of the tissue; determining the initial signal segment in which the waveform in the waveform signal matches the standard waveform corresponding to a preset physiological event includes: determining the strain rate peak of the preset stage based on the dynamic strain rate curve of the tissue; when the waveform similarity between the strain rate peak of the preset stage and the third standard waveform meets a third threshold, determining that the signal segment containing the strain rate peak of the preset stage is the initial signal segment corresponding to the third physiological event.

[0014] As a further improvement of an embodiment of the present invention, before the initial signal segment meets the conditions regarding signal credibility, the method also includes: based on a third standard waveform, determining a corresponding third score according to at least one of the amplitude of the initial signal segment corresponding to the third physiological event and the previous strain rate valley value; when the initial signal segment meets the conditions regarding signal credibility, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment, including: when the third score is greater than the third standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at the moment corresponding to the initial signal segment.

[0015] As a further improvement of one embodiment of the present invention, obtaining a waveform signal corresponding to the mechanical movement of the target tissue includes: obtaining an electrocardiogram, and comparing the waveform signal of the electrocardiogram with the standard waveforms corresponding to the first physiological event, the second physiological event, and the third physiological event at the same time; and determining that the waveform signal that meets any one of the first physiological event, the second physiological event, and the third physiological event is the initial signal segment.

[0016] As a further improvement of one embodiment of the present invention, the method also includes: obtaining a valve pulse Doppler spectrum, comparing the waveform signal of the valve pulse Doppler spectrum with a standard waveform corresponding to a second physiological event; when the waveform signals of the electrocardiogram and the valve pulse Doppler spectrum both meet the standard waveform corresponding to the second physiological event, determining that the waveform signal of the valve pulse Doppler spectrum is the initial waveform.

[0017] As a further improvement of one embodiment of the present invention, the method also includes: obtaining a tissue dynamic strain rate curve, comparing the waveform signal of the tissue dynamic strain rate curve with a standard waveform corresponding to a third physiological event; when the waveform signals of the electrocardiogram and the tissue dynamic strain rate curve both meet the standard waveform corresponding to the third physiological event, determining that the waveform signal of the tissue dynamic strain rate curve is the initial waveform.

[0018] As a further improvement of one embodiment of the present invention, the control of the ultrasonic probe to perform ultrasonic imaging of the target tissue at this moment includes: controlling the ultrasonic probe to transmit ultrasonic signals to the target tissue and receive echo signals according to a preset acquisition sequence; the preset acquisition sequence includes at least one of diffuse waves and focused waves; and performing ultrasonic imaging of the target tissue according to the echo signals.

[0019] In order to achieve one of the above-mentioned purposes of the invention, the present invention also provides a method for measuring tissue mechanical characteristic parameters based on ultrasonic imaging, including: executing the tissue ultrasonic imaging method to determine the target tissue ultrasonic image; performing mechanical wave imaging analysis on the target tissue ultrasonic image to determine the propagation speed of the mechanical waves generated by the mechanical movement of the target tissue in the target area; and determining the corresponding mechanical characteristic parameters of the target tissue based on the propagation speed.

[0020] As a further improvement of an embodiment of the present invention, the target tissue ultrasound image includes N frames of images to be detected; the mechanical wave imaging analysis of the target tissue ultrasound image to determine the propagation speed of the mechanical wave generated by the mechanical movement of the target tissue within the target area includes: determining a reference object within the target area; determining the propagation speed of the mechanical wave within the target area based on N time information and M position information when the mechanical wave in the N frames of images to be detected reaches the reference object, where N and M are both integers, N>0, M>0.

[0021] As a further improvement of an embodiment of the present invention, the method of determining the propagation speed of the mechanical wave in the target area based on the N time information and M position information when the mechanical wave reaches the reference object in N frames of images to be detected includes: recording the time information of the mechanical wave arriving at different pixel points of the reference object, and fitting the time information using a surface fitting method to generate an isochrone map; determining the velocity components of each pixel point in the first direction and the second direction based on the distance relationship between the isochrone map and the pixel points; and determining the propagation speed of the mechanical wave in the target area based on the velocity components.

[0022] As a further improvement of one embodiment of the present invention, the method also includes: determining a first mechanical characteristic parameter of a first detection object to obtain a first blood pressure of the first detection object; determining a second mechanical characteristic parameter of a second detection object to obtain a second blood pressure of the second detection object; converting the first blood pressure and the second blood pressure into a first tissue stress and a second tissue stress, respectively, and standardizing the first mechanical characteristic parameter and the second mechanical characteristic parameter using the first tissue stress and the second tissue stress, respectively; when the standardized first mechanical characteristic parameter is greater than the standardized second mechanical characteristic parameter, the tissue intrinsic hardness of the first detection object is higher than the tissue intrinsic hardness of the second detection object.

[0023] In order to achieve one of the above-mentioned purposes of the invention, the present invention also provides a tissue ultrasound imaging system, including: an input module for obtaining a waveform signal corresponding to the mechanical movement of the target tissue; a processing module for determining an initial signal segment in the waveform signal whose waveform matches the standard waveform corresponding to a preset physiological event; and an imaging module for controlling the ultrasound probe to perform ultrasound imaging of the target tissue at that moment when the initial signal segment meets the conditions regarding signal credibility.

[0024] As a further improvement of one embodiment of the present invention, the system also includes: a first measurement module, used to perform mechanical wave imaging analysis on the target tissue ultrasound image generated by the imaging module to determine the propagation speed of the mechanical wave in the target area; and used to determine the mechanical characteristic parameters of the corresponding target tissue based on the propagation speed.

[0025] Compared with the prior art, the embodiments of the present invention have at least one of the following beneficial effects: The present invention adopts a tissue ultrasound imaging method, which captures and analyzes the characteristic waveform signal generated by the mechanical movement of the target tissue in real time, and triggers the ultrasound probe to collect the target tissue ultrasound imaging data when the characteristic waveform signal meets the credibility condition, ensuring that the acquisition time of the target tissue ultrasound imaging is synchronized with the phase generated by the spontaneous mechanical wave of the target tissue, avoiding the problem of timing deviation, and providing more reliable tissue mechanical property data for clinical use; in addition, the acquisition is triggered only when the conditions are met, avoiding the redundant storage of invalid data and reducing the system load. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 FIG. 1 is a schematic structural diagram of a tissue ultrasound imaging system according to an embodiment of the present invention.

[0027] Figure 2 1 is a schematic diagram of the steps of a tissue ultrasound imaging method according to one embodiment of the present invention.

[0028] Figure 3 1 is a schematic diagram of step S1 and step S2 in one embodiment of the present invention.

[0029] FIG4( a ) is a schematic diagram of step S1 and step S2 in one embodiment of the present invention.

[0030] FIG4( b ) is a schematic diagram of step S1 and step S2 in another embodiment of the present invention.

[0031] FIG4( c ) is a schematic diagram of step S1 and step S2 in yet another embodiment of the present invention.

[0032] FIG5( a ) is a schematic diagram of an electrocardiogram waveform according to an embodiment of the present invention.

[0033] FIG5( b ) is a waveform diagram of a pulsed Doppler spectrum of a valve in one embodiment of the present invention.

[0034] FIG5( c ) is a waveform diagram of a dynamic strain rate curve of tissue according to an embodiment of the present invention.

[0035] FIG5( d ) is a schematic diagram of the structure of an acquisition sequence in one embodiment of the present invention.

[0036] Figure 6 FIG. 1 is a schematic diagram of step S1 in an embodiment of the present invention.

[0037] FIG. 7( a ) is a schematic diagram of the timing of mechanical waves generated by mechanical motion of target tissue in one embodiment of the present invention.

[0038] FIG7( b ) is a schematic diagram of isochronal lines of the dynamic propagation of mechanical waves in the target area according to an embodiment of the present invention.

[0039] Figure 8 3 is a schematic diagram of step S3 in one embodiment of the present invention.

[0040] FIG9( a ) is a schematic diagram of a process for marking the credibility of different signal sources according to an embodiment of the present invention.

[0041] FIG9( b ) is a schematic diagram of a process for marking the credibility of different signal sources in another embodiment of the present invention.

[0042] Figure 10 1 is a schematic diagram of the steps of a method for determining tissue mechanical characteristic parameters based on ultrasound imaging in one embodiment of the present invention.

[0043] Figure 11 1 is a schematic diagram of the steps of a method for determining tissue mechanical characteristic parameters based on ultrasound imaging in one embodiment of the present invention.

[0044] FIG12( a ) is a schematic diagram showing mechanical characteristic parameters and blood pressure load in one embodiment of the present invention.

[0045] FIG12( b ) is a schematic diagram showing the display of mechanical characteristic parameters after tissue stress normalization in one embodiment of the present invention.

[0046] FIG12( c ) is a schematic diagram showing a mechanical characteristic parameter-blood pressure cycle curve according to an embodiment of the present invention.

[0047] FIG12( d ) is a schematic diagram showing a mechanical characteristic parameter-blood pressure closed-loop curve according to an embodiment of the present invention.

[0048] Figure 13 It is a flow chart of a tissue ultrasound imaging method in a preferred embodiment of the present invention. DETAILED DESCRIPTION

[0049] The present invention will be described in detail below with reference to the specific embodiments shown in the accompanying drawings. However, these embodiments do not limit the present invention, and any structural, methodological, or functional changes made by those skilled in the art based on these embodiments are all within the scope of protection of the present invention.

[0050] It should be noted that the term "comprises" or any other variant thereof is intended to cover non-exclusive inclusion, so that a process, method, article or apparatus that includes a list of elements includes not only those elements but also other elements not explicitly listed, or elements inherent to such process, method, article or apparatus. In addition, the terms "first," "second," "third," "fourth," "fifth," etc. are used for descriptive purposes only and are not to be understood as indicating or implying relative importance.

[0051] like Figure 1 As shown, a tissue ultrasound imaging system 100 is provided in one embodiment of the present invention.

[0052] The tissue ultrasound imaging system 100 is a medical imaging technology used to evaluate the mechanical properties (such as elasticity, hardness, etc.) of target tissue. By measuring the response of the target tissue under force or strain, it provides quantitative information about the function, structure and pathological changes of the target tissue for clinical diagnosis.

[0053] The tissue ultrasound imaging system 100 includes an input module 11. The input module 11 is used to obtain a waveform signal corresponding to the mechanical motion of the target tissue.

[0054] The input module 11 is used to obtain the original waveform signal of the mechanical movement of the target tissue in real time, such as ultrasound echo signal, electrocardiogram signal, heart sound signal, etc.

[0055] The tissue ultrasound imaging system 100 includes a processing module 12 .

[0056] In one embodiment, the processing module 12 is configured to determine an initial signal segment in the waveform signal whose waveform matches a standard waveform corresponding to a preset physiological event.

[0057] Specifically, the standard waveform corresponding to the spontaneous event of the target tissue (such as characteristic phases such as extra pumping of blood by atrial contraction and valve closure) is identified from the waveform signal for comparison to identify the matching initial signal segment.

[0058] In this embodiment, a pattern recognition algorithm may be used to achieve waveform matching, determine credible target tissue activity periods, and preliminarily exclude invalid signals caused by noise, such as respiratory motion artifacts.

[0059] The tissue ultrasound imaging system 100 includes an imaging module 13 .

[0060] The imaging module 13 is configured to control the ultrasound probe to perform ultrasound imaging of the target tissue at a moment when the initial signal segment meets the conditions regarding signal credibility.

[0061] The imaging module 13 checks whether the initial signal segment meets the preset signal quality conditions (such as signal-to-noise ratio, waveform consistency, etc.); if so, it controls the ultrasound probe to emit ultrasound imaging pulses at a precise moment and collects motion echo data generated by the spontaneous mechanical wave propagation of the target tissue. The tissue hardness (such as elastic modulus) is calculated based on the motion echo data to make a health assessment.

[0062] The tissue ultrasound imaging system 100 achieves precise ultrasound imaging of target tissue through the collaborative work of the input module 11, the processing module 12, and the imaging module 13. Specifically, the system acquires the original waveform signal of the mechanical motion of the target tissue, which is determined based on ultrasound echoes, electrocardiograms, or other motion sensors.

[0063] Input module 11 transmits the raw waveform signal to processing module 12, which compares the input waveform signal with a preset standard physiological event waveform and uses a pattern matching algorithm to filter out initial signal segments that match the waveform. This step eliminates invalid signals caused by respiratory interference, noise, or other artifacts, ensuring the accuracy of subsequent analysis.

[0064] Once the initial signal segment is confirmed to meet preset credibility criteria, such as signal-to-noise ratio and waveform consistency, the imaging module 13 is activated. This module precisely controls the ultrasound probe to emit ultrasound waves for tissue imaging, while simultaneously collecting dynamic deformation response data of the target tissue. Based on this response data, it generates an ultrasound image of the target tissue for clinical assessment of pathological features such as myocardial lesions and fibrosis.

[0065] In one embodiment, the tissue ultrasound imaging system 100 further includes a first measurement module 14 .

[0066] On the one hand, the first measurement module 14 is used to perform mechanical wave imaging analysis on the target tissue ultrasound image generated by the imaging module 13 to determine the propagation speed of the mechanical wave in the target area.

[0067] On the other hand, the first measurement module 14 is configured to determine the mechanical characteristic parameters of the corresponding target tissue according to the propagation velocity.

[0068] In one embodiment, the tissue ultrasound imaging system 100 further includes a second measurement module 15. The second measurement module 15 is configured to measure the blood pressure of a target tissue (e.g., heart or artery) at different times; or the second measurement module 15 is configured to measure the blood pressure of target tissues (e.g., heart or artery) of different subjects.

[0069] In one embodiment, the tissue ultrasound imaging system 100 further includes a display module 16 . The display module 16 is configured to receive and display the mechanical characteristic parameters of the target tissue determined by the first measurement module 14 and the blood pressure measurement result obtained by the second measurement module 15 .

[0070] In this way, through the coupling analysis of physiological parameters, it helps doctors determine whether the change in the hardness of the target tissue is related to the blood pressure load, thereby providing effective reference information for precise diagnosis and treatment.

[0071] In one embodiment of the present invention, a method for tissue ultrasound imaging is provided.

[0072] The tissue ultrasonic imaging method can be applied to a tissue ultrasonic imaging system to determine the time when the ultrasonic imaging system collects mechanical property data of the target tissue.

[0073] In one embodiment, the tissue ultrasound imaging system can be as follows Figure 1 The above configuration is carried out, and the corresponding technical solution is set to be referenced in the imaging method provided by the present invention. Of course, the tissue ultrasound imaging system used in the tissue ultrasound imaging method provided by the present invention is not limited to this configuration structure.

[0074] like Figure 2 As shown, the tissue ultrasound imaging method provided by the present invention includes but is not limited to the following steps.

[0075] Step S1, obtaining a waveform signal corresponding to the mechanical motion of the target tissue; Step S2, determining an initial signal segment in the waveform signal whose waveform matches a standard waveform corresponding to a preset physiological event; Step S3: When the initial signal segment meets the signal credibility condition, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at this moment.

[0076] In this way, by capturing and analyzing the characteristic waveform signal generated by the mechanical movement of the target tissue in real time, and triggering the ultrasound probe to collect the target tissue imaging data when the characteristic waveform signal meets the credibility condition, it is ensured that the acquisition time of the target tissue ultrasound imaging is synchronized with the phase generated by the spontaneous mechanical wave of the target tissue, avoiding the timing deviation problem and providing more reliable tissue mechanical property data for clinical use; in addition, the acquisition is triggered only when the conditions are met to avoid redundant storage of invalid data and reduce the system load.

[0077] In step S1, the target tissue refers to the body tissue part that is observed and analyzed using ultrasound technology to obtain specific information for research or diagnostic purposes. Mechanical motion refers to the mechanical movement of the specific tissue being studied, such as positional movement, morphological change, or rotation, caused by physiological activities or external factors.

[0078] In one embodiment, the target tissue is the heart.

[0079] For example, when the target tissue is the heart, the corresponding mechanical motion is the physical deformation and displacement produced during the heart's contraction and relaxation during a cardiac cycle. A cardiac cycle is the period from the start of one heartbeat to the start of the next, i.e., the complete contraction (systole) and relaxation (diastole) of the heart.

[0080] Specifically, during systole, the aortic valve opens and closes, allowing the ventricles to eject blood; during diastole, the mitral valve opens and closes, allowing the ventricles to fill. Ultrasound imaging requires precisely capturing specific moments in the cardiac cycle (such as aortic valve closure) to analyze changes in myocardial stiffness.

[0081] Waveform signals refer to the time-amplitude curves recorded by medical sensors, which characterize the different dimensions of target tissue activity. Waveform signals are easy to obtain and process.

[0082] In one embodiment, the waveform signal comprises at least one of an electrocardiogram (ECG), a valve pulsed Doppler spectrum, and a tissue dynamic strain rate curve.

[0083] The valve pulsed Doppler spectrum, obtained using Doppler technology, shows the temporal variation of valve-related blood flow signals. It can reflect characteristics such as blood flow velocity and direction at the valve. The dynamic tissue strain rate curve, recorded using specific technology, shows the temporal variation of tissue strain rate during dynamic processes. It can reflect dynamic characteristics such as tissue deformation rate. Both can be used to assess relevant physiological or pathological conditions.

[0084] In a specific embodiment, when the target tissue is the heart, the corresponding valve pulsed Doppler spectrum may be an aortic valve Doppler spectrum diagram, and the corresponding tissue dynamic strain rate curve may be a myocardial strain rate curve.

[0085] In this embodiment, the electrocardiogram indirectly reflects the mechanical state of the heart through the timing of electrical activity, which is derived from the heart's electrical activity. For example, the R wave in the electrocardiogram is generated by ventricular depolarization. The aortic valve Doppler spectrum is used to measure the temporal changes in blood flow velocity and direction within the cardiac cavity near the aortic valve, which is derived from the changes in blood flow during the cardiac cycle. The myocardial strain rate curve is used to record the instantaneous rate of myocardial deformation, which is derived from the myocardial deformation during the cardiac cycle.

[0086] In step S2, a preset physiological event refers to a pre-defined event with specific physiological significance that generates a recognizable characteristic signal. For example, when the target tissue is the heart, the corresponding preset physiological event is a preset cardiac event, which refers to a critical mechanical motion moment within the cardiac cycle that triggers the acquisition of ultrasound imaging data for the corresponding target tissue.

[0087] In a specific embodiment, the preset physiological events include a first physiological event, a second physiological event, and a third physiological event.

[0088] When the target tissue is a heart, the corresponding preset cardiac event includes at least one of mitral valve closure, aortic valve closure, and extra pumping of blood by atrial contraction.

[0089] A cardiac event is a specific physiological event, and the initial signal segment refers to the portion of the waveform signal that is extracted and associated with the predefined cardiac event. For example, the R wave signal in an ECG graph is associated with the cardiac event of mitral valve closure. Therefore, a cardiac event is a specific physiological moment in the cardiac cycle that triggers the acquisition of cardiac ultrasound imaging data.

[0090] It should be noted that although the electrocardiogram can mark the timing of electrical activity, its T wave and P wave are susceptible to interference; relying solely on mechanical signals (such as Doppler spectrum or strain rate curve) may cause some events to be missed due to noise. In order to ensure the accurate triggering of all preset physiological events within the physiological activity cycle, a multi-modal signal source collaborative triggering strategy can be adopted.

[0091] like Figure 3As shown, in one embodiment, step S1 may specifically include the following steps.

[0092] Step S1', simultaneously obtaining waveform signals of an electrocardiogram, a valve pulsed Doppler spectrum, and a tissue dynamic strain rate curve; Step S2 may specifically include the following steps.

[0093] Step S21, comparing the electrocardiogram waveform signal with a first standard waveform corresponding to a first physiological event, comparing the valve pulsed Doppler spectrum with a second standard waveform corresponding to a second physiological event, and comparing the tissue dynamic strain rate curve with a third standard waveform corresponding to a third physiological event; Step S22: determining a waveform signal that conforms to any one of the first physiological event, the second physiological event, and the third physiological event as an initial signal segment.

[0094] In this way, by synchronously acquiring multimodal waveform signals and comparing the three waveform signals with the standard waveform corresponding to the preset physiological events, the waveform segments that meet any event are automatically screened out, which helps to fully cover the key mechanical events of the physiological activity cycle.

[0095] Among them, the electrocardiogram, as an independent module of the target tissue ultrasound imaging system, can be continuously acquired synchronously with any target tissue imaging function. The valve pulse Doppler spectrum and tissue dynamic strain rate curve can be acquired synchronously based on multi-gate Doppler technology.

[0096] It can be understood that different types of waveform signals correspond to different preset physiological events. This signal-event mapping relationship essentially originates from the hierarchical conduction law of the electrophysiological and mechanical activities of the target tissue.

[0097] Specifically, electrical signals (such as ECG) provide leading markers for event triggering, while mechanical signals (such as Doppler spectrum and strain rate) provide direct evidence of the mechanical phase. Through feature matching and credibility evaluation, the two together construct the timing control of ultrasound imaging of target tissues during the physiological activity cycle.

[0098] When the target tissue is the heart, the first physiological event is mitral valve closure, the second is aortic valve closure, and the third is atrial contraction with additional pumping. To accurately trigger these key physiological events, a reliable signal recognition and verification mechanism is required. Different waveform signals have distinct signal characteristics. By extracting and matching specific waveform features (such as the R wave), we ensure that ultrasound imaging data acquisition of the target tissue is strictly synchronized with the mechanical motion of the heart.

[0099] As shown in FIG4( a ), in one embodiment, step S1 and step S2 include the following steps.

[0100] Step S111, obtaining an electrocardiogram; Step S211, determining the positive waveform with the largest amplitude within the physiological activity cycle according to the waveform signal of the electrocardiogram; Step S212 : When the waveform similarity between the positive waveform and the first standard waveform meets a first threshold, determining the signal segment including the positive waveform as the initial signal segment corresponding to the first physiological event.

[0101] In this way, by identifying the positive waveform with the largest amplitude in the electrocardiogram and verifying its matching degree with the first standard waveform, high-reliability trigger control of the first physiological event is achieved.

[0102] In this embodiment, the positive waveform in step S211 refers to the R wave in the electrocardiogram. In other words, when the waveform signal is an electrocardiogram, the initial signal segment corresponding to the first physiological event can be determined based on the R wave in the waveform signal.

[0103] For example, taking the target tissue as the heart and the first physiological event as the mitral valve closure event, when the mitral valve closure event is detected, a corresponding signal feature will appear on the electrocardiogram, specifically the appearance of the R wave, that is, the R wave of the electrocardiogram is associated with the cardiac event of mitral valve closure. The electrocardiogram, as a detection carrier, reflects the occurrence of the cardiac event of mitral valve closure through the signal feature of the R wave, as shown in Figure 5 (a).

[0104] In another embodiment, an electrocardiogram is obtained; a T wave corresponding to a physiological cycle is determined based on a waveform signal of the electrocardiogram; and when the waveform similarity between the waveform of the T wave and a fourth standard waveform meets a fourth threshold, the signal segment containing the T wave is determined to be the initial signal segment corresponding to the second physiological event.

[0105] In this embodiment, when the waveform signal is an electrocardiogram, the initial signal segment corresponding to the second physiological event is determined according to the T wave in the waveform signal.

[0106] For example, taking the target tissue as the heart and the second physiological event as aortic valve closure, when the aortic valve closure cardiac event is detected, the corresponding signal characteristics will appear on the electrocardiogram, specifically the appearance of the T wave, that is, the T wave of the electrocardiogram is associated with the cardiac event of aortic valve closure. The electrocardiogram, as a detection carrier, reflects the occurrence of the cardiac event of aortic valve closure through the signal characteristic of the T wave, as shown in Figure 5 (a).

[0107] In another embodiment, an electrocardiogram is obtained; a P wave corresponding to a physiological cycle is determined based on a waveform signal of the electrocardiogram; and when the waveform similarity between the P wave and a fifth standard waveform meets a fifth threshold, the signal segment containing the P wave is determined to be the initial signal segment corresponding to the third physiological event.

[0108] In this embodiment, when the waveform signal is an electrocardiogram, the initial signal segment corresponding to the third physiological event is determined according to the P wave in the waveform signal.

[0109] For example, taking the target tissue as the heart and the third physiological event as extra blood pumping by atrial contraction, when the cardiac event of extra blood pumping by atrial contraction is detected, a corresponding signal feature will appear on the electrocardiogram, specifically the appearance of a P wave, that is, the P wave of the electrocardiogram is associated with the cardiac event of extra blood pumping by atrial contraction. As a detection carrier, the electrocardiogram reflects the occurrence of the cardiac event of extra blood pumping by atrial contraction through the signal feature of the P wave, as shown in Figure 5 (a).

[0110] In another embodiment, two or even three of the above embodiments may be combined. That is, the waveform signal of the electrocardiogram is compared with the standard waveforms corresponding to the first physiological event and the second physiological event, and the waveform signal that matches either the first physiological event or the second physiological event is determined as the initial signal segment.

[0111] Alternatively, the waveform signal of the electrocardiogram is compared with the standard waveforms corresponding to the first physiological event and the third physiological event, and the waveform signal that meets either the first physiological event or the third physiological event is determined as the initial signal segment.

[0112] Alternatively, the waveform signal of the electrocardiogram is compared with the standard waveforms corresponding to the first physiological event, the second physiological event, and the third physiological event at the same time; and the waveform signal that meets any one of the first physiological event, the second physiological event, and the third physiological event is determined as the initial signal segment.

[0113] Based on this, before step S3, the method further includes the following steps.

[0114] Step P311, based on the first standard waveform, determining a corresponding first score according to at least one of the amplitude, duration, and waveform steepness of the initial signal segment corresponding to the first physiological event; Based on this, step S3 may specifically include the following steps.

[0115] Step S3 ′: when the first score is greater than a first standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

[0116] In this way, the initial signal segment and the first standard waveform are compared through multi-dimensional features such as amplitude, duration and waveform steepness, and the credibility of the relationship between the two is quantified, which not only avoids the mechanical error of the traditional fixed delay trigger method, but also overcomes the risk of false triggering.

[0117] In step S211, a first standard waveform encapsulates the typical spatiotemporal characteristics of a first physiological event (e.g., a mitral valve closure event) and is used to measure or evaluate the degree of abnormality of the current waveform signal. A first score is used to determine a quantified value of the matching between the current R wave signal and the first standard waveform. A higher first score (e.g., greater than the first standard value) indicates a more reliable R wave.

[0118] In a specific embodiment, the amplitude of the initial signal segment is compared with the amplitude of the first standard waveform, the duration of the initial signal segment is compared with the duration of the first standard waveform, and the waveform steepness of the initial signal segment is compared with the waveform steepness of the first standard waveform to determine several local scores; and a weighted average is performed on the several local scores to obtain a first score.

[0119] Similarly, the matching process of the T wave in the electrocardiogram and the corresponding fourth standard waveform, as well as the matching process of the P wave and the corresponding fifth standard waveform, can also adopt a similar calculation process. For details, please refer to the calculation process of the first score in the previous article, which will not be repeated here.

[0120] As shown in FIG4( b ), in another embodiment, step S1 and step S2 include the following steps.

[0121] Step S121, obtaining a pulsed Doppler spectrum of the valve; Step S221, determining spectrum artifacts according to the valve pulse Doppler spectrum; Step S222 : When the waveform similarity between the spectral artifact and the second standard waveform meets a second threshold, determining the signal segment containing the spectral artifact as the initial signal segment corresponding to the second physiological event.

[0122] In this way, by identifying the aortic valve spectrum artifact in the valve pulsed Doppler spectrum and verifying its matching degree with the second standard waveform, high-reliability triggering control of the second physiological event is achieved.

[0123] In a specific embodiment, when the target tissue is a heart, the valve pulsed Doppler spectrum is an aortic valve Doppler spectrum diagram, and the spectrum artifact is an aortic valve spectrum artifact.

[0124] In this embodiment, the aortic valve Doppler spectrum is a pulsed Doppler spectrum, which can intuitively present the hemodynamic characteristics of the aortic valve during cardiac activity.

[0125] Aortic valve spectral artifact is a manifestation of aortic valve closure events on the spectrum graph. By analyzing the artifact characteristics on the aortic valve Doppler spectrum graph, it can help determine whether the cardiac physiological process of aortic valve closure occurs and when it occurs.

[0126] Among them, the aortic valve spectrum artifact refers to a short, bright, thin line signal perpendicular to the baseline that appears on the blood flow spectrum when the aortic valve is closed during pulsed Doppler ultrasound examination, as indicated by the arrow in Figure 5 (b).

[0127] Similarly, only when the initial signal segment corresponding to the aortic valve closure event is credible can the ultrasound probe be controlled to perform tissue ultrasound imaging at the moment corresponding to the initial signal segment.

[0128] Based on this, before step S3, the method further includes the following steps.

[0129] Step P321, based on the second standard waveform, determining a corresponding second score according to at least one of the brightness information and the duration of the initial signal segment corresponding to the second physiological event; Based on this, step S3 may specifically include the following steps.

[0130] Step S3 ″: when the second score is greater than a second standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

[0131] In this way, the initial signal segment and the second standard waveform are compared through multi-dimensional features such as brightness information and duration, and the credibility of the relationship between the two is quantified, which not only avoids the mechanical error of traditional fixed delay triggering, but also overcomes the risk of false triggering.

[0132] In step P321, the second standard waveform encapsulates the typical spatiotemporal characteristics of a second physiological event (e.g., aortic valve closure) and is used to measure or evaluate the degree of abnormality of the current waveform signal. A second score is used to determine a quantitative match between the current aortic valve spectral artifact and the second standard waveform. A higher second score (e.g., greater than the first standard value) indicates a more reliable aortic valve spectral artifact.

[0133] In a specific embodiment, the brightness information of the initial signal segment is compared with the brightness information of the second standard waveform, the duration of the initial signal segment is compared with the duration of the second standard waveform, and the time difference between the initial signal segment and the previous R wave in the synchronized electrocardiogram and the standard time difference between the second standard waveform and the previous R wave in the second standard waveform are compared to determine several local scores; and a weighted average is performed on the several local scores to obtain a second score.

[0134] As shown in FIG4( c ), in another embodiment, step S1 and step S2 include the following steps.

[0135] Step S131, obtaining a tissue dynamic strain rate curve; Step S231, determining the strain rate peak value of a preset stage according to the tissue dynamic strain rate curve; Step S232 : when the waveform similarity between the strain rate peak value in the preset stage and the third standard waveform meets a third threshold, determining the signal segment including the strain rate peak value in the preset stage as the initial signal segment corresponding to the atrial contraction excess pumping event.

[0136] In this way, by identifying the strain rate peak at a preset stage in the tissue dynamic strain rate curve and verifying its matching degree with the third standard waveform, high-reliability triggering control of the third physiological event is achieved.

[0137] In a specific embodiment, when the target tissue is the heart, the tissue dynamic strain rate curve is a myocardial strain rate curve, and the preset stage strain rate peak is a diastolic strain rate peak.

[0138] In this embodiment, the myocardial strain rate curve is a type of myocardial motion velocity data obtained based on tissue Doppler technology. The curve obtained through further processing and analysis can intuitively reflect the image of the mechanical properties of the myocardium. It presents the changes in the strain rate of the myocardium at different stages of the cardiac cycle in the form of a curve, as shown in Figure 5 (c).

[0139] As shown in Figure 5(c), the arrow points to the diastolic strain rate peak. As a key signal characteristic on the myocardial strain rate curve, the diastolic strain rate peak accurately reflects the maximum rate of myocardial tissue stretch and deformation during this specific period. The generation of this peak signal is closely related to cardiac physiological activity, marking a key mechanical change node during diastolic myocardial relaxation. Analysis of the diastolic strain rate peak can indirectly reveal the extent of atrial contraction and, consequently, assess the heart's diastolic function and overall pumping capacity.

[0140] Similarly, only when the initial signal segment corresponding to the extra pumping event of atrial contraction (the third physiological event) is credible, can the ultrasound probe be controlled to perform tissue ultrasound imaging at the moment corresponding to the initial signal segment.

[0141] Based on this, before step S3, the method further includes the following steps.

[0142] Step P331, based on the third standard waveform, determining a corresponding third score according to at least one of the amplitude of the initial signal segment corresponding to the third physiological event and the previous strain rate valley value; Based on this, step S3 may specifically include the following steps.

[0143] Step S3''': when the third score is greater than a third standard value, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

[0144] In this way, the initial signal segment and the third standard waveform are compared through multi-dimensional features such as amplitude and the previous strain rate valley value, and the credibility of the relationship between the two is quantified, which not only avoids the mechanical error of the traditional fixed delay triggering method, but also overcomes the risk of false triggering.

[0145] In step P331, the third standard waveform encapsulates the typical spatiotemporal characteristics of a third physiological event (e.g., an extra atrial pumping event) and is used to measure or evaluate the degree of abnormality of the current waveform signal. A third score is used to quantify the match between the strain rate peak value of the current preset phase and the third standard waveform. A higher third score (e.g., greater than the third standard value) indicates a more reliable strain rate peak value of the preset phase.

[0146] In a specific embodiment, the amplitude of the initial signal segment is compared with the amplitude of the third standard waveform, the previous strain rate trough of the initial signal segment is compared with the previous strain rate trough of the third standard waveform, and the time difference between the initial signal segment and the previous R wave in the synchronized electrocardiogram is compared, and the standard time difference between the third standard waveform and the previous R wave in the third standard waveform is compared to determine several local scores; and a weighted average is performed on the several local scores to obtain a third score.

[0147] The above is the process of triggering and controlling three different types of waveform signals (i.e., electrocardiogram, valve pulsed Doppler spectrum, and tissue dynamic strain rate curve) and their corresponding preset physiological events through standard waveform matching and credibility scoring.

[0148] Based on the previous description, the valve pulse Doppler spectrum and tissue dynamic strain rate curve can both be acquired based on multi-gate Doppler technology. They are indirect representations of mechanical signals rather than cardiac electrical conduction signals. There is a delay between cardiac electrical conduction and mechanical response, with electrical conduction occurring first and mechanical response following.

[0149] Therefore, when the corresponding signal features in the electrocardiogram and the corresponding signal features of the valve pulse Doppler spectrum, or the corresponding signal features of the tissue dynamic strain rate curve all meet the credibility evaluation, it is preferred to generate the acquisition trigger signal based on the valve pulse Doppler spectrum and the tissue dynamic strain rate curve, because the time point determined by the valve pulse Doppler spectrum and the tissue dynamic strain rate curve characteristics is closer to the time point when the mechanical wave is generated, the time required for acquisition will be shorter, and thus the amount of collected data will also be smaller.

[0150] Based on this, Figure 6 As shown, in one embodiment, step S1 may specifically include the following steps.

[0151] Step S141, obtaining an electrocardiogram, and comparing the waveform signal of the electrocardiogram with standard waveforms corresponding to the first physiological event, the second physiological event, and the third physiological event; Step S142 : determining a waveform signal that conforms to any one of the first physiological event, the second physiological event, and the third physiological event as an initial signal segment.

[0152] In this way, by dynamically comparing the ECG with three standard waveforms (corresponding to the R wave of mitral valve closure, the T wave of aortic valve closure, and the P wave characteristic of extra atrial pumping), the timing markers of multiple mechanical events can be decoupled from a single electrophysiological signal. When any characteristic segment (such as the R wave) meets the required match with the corresponding standard waveform (such as the mitral valve closure event), it is determined to be a valid initial signal segment, thus achieving multi-event triggering based solely on the ECG without the need for additional multimodal data acquisition.

[0153] It should be noted that although the electrocardiogram can provide electrical activity markers for the entire physiological activity cycle, on the one hand, its T wave and P wave have smaller amplitudes and are easily affected by factors such as myoelectric interference and external noise, resulting in the detection reliability of secondary physiological events (such as aortic valve closure) and tertiary physiological events (such as extra pumping events due to atrial contraction) being significantly lower than that of the R wave.

[0154] On the other hand, an ECG records the electrical activity of the target tissue, while ultrasound imaging of the target tissue is based on its mechanical activity. There is an inherent delay between the two, which varies from person to person and can be even greater in certain pathological conditions. Therefore, relying solely on the ECG to time-localize the secondary and tertiary physiological events is less accurate and stable.

[0155] To improve the triggering accuracy of key events, the present invention further introduces a mechanical signal source for cross-validation. Specifically, the valve pulsed Doppler spectrum is used to directly capture the valve vibration characteristics associated with the second physiological event, and the dynamic tissue strain rate curve is used to extract the tissue deformation rate characteristics associated with the atrial contraction extra pumping event.

[0156] Based on this, in a specific embodiment, the method further includes: obtaining a valve pulse Doppler spectrum, and comparing the waveform signal of the valve pulse Doppler spectrum with a standard waveform corresponding to a second physiological event; when the waveform signals of the electrocardiogram and the valve pulse Doppler spectrum both meet the standard waveform corresponding to the second physiological event, determining that the waveform signal of the valve pulse Doppler spectrum is the initial waveform.

[0157] In another specific embodiment, the method further includes: obtaining a tissue dynamic strain rate curve, and comparing the waveform signal of the tissue dynamic strain rate curve with a standard waveform corresponding to a third physiological event; when the waveform signals of the electrocardiogram and the tissue dynamic strain rate curve both meet the standard waveform corresponding to the third physiological event, determining that the waveform signal of the tissue dynamic strain rate curve is the initial waveform.

[0158] Compared to the physiological delay between cardiac electrical conduction (ECG) and mechanical response, prioritizing the Doppler spectrum and strain rate curve allows for direct capture of the moment of spontaneous cardiac mechanical waves, shortening acquisition time and reducing data volume. Furthermore, the Doppler spectrum and strain rate curve record the physical effects of mechanical motion, providing strong anti-interference capabilities and facilitating stable triggering of ultrasound imaging.

[0159] It should be noted that the above embodiments show that the electrocardiogram, valve pulse Doppler spectrum and tissue dynamic strain rate curve can be obtained at the initial moment, and the initial signal segment corresponding to the preset heart time can be determined based on these three waveform signals; or the electrocardiogram can be obtained first at the initial moment, and the T wave and P wave corresponding to the second physiological event and the third physiological event can be determined based on the electrocardiogram; and then the valve pulse Doppler spectrum and tissue dynamic strain rate curve corresponding to the second physiological event and the third physiological event can be obtained. In this way, cross-validation or supplementary validation can be further achieved, so that the acquisition moment of the target tissue ultrasound imaging is more closely aligned with the mechanical movement moment of the target tissue.

[0160] In step S3, the signal credibility refers to a scoring index that quantifies the degree of matching between the initial signal segment and the standard waveform, and the scoring criteria include at least one of waveform amplitude, timing deviation and waveform width.

[0161] Ultrasound imaging of target tissue refers to ultrasound data used to assess the mechanical properties of target tissue, specifically determined based on the target tissue's spontaneous mechanical wave data. This data is generated by emitting high-frame-rate diffusion waves to capture the propagation of mechanical waves generated by the target tissue's own mechanical activity (such as valve closure). This data represents dynamic propagation information during ultrasound imaging, as shown in Figure 7(a). Figure 7(a) illustrates the propagation of target tissue spontaneous mechanical wave data at different times.

[0162] like Figure 8 As shown, in one embodiment, step S3 may specifically include the following steps.

[0163] Step S311, obtaining a standard waveform of a preset physiological event corresponding to the initial signal segment; Step S312 : When the waveform similarity between the standard waveform and the initial signal segment is greater than a preset threshold, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

[0164] In this way, by comparing the standard waveform with the actual waveform, the accurate correspondence between the initial signal segment and the preset physiological event can be dynamically verified, avoiding imaging deviations caused by signal noise, individual differences or equipment errors, and ensuring that the imaging operation is strictly synchronized with the real physiological events of the heart, thereby improving the quality of the imaging results and the diagnostic value.

[0165] In step S31, the standard waveform essentially encapsulates the typical spatiotemporal characteristics of the pre-defined physiological event and possesses clear physiological significance. As an idealized acoustic representation of the target tissue's mechanical motion (e.g., the spectral artifacts produced by valve closure vibrations), the standard waveform shares physical homology with the mechanical response of real tissue. The waveform similarity calculation quantifies the degree to which the real-time signal adheres to physiological laws.

[0166] The aforementioned electrocardiogram, valve pulsed Doppler spectrum, and tissue dynamic strain rate curve can be understood as waveform signals acquired from different signal sources. To facilitate intuitive determination of the credibility evaluation results for various signal sources, as shown in Figures 9(a) and 9(b), credible signal sources are marked as 1, and uncredible signal sources are marked as 0. The following summarizes the corresponding processing procedures, combining the content shown in Figures 9(a) and 9(b).

[0167] The waveform signals collected from different signal sources are matched with the standard waveforms corresponding to preset physiological events to determine the initial signal segment, and the initial signal segment is scored for credibility, and the scoring result is compared with the standard value; if the scoring result is greater than the standard value, the signal source is marked as a credible label 1; if the scoring result is less than or equal to the standard value, the signal source is marked as an untrustworthy label 0.

[0168] When processing the electrocardiogram and valve pulse Doppler spectrum collected from different signal sources at the same time, determine whether the label corresponding to the valve pulse Doppler spectrum is the trusted label 1; if so, select the Doppler signal to trigger the acquisition; if not, determine whether the label corresponding to the electrocardiogram is the trusted label 1; if the label corresponding to the electrocardiogram is the trusted label 1, select the electrocardiogram to trigger the acquisition; if the label corresponding to the electrocardiogram is the untrusted label 0, manually intervene to select the trigger condition.

[0169] Continuing with Figures 5(a)-5(c), when a credible initial signal segment corresponding to each preset physiological event is confirmed, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at the time corresponding to the initial signal segment, as shown in Figure 5(d). For example, taking the heart as an example, a trigger acquisition signal for a mitral valve closure event is generated by real-time detection of the R wave of the ECG signal, a trigger acquisition signal for an aortic valve closure event is generated by real-time detection of special artifacts in the valve pulsed Doppler spectrum, and an acquisition trigger signal for an atrial contraction pumping event is generated by real-time detection of the diastolic strain rate peak of the tissue dynamic strain rate curve.

[0170] In one embodiment, controlling the ultrasound probe to perform tissue ultrasound imaging at this moment in step S3 specifically includes the following steps.

[0171] Step S321, controlling the ultrasound probe to transmit ultrasound signals to the target tissue and receive echo signals according to a preset acquisition sequence; the preset acquisition sequence includes at least one of diffuse wave and focused wave; Step S322: Perform ultrasonic imaging of the target tissue according to the echo signal.

[0172] In this way, by adopting a composite acquisition sequence including diffuse waves and focused waves, it is helpful to use focused wave images to accurately identify the target area of ​​interest, and perform high-frame-rate mechanical wave imaging based on diffuse waves within the target area of ​​interest, thereby achieving a balanced control between penetration depth and spatial resolution in ultrasonic imaging of target tissue.

[0173] Among them, the diffusion wave has the characteristics of high frame rate and wide field of view. The high frame rate enables it to quickly capture dynamic changes, while the wide field of view can provide a larger imaging area; the focused wave has the characteristics of high spatial resolution, deep imaging penetration and energy focusing. It can perform high-precision imaging of the area of ​​interest and clearly present the details of the local tissue structure. It is used to accurately identify the key areas of the target tissue in the target tissue ultrasound imaging.

[0174] In a specific embodiment, the ultrasonic probe is controlled to transmit ultrasonic signals to the target tissue and receive echo signals according to an acquisition sequence of first diffuse wave and then focused wave.

[0175] In a specific embodiment, the ultrasonic probe is controlled to transmit ultrasonic signals to the target tissue and receive echo signals according to an acquisition sequence of focusing waves first and then spreading waves.

[0176] Continuing with Figure 5(d), a high-frame-rate diffuse wave is emitted during a first time period, and a focused wave is emitted during a second time period following the emission of the diffuse wave. High-frame-rate signal transmission and reception can be achieved by reducing the width of the imaging area, emitting a focused wide beam, or emitting a non-focused plane wave or diffuse wave. The present invention prioritizes diffuse waves, imaging a large field of view at a frame rate of several kilohertz or higher. The duration of high-frame-rate imaging is set to tens of milliseconds, sufficient to cover the propagation of spontaneous mechanical waves within the target region of interest, and can be adaptively adjusted based on the subject's heart rate.

[0177] To facilitate understanding of the acquisition triggering process for multiple different preset physiological events within a complete physiological activity cycle, the switching process of the acquisition trigger signal can be illustrated by taking the simultaneous acquisition of an electrocardiogram, a valve pulsed Doppler spectrum, and a tissue dynamic strain rate curve as an example.

[0178] Continuing with Figures 5(a)-5(d), taking the heart as an example, an electrocardiogram, an aortic valve pulsed Doppler spectrum, and a myocardial strain rate curve are continuously acquired. When an R wave is detected, an acquisition trigger signal is generated, and the preset acquisition sequence begins to acquire data on the spontaneous mechanical waves caused by mitral valve closure for 50 milliseconds. After acquisition is complete, the sequence switches back to the aortic valve Doppler spectrum and myocardial strain rate curve. When an aortic valve spectral artifact is detected, the preset acquisition sequence is again switched to acquire data on the spontaneous mechanical waves caused by aortic valve closure for 50 milliseconds. After acquisition is complete, the sequence switches back to the aortic valve Doppler spectrum and myocardial strain rate curve. When a diastolic strain rate peak is detected, the preset acquisition sequence is again switched to acquire data on the spontaneous mechanical waves caused by aortic valve closure for 50 milliseconds.

[0179] like Figure 10 As shown, one embodiment of the present invention provides a method for measuring tissue mechanical characteristic parameters based on ultrasound imaging, including but not limited to the following steps.

[0180] Step M1, executing a tissue ultrasound imaging method to determine a target tissue ultrasound image; Step M2, performing mechanical wave imaging analysis on the target tissue ultrasound image to determine the propagation speed of the mechanical wave generated by the mechanical movement of the target tissue within the target area; Step M3: determining the mechanical characteristic parameters of the corresponding target tissue according to the propagation velocity.

[0181] In this way, the mechanical waves generated by the mechanical movement of the target tissue itself are used as the detection source, and the mechanical properties of the target tissue are deduced by measuring the wave velocity, a physical quantity that directly reflects the hardness of the tissue, which can better reflect the actual mechanical state of the target tissue during the mechanical movement.

[0182] In one embodiment, a tissue ultrasound imaging method can refer to the tissue ultrasound imaging method described above, which will not be described in detail here.

[0183] In step M2, the mechanical wave propagation velocity is positively correlated with the stiffness of tissue (e.g., the heart). In other words, greater tissue stiffness corresponds to a higher propagation velocity. The mechanical property parameters of the target tissue are used to quantitatively describe tissue characteristics and reflect the tissue's response to changes in microstructure and stress conditions.

[0184] In a specific embodiment, the mechanical property parameter of the target tissue includes the elastic modulus of myocardial tissue.

[0185] In this embodiment, the elastic modulus of myocardial tissue is used to describe the physical quantity of myocardial tissue's ability to resist deformation and reflect myocardial hardness. For example, the elastic modulus of myocardial tissue is defined as , myocardial density is , the mechanical wave propagation speed is , can be obtained through a simplified myocardial mechanics model .in, Can take 1000kg / m 3 .

[0186] In one embodiment, the target tissue ultrasound image includes N frames of images to be detected, and step M2 may specifically include the following steps.

[0187] Step M21, determining a reference object within the target area; Step M22: Determine the propagation speed of the mechanical wave in the target area based on the N time information and M position information when the mechanical wave reaches the reference object in the N frames of the image to be detected, where N and M are both integers, N>0, M>0.

[0188] In this way, by using N-frame detection images to capture the propagation process of mechanical waves in the target area, rich spatiotemporal information can be obtained, which can reflect the mechanical properties of the target tissue in real time and accurately, providing an important basis for the diagnosis and treatment of diseases.

[0189] In one embodiment, when the target tissue is the heart, the reference object is the myocardial line, thereby reducing wavefront misjudgment caused by overall heart motion or local image noise.

[0190] In a specific embodiment, step M22 may specifically include the following steps.

[0191] Step M221, recording the time information of the mechanical wave reaching different pixel points of the reference object, and fitting the time information using a surface fitting method to generate an isochrone map; Step M222, determining the velocity components of each pixel in the first direction and the second direction based on the isochronal map and the distance relationship between the pixels; Step M223: determining the propagation speed of the mechanical wave in the target area based on the velocity component.

[0192] In this way, by converting the discrete time of the mechanical wave front reaching each pixel point of the target tissue into a continuous tissue mechanical field distribution, it provides the clinic with an intuitive and quantifiable basis for elasticity assessment.

[0193] In step M221, the isochronal map is a diagram that records the time information of the mechanical wave reaching different pixels of the reference object in the target area.

[0194] Specifically, the time information of the mechanical wave reaching each pixel point of the myocardial line is smoothly reconstructed through surface fitting to generate an isochrone map reflecting the dynamic propagation of the wavefront, as shown in Figure 7(b). Based on the spatiotemporal gradient of the isochrone map, the velocity components of the mechanical wave along the first and second directions are calculated. This not only captures the wave velocity differences caused by the anisotropy and inhomogeneity of the target tissue, but also decouples the macroscopic propagation trajectory into the microscopic mechanical response through partial differential operations. The final two-dimensional wave velocity vector retains the spatial resolution while avoiding the amplitude and direction deviations of traditional one-dimensional velocity measurements.

[0195] In step M222, the first direction and the second direction represent the horizontal axis direction (x-axis) and the vertical axis direction (y-axis), respectively. For example, the velocity component of each pixel point in the first direction is defined as , the velocity component in the second direction is , then the propagation speed at the corresponding point is , and finally form a spatial distribution map of mechanical wave velocity.

[0196] In other embodiments, when the target tissue is the heart, the myocardial line can be selected as a reference object. By recording the time-space sequence of the leading edge of the mechanical wave generated by the mechanical movement of the heart reaching different positions of the myocardial line, the mechanical wave arrival time and the myocardial line position data are fitted using mathematical fitting methods (such as linear fitting, polynomial fitting, etc.) to obtain a mathematical model that can describe the average propagation velocity of the mechanical wave; based on the fitted mathematical model, the average velocity of the mechanical wave in the myocardial tissue can be calculated.

[0197] In addition, changes in blood pressure levels will change the mechanical load borne by the target tissue, which will directly affect the measurement of the mechanical wave propagation velocity of the target tissue even when the microstructure of the target tissue itself does not change.

[0198] Based on this, Figure 11 As shown, in one embodiment, the method for measuring tissue mechanical characteristic parameters based on ultrasound imaging further includes the following steps.

[0199] Step M41, determining a first mechanical characteristic parameter of a first detection subject to obtain a first blood pressure of the first detection subject; Step M42, determining a second mechanical characteristic parameter of the second test subject, and obtaining a second blood pressure of the second test subject; Step M43: Convert the first blood pressure and the second blood pressure into a first tissue stress and a second tissue stress, respectively, and use the first tissue stress and the second tissue stress to standardize the first mechanical characteristic parameter and the second mechanical characteristic parameter, respectively. When the standardized first mechanical characteristic parameter is greater than the standardized second mechanical characteristic parameter, the tissue intrinsic hardness of the first detection object is higher than the tissue intrinsic hardness of the second detection object.

[0200] In this way, by comparing mechanical property parameters under standard physiological load conditions, the influence of blood pressure on the assessment of tissue intrinsic hardness is effectively removed, making the determination results of tissue hardness more clinically valuable and providing a quantitative basis for cardiovascular disease risk assessment and tissue function monitoring.

[0201] In step M43, tissue stress refers to the distribution of internal forces per unit area within biological tissue due to external loads or internal deformation, reflecting the tissue's ability to resist deformation. When the target tissue is the heart, tissue stress refers to myocardial wall stress, which refers to the mechanical load per unit area of ​​the myocardial wall during cardiac contraction or relaxation. It reflects the mechanical state of the myocardium under the combined effects of blood pressure and ventricular geometry.

[0202] In one embodiment, the first blood pressure is converted into the first tissue stress using Laplace's law; and the second blood pressure is converted into the second tissue stress using Laplace's law.

[0203] In this embodiment, by comparing the mechanical characteristic parameters of different objects (the first object and the second object) under the same load conditions, it is helpful to directly reflect the difference in intrinsic hardness of tissues between individuals.

[0204] In other embodiments, a third mechanical characteristic parameter of the first detection object is determined in a first time period to obtain a third blood pressure of the first period; a fourth mechanical characteristic parameter of the first detection object is determined in a second time period to obtain a fourth blood pressure of the second time period; the third blood pressure and the fourth blood pressure are converted into a third tissue stress and a fourth tissue stress, respectively, and the third mechanical characteristic parameter and the fourth mechanical characteristic parameter are standardized using the third tissue stress and the fourth tissue stress, respectively. When the standardized third tissue stress is greater than the standardized fourth tissue stress, the tissue intrinsic hardness of the first detection object in the first time period is higher than the tissue intrinsic hardness in the second time period.

[0205] The third blood pressure, the third mechanical characteristic parameter, the fourth blood pressure, and the fourth mechanical characteristic parameter are used to determine the intrinsic hardness of the tissue of the first detection object in the first time period and the second time period.

[0206] In this embodiment, the mechanical property parameters of the same test object at different stages under the same load conditions are used to help evaluate disease progression or treatment effects.

[0207] Since there is a close physiological correlation between blood pressure levels and mechanical property parameters, the simultaneous display of different physiological events within the physiological activity cycle and mechanical property parameters can provide clinicians with a more comprehensive basis for tissue function assessment.

[0208] Figures 12(a) to 12(d) are schematic diagrams showing the measurement results of tissue mechanical characteristic parameters based on ultrasound imaging in a preferred embodiment. Taking the heart as an example, the following specifically describes the measurement results of myocardial tissue mechanical characteristic parameters based on cardiac ultrasound imaging in combination with Figures 12(a) to 12(d).

[0209] As shown in Figure 12(a), tissue mechanical parameters (such as elastic modulus) and blood pressure load (such as isovolumetric contraction blood pressure) corresponding to spontaneous mechanical waves of the same target tissue (e.g., the heart) are paired and displayed in a table format. Specifically, tissue mechanical parameters (such as elastic modulus) corresponding to preset physiological events (such as mitral valve closure, aortic valve closure, and atrial contraction with extra blood pumping) are displayed alongside simultaneously recorded blood pressure values ​​in a table format. This helps quickly locate abnormal combinations and supports multi-parameter combined diagnosis.

[0210] As shown in Figure 12(b), tissue mechanical parameters (such as myocardial elastic modulus) are normalized using tissue stress (e.g., myocardial wall stress). This helps eliminate the effects of load and identify true pathological changes (if the normalized value remains high, a diagnosis of intrinsic tissue stiffness may be made).

[0211] Figure 12(c) shows the changes in tissue mechanical properties (such as elastic modulus) and synchronized blood pressure cycle changes during a complete physiological activity cycle. This figure helps to reveal the phase response of tissue intrinsic stiffness to blood pressure.

[0212] Figure 12(d) shows the elasticity-blood pressure closed curve. This curve plots tissue mechanical properties (e.g., elastic modulus) and blood pressure in a phase-space curve (elasticity on the Y-axis, blood pressure on the X-axis), forming a closed loop. The area of ​​this closed loop quantifies the mechanical work expended by the target tissue to maintain a balance between elastic deformation and blood pressure load during a physiological activity cycle. Specifically, if the closed loop area is large and full, the elastic response is synchronized with blood pressure changes, indicating a healthy target tissue. Conversely, if the closed loop area is small, elastic regulation is lagging, indicating the presence of localized pathology in the target tissue.

[0213] Figure 13 A schematic diagram of the flow chart of the tissue ultrasound imaging method in a preferred embodiment is shown below. Figure 13 The content shown summarizes the process of ultrasound imaging of target tissue.

[0214] The tissue ultrasound imaging system enters the cardiac ultrasound imaging mode. In this mode, there are two different operation process paths. These two process paths can be executed independently or used in combination according to actual needs.

[0215] Specifically, one approach involves first determining the acquisition triggering method corresponding to each preset physiological event (i.e., spontaneous mechanical wave data); responding to the trigger signal, acquiring cardiac ultrasound imaging data based on the trigger signal, and performing mechanical wave imaging analysis on the acquired target tissue ultrasound imaging data to determine the target tissue mechanical property parameters; and then displaying the calculated target tissue mechanical property parameters. Another approach involves performing a blood pressure load measurement after entering the target tissue ultrasound imaging mode. After the measurement is completed, the blood pressure load measurement result is displayed directly or converted to tissue stress (e.g., using Laplace's law).

[0216] In summary, the tissue ultrasound imaging system and method, as well as the mechanical property parameter measurement method, provided by the present invention capture and analyze the characteristic waveform signal generated by the mechanical motion of the target tissue in real time. When the characteristic waveform signal meets the credibility condition, the ultrasound probe is triggered to acquire ultrasound imaging data. This ensures that the acquisition time of the target tissue ultrasound imaging is synchronized with the phase of the spontaneous mechanical waves generated by the target tissue, avoiding timing deviations and providing more reliable tissue mechanical property data for clinical use. Furthermore, by triggering acquisition only when the conditions are met, redundant storage of invalid data is avoided, reducing system load.

[0217] It should be understood that although this specification is described in terms of implementation methods, not every implementation method contains only one independent technical solution. This narrative method of the specification is only for the sake of clarity. Those skilled in the art should regard the specification as a whole. The technical solutions in each implementation method can also be appropriately combined to form other implementation methods that can be understood by those skilled in the art.

[0218] The series of detailed descriptions listed above are only specific descriptions of feasible implementation methods of the present invention. They are not intended to limit the scope of protection of the present invention. Any equivalent implementation methods or changes that do not deviate from the technical spirit of the present invention should be included in the scope of protection of the present invention.

Claims

1. A tissue ultrasound imaging method, characterized in that: include: Obtaining a waveform signal corresponding to the mechanical motion of the target tissue; determining an initial signal segment in the waveform signal whose waveform matches a standard waveform corresponding to a preset physiological event; When the initial signal segment meets the conditions regarding signal credibility, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at this moment.

2. The tissue ultrasound imaging method according to claim 1, wherein: The obtaining of a waveform signal corresponding to the mechanical motion of the target tissue comprises: Simultaneously obtain waveform signals of electrocardiogram, valve pulsed Doppler spectrum and tissue dynamic strain rate curve; The step of determining an initial signal segment in which a waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: Comparing the waveform signal of the electrocardiogram with a first standard waveform corresponding to a first physiological event, comparing the waveform signal of the valve pulsed Doppler spectrum with a second standard waveform corresponding to a second physiological event, and comparing the waveform signal of the tissue dynamic strain rate curve with a third standard waveform corresponding to a third physiological event; A waveform signal that conforms to any one of the first physiological event, the second physiological event, and the third physiological event is determined as an initial signal segment.

3. The tissue ultrasound imaging method according to claim 1, wherein: When the initial signal segment meets the signal credibility condition, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at this moment includes: Obtaining a standard waveform corresponding to a preset physiological event matching the initial signal segment; When the waveform similarity between the standard waveform and the initial signal segment is greater than a preset threshold, the ultrasonic probe is controlled to perform ultrasonic imaging of the target tissue at a time corresponding to the initial signal segment.

4. The tissue ultrasound imaging method according to claim 1, wherein: The obtaining of a waveform signal corresponding to the mechanical motion of the target tissue comprises: Obtain an electrocardiogram; The step of determining an initial signal segment in which a waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: Determine the positive waveform with the maximum amplitude in the physiological activity cycle according to the waveform signal of the electrocardiogram; When the waveform similarity between the positive waveform and the first standard waveform meets a first threshold, the signal segment including the positive waveform is determined to be the initial signal segment corresponding to the first physiological event.

5. The tissue ultrasound imaging method according to claim 2, wherein: Before the initial signal segment meets the condition on signal credibility, the method further includes: Determining a corresponding first score based on the first standard waveform according to at least one of the amplitude, duration, and waveform steepness of the initial signal segment corresponding to the first physiological event; When the initial signal segment meets the signal credibility condition, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at this moment includes: When the first score is greater than a first standard value, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

6. The tissue ultrasound imaging method according to claim 1, characterized in that: The obtaining of a waveform signal corresponding to the mechanical motion of the target tissue comprises: Obtain valve pulsed Doppler spectrum; The step of determining an initial signal segment in which a waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: Spectral artifacts were determined based on the valve pulsed Doppler spectrum; When the waveform similarity between the spectral artifact and the second standard waveform meets a second threshold, the signal segment containing the spectral artifact is determined to be the initial signal segment corresponding to the second physiological event.

7. The tissue ultrasound imaging method according to claim 2, wherein: Before the initial signal segment meets the condition on signal credibility, the method further includes: Determining a corresponding second score based on the second standard waveform and at least one of the brightness information and the duration of the initial signal segment corresponding to the second physiological event; When the initial signal segment meets the signal credibility condition, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at this moment includes: When the second score is greater than a second standard value, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

8. The tissue ultrasound imaging method according to claim 1, wherein: The obtaining of a waveform signal corresponding to the mechanical motion of the target tissue comprises: Obtain tissue dynamic strain rate curve; The step of determining an initial signal segment in which a waveform in the waveform signal matches a standard waveform corresponding to a preset physiological event includes: Determine the peak strain rate of the preset stage according to the dynamic strain rate curve of the tissue; When the waveform similarity between the strain rate peak value in the preset stage and the third standard waveform meets a third threshold, the signal segment including the strain rate peak value in the preset stage is determined as the initial signal segment corresponding to the third physiological event.

9. The tissue ultrasound imaging method according to claim 2, wherein: Before the initial signal segment meets the condition on signal credibility, the method further includes: determining, based on the third standard waveform, a corresponding third score according to at least one of an amplitude of an initial signal segment corresponding to the third physiological event and a previous strain rate trough value; When the initial signal segment meets the signal credibility condition, controlling the ultrasound probe to perform ultrasound imaging of the target tissue at this moment includes: When the third score is greater than a third standard value, the ultrasound probe is controlled to perform ultrasound imaging of the target tissue at a time corresponding to the initial signal segment.

10. The tissue ultrasound imaging method according to claim 1, wherein: The obtaining of a waveform signal corresponding to the mechanical motion of the target tissue comprises: Obtaining an electrocardiogram, and comparing a waveform signal of the electrocardiogram with standard waveforms corresponding to the first physiological event, the second physiological event, and the third physiological event; A waveform signal that conforms to any one of the first physiological event, the second physiological event, and the third physiological event is determined as an initial signal segment.

11. The tissue ultrasound imaging method according to claim 10, characterized in that: The method further comprises: obtaining a valve pulsed Doppler spectrum, and comparing a waveform signal of the valve pulsed Doppler spectrum with a standard waveform corresponding to a second physiological event; When the waveform signals of the electrocardiogram and the valve pulse Doppler spectrum both conform to the standard waveform corresponding to the second physiological event, the waveform signal of the valve pulse Doppler spectrum is determined to be the initial waveform.

12. The tissue ultrasound imaging method according to claim 10, wherein: The method further comprises: obtaining a tissue dynamic strain rate curve, and comparing a waveform signal of the tissue dynamic strain rate curve with a standard waveform corresponding to a third physiological event; When the waveform signals of the electrocardiogram and the tissue dynamic strain rate curve both conform to the standard waveform corresponding to the third physiological event, the waveform signal of the tissue dynamic strain rate curve is determined to be the initial waveform.

13. The tissue ultrasound imaging method according to claim 1, wherein: The controlling the ultrasonic probe to perform ultrasonic imaging of the target tissue at this moment includes: Controlling the ultrasonic probe to transmit ultrasonic signals to the target tissue and receive echo signals according to a preset acquisition sequence; the preset acquisition sequence includes at least one of a diffuse wave and a focused wave; Ultrasonic imaging of target tissue is performed based on the echo signal.

14. A method for measuring tissue mechanical characteristic parameters based on ultrasound imaging, characterized in that: include: Executing the tissue ultrasonic imaging method according to any one of claims 1 to 13 to determine an ultrasonic image of the target tissue; Performing mechanical wave imaging analysis on the target tissue ultrasound image to determine the propagation speed of the mechanical wave generated by the mechanical movement of the target tissue within the target area; The mechanical characteristic parameters of the corresponding target tissue are determined according to the propagation velocity.

15. The method for measuring tissue mechanical characteristic parameters according to claim 14, wherein: The target tissue ultrasound image includes N frames of images to be detected; performing mechanical wave imaging analysis on the target tissue ultrasound image to determine the propagation speed of the mechanical wave generated by the mechanical movement of the target tissue in the target area includes: Identify reference objects within the target area; The propagation speed of the mechanical wave in the target area is determined based on the N time information and M position information when the mechanical wave reaches the reference object in N frames of the image to be detected, where N and M are both integers, N>0, M>0.

16. The method for measuring tissue mechanical characteristic parameters according to claim 15, characterized in that: The method of determining the propagation speed of the mechanical wave in the target area according to N time information and M position information when the mechanical wave reaches the reference object in N frames of the image to be detected includes: Recording the time information of the mechanical wave reaching different pixel points of the reference object, and fitting the time information using a surface fitting method to generate an isochrone map; Determine the velocity components of each pixel point in the first direction and the second direction based on the isochrone map and the distance relationship between the pixels; A propagation speed of the mechanical wave in the target area is determined based on the velocity component.

17. The method for measuring tissue mechanical characteristic parameters according to claim 14, wherein: The method further comprises: determining a first mechanical characteristic parameter of a first detection subject and obtaining a first blood pressure of the first detection subject; determining a second mechanical characteristic parameter of the second test subject and obtaining a second blood pressure of the second test subject; converting the first blood pressure and the second blood pressure into a first tissue stress and a second tissue stress, respectively, and standardizing the first mechanical characteristic parameter and the second mechanical characteristic parameter using the first tissue stress and the second tissue stress, respectively; When the standardized first mechanical characteristic parameter is greater than the standardized second mechanical characteristic parameter, the tissue intrinsic hardness of the first detection object is higher than the tissue intrinsic hardness of the second detection object.

18. A tissue ultrasound imaging system, characterized in that: include: An input module, used to obtain a waveform signal corresponding to the mechanical motion of the target tissue; a processing module, configured to determine an initial signal segment in the waveform signal whose waveform matches a standard waveform corresponding to a preset physiological event; The imaging module is used to control the ultrasound probe to perform ultrasound imaging of the target tissue at this moment when the initial signal segment meets the conditions on signal credibility.

19. The tissue ultrasound imaging system according to claim 18, wherein: The system further comprises: The first measurement module is used to perform mechanical wave imaging analysis on the target tissue ultrasound image generated by the imaging module to determine the propagation speed of the mechanical wave in the target area; and to determine the mechanical characteristic parameters of the corresponding target tissue based on the propagation speed.

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