Parameter measurement method based on cardiac ultrasound and ultrasonic imaging system

Abstract

The invention provides a cardiac ultrasound-based parameter measurement method and an ultrasound imaging system. The method comprises the following steps: acquiring multiple frames of first ultrasound images of a first scanning section of a heart part of a target object; based on the multiple frames of first ultrasonic images of the first scanning section, determining the duration of a first cardiac cycle corresponding to the first scanning section; based on the duration of the first cardiac cycle, determining a first heart rate corresponding to the first cardiac cycle; acquiring multiple frames of second ultrasonic images of a second scanning section of the heart part of the target object, wherein the second scanning section is different from the first scanning section; determining the duration of a second cardiac cycle corresponding to the second scanning section based on multiple frames of second ultrasonic images of the second scanning section; determining a second heart rate corresponding to the second cardiac cycle based on the duration of the second cardiac cycle; and determining the heart rate variability between the first scanning section and the second scanning section based on the first heart rate and the second heart rate, thereby improving the parameter measurement precision.

Description

Technical Field

[0001] The present invention relates to the technical field of ultrasonic imaging, and more particularly to a parameter measurement method based on cardiac ultrasound and an ultrasonic imaging system. Background Art

[0002] Echocardiography is a classic imaging method for analyzing patients' cardiac function (e.g., calculation of ejection fraction, analysis of myocardial stress and strain, etc.). The measurement of some cardiac-related parameters may involve the calculation of multiple sections, such as the Simpson biplane method for calculating ejection fraction (EF) values, and the three-section method for calculating stress and strain such as global longitudinal strain (GLS), etc. However, if the data of multiple sections are not obtained in the same period, excessive heart rate variability or excessive apical shortening will affect the measurement accuracy, making the parameter measurement results of cardiac ultrasound unreliable. Summary of the invention

[0003] A series of simplified concepts are introduced in the Summary of the Invention, which will be further described in detail in the Detailed Description of the Invention. The Summary of the Invention does not mean to attempt to define the key features and essential technical features of the claimed technical solution, nor does it mean to attempt to determine the scope of protection of the claimed technical solution.

[0004] An embodiment of the present invention provides a parameter measurement method based on cardiac ultrasound, the method comprising:

[0005] Acquire a plurality of frames of first ultrasound images of a first scanning section of a heart portion of a target object;

[0006] Determining the duration of a first cardiac cycle corresponding to the first scanning section based on the multiple frames of the first ultrasound image of the first scanning section;

[0007] Determining a first heart rate corresponding to the first cardiac cycle based on the duration of the first cardiac cycle;

[0008] Acquire multiple frames of second ultrasound images of a second scanning section of a heart portion of the target object, wherein the second scanning section is different from the first scanning section;

[0009] Determining the duration of a second cardiac cycle corresponding to the second scanning section based on the multiple frames of second ultrasound images of the second scanning section;

[0010] determining a second heart rate corresponding to the second cardiac cycle based on the duration of the second cardiac cycle;

[0011] Based on the first heart rate and the second heart rate, the heart rate variability between the first scanning plane and the second scanning plane is determined.

[0012] On the other hand, the present application provides a parameter measurement method based on cardiac ultrasound, characterized in that the method comprises:

[0013] Acquire a plurality of frames of first ultrasound images of a first scanning section of a heart portion of a target object;

[0014] Acquire multiple frames of second ultrasound images of a second scanning section of the heart of the target object;

[0015] Determine a first apical long-axis diameter of the ventricle based on the first ultrasound image corresponding to a specific frame in a first cardiac cycle corresponding to the first scanning section, and determine a second apical long-axis diameter of the ventricle based on the second ultrasound image corresponding to the specific frame in a second cardiac cycle corresponding to the second scanning section;

[0016] An amount of apical shortening between the first apical major axis diameter and the second apical major axis diameter is calculated.

[0017] In another aspect, the present application provides an ultrasound imaging system, the ultrasound imaging system comprising:

[0018] Ultrasound probe;

[0019] A transmitting circuit, used for controlling the ultrasonic probe to transmit ultrasonic waves toward the heart of the target object;

[0020] A receiving circuit, used for receiving an ultrasonic echo based on the ultrasonic wave returned from the heart part to obtain an ultrasonic echo signal;

[0021] A processor, configured to acquire ultrasound images of at least two scanning sections of a heart portion of a target object according to the ultrasound echo signal;

[0022] A memory for storing executable program instructions;

[0023] A processor, configured to execute the program instructions stored in the memory, so that the processor executes the aforementioned parameter measurement method based on cardiac ultrasound;

[0024] A display for displaying visual information.

[0025] According to the cardiac ultrasound-based parameter measurement method and ultrasound imaging system of the embodiments of the present invention, by calculating the heart rate variability between different scanning sections, a basis is provided for judging the reliability of the parameter measurement results, thereby improving the measurement accuracy and reliability of the parameter measurement.

[0026] According to the cardiac ultrasound-based parameter measurement method and ultrasound imaging system of the embodiments of the present invention, by calculating the amount of apical shortening between different scanning sections, a basis is provided for judging the reliability of parameter measurement results, thereby improving the measurement accuracy and reliability of parameter measurement. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings required for use in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings in the following description are only some embodiments of the present invention. For ordinary technicians in this field, other accompanying drawings can be obtained based on these accompanying drawings without paying creative labor.

[0028] In the attached picture:

[0029] Figure 1 A schematic block diagram of an ultrasound imaging system according to an embodiment of the present invention is shown;

[0030] Figure 2 A schematic flow chart showing a parameter measurement method based on cardiac ultrasound according to an embodiment of the present invention;

[0031] Figure 3 A schematic diagram showing a standard level prompt of a section and endocardial tracing according to an embodiment of the present invention;

[0032] Figure 4A Shows a prompting method of first prompting information when the heart rate variability exceeds a first preset threshold according to an embodiment of the present invention;

[0033] Figure 4B The second prompt information and the third prompt information are shown when the amount of apical shortening exceeds the second preset threshold according to an embodiment of the present invention;

[0034] Figure 5 A schematic diagram showing a standard section and a measurement method recommended by the Simpson biplane method according to an embodiment of the present invention;

[0035] Figure 6 A schematic flow chart of a parameter measurement method based on cardiac ultrasound according to another embodiment of the present invention is shown. DETAILED DESCRIPTION

[0036] In order to make the purpose, technical scheme and advantages of the present invention more obvious, the exemplary embodiments according to the present invention will be described in detail with reference to the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments of the present invention, and it should be understood that the present invention is not limited to the exemplary embodiments described herein. Based on the embodiments of the present invention described in the present invention, all other embodiments obtained by those skilled in the art without creative work should fall within the protection scope of the present invention.

[0037] In the following description, a large number of specific details are provided to provide a more thorough understanding of the present invention. However, it is apparent to those skilled in the art that the present invention can be implemented without one or more of these details. In other examples, in order to avoid confusion with the present invention, some technical features well known in the art are not described.

[0038] It should be understood that the present invention can be implemented in different forms and should not be interpreted as limited to the embodiments set forth herein. On the contrary, these embodiments are provided to make the disclosure thorough and complete and to fully convey the scope of the present invention to those skilled in the art.

[0039] The purpose of the terms used herein is only to describe specific embodiments and is not intended to be limiting of the present invention. When used herein, the singular forms "a", "an" and " / the" are also intended to include plural forms, unless the context clearly indicates another way. It should also be understood that the terms "consisting of" and / or "comprising" when used in this specification determine the presence of features, integers, steps, operations, elements and / or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and / or groups. When used herein, the term "and / or" includes any and all combinations of the relevant listed items.

[0040] In order to fully understand the present invention, a detailed structure will be presented in the following description to illustrate the technical solution proposed by the present invention. The optional embodiments of the present invention are described in detail as follows, but in addition to these detailed descriptions, the present invention may also have other implementations.

[0041] Next, first refer to Figure 1 An ultrasound imaging system according to an embodiment of the present invention is described. Figure 1 FIG. 1 is a schematic structural block diagram of an ultrasound imaging system 100 according to an embodiment of the present invention.

[0042] like Figure 1As shown, the ultrasound imaging system 100 includes an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118. Further, the ultrasound imaging system may also include a transmit / receive selection switch 120 and a beamforming module 122, and the transmitting circuit 112 and the receiving circuit 114 may be connected to the ultrasound probe 110 through the transmit / receive selection switch 120.

[0043] The ultrasonic probe 110 includes a plurality of transducer array elements, which can be arranged in a row to form a linear array, or arranged in a two-dimensional matrix to form a surface array, or a plurality of transducer array elements can also form a convex array. The transducer array element is used to transmit ultrasonic waves according to the excitation electrical signal, or to convert the received ultrasonic waves into electrical signals, so each transducer array element can be used to realize the mutual conversion between the electrical pulse signal and the ultrasonic wave, so as to realize the transmission of ultrasonic waves to the tissue of the target area of ​​the object to be tested, and can also be used to receive the ultrasonic wave echo reflected by the tissue. When performing ultrasonic testing, which transducer array elements are used to transmit ultrasonic waves and which transducer array elements are used to receive ultrasonic waves can be controlled by the transmission sequence and the reception sequence, or the transducer array elements can be controlled to transmit ultrasonic waves or receive ultrasonic wave echoes in time slots. The transducer array elements participating in ultrasonic wave transmission can be excited by electrical signals at the same time, so as to transmit ultrasonic waves at the same time; or, the transducer array elements participating in ultrasonic wave beam transmission can also be excited by several electrical signals with a certain time interval, so as to continuously transmit ultrasonic waves with a certain time interval.

[0044] During the ultrasonic imaging process, the transmitting circuit 112 sends the delayed focused transmitting pulse to the ultrasonic probe 110 through the transmitting / receiving selection switch 120. The ultrasonic probe 110 is stimulated by the transmitting pulse to transmit an ultrasonic beam to the tissue of the target area of ​​the object to be measured, and receives the ultrasonic echo with tissue information reflected from the tissue of the target area after a certain delay, and reconverts the ultrasonic echo into an electrical signal. The receiving circuit 114 receives the electrical signal converted and generated by the ultrasonic probe 110, obtains the ultrasonic echo signal, and sends these ultrasonic echo signals to the beamforming module 122, which performs focusing delay, weighting and channel summing on the ultrasonic echo data, and then sends them to the processor 116. The processor 116 performs signal detection, signal enhancement, data conversion, logarithmic compression and other processing on the ultrasonic echo signal to form an ultrasonic image. The ultrasonic image obtained by the processor 116 can be displayed on the display 118 or stored in the memory 124.

[0045] Optionally, the processor 116 may be implemented as software, hardware, firmware or any combination thereof, and may use a single or multiple application specific integrated circuits (ASICs), a single or multiple general purpose integrated circuits, a single or multiple microprocessors, a single or multiple programmable logic devices, or any combination of the aforementioned circuits and / or devices, or other suitable circuits or devices. Furthermore, the processor 116 may control other components in the ultrasound imaging system 100 to perform the corresponding steps of the methods in various embodiments of the present specification.

[0046] The display 118 is connected to the processor 116, and the display 118 may be a touch screen, a liquid crystal display, etc.; or, the display 118 may be an independent display such as a liquid crystal display, a television, etc., which is independent of the ultrasound imaging system 100; or, the display 118 may be a display screen of an electronic device such as a smart phone or a tablet computer, etc. The number of the display 118 may be one or more.

[0047] The display 118 can display the ultrasound image obtained by the processor 116. In addition, while displaying the ultrasound image, the display 118 can also provide the user with a graphical interface for human-computer interaction. One or more controlled objects are set on the graphical interface, and the user is provided with a human-computer interaction device to input operation instructions to control these controlled objects, thereby performing corresponding control operations. For example, an icon is displayed on the graphical interface, and the icon can be operated by the human-computer interaction device to perform a specific function, such as drawing a region of interest box on the ultrasound image.

[0048] Optionally, the ultrasound imaging system 100 may further include other human-machine interaction devices in addition to the display 118, which are connected to the processor 116. For example, the processor 116 may be connected to the human-machine interaction device via an external input / output port, and the external input / output port may be a wireless communication module, or a wired communication module, or a combination of the two. The external input / output port may also be implemented based on USB, bus protocols such as CAN, and / or wired network protocols.

[0049] The human-computer interaction device may include an input device for detecting user input information, which may be, for example, a control instruction for ultrasonic transmission / reception timing, an operation input instruction for drawing points, lines or frames on an ultrasonic image, or other instruction types. The input device may include a keyboard, a mouse, a scroll wheel, a trackball, a mobile input device (such as a mobile device with a touch screen, a mobile phone, etc.), a multi-function knob, etc., or a combination of multiple thereof. The human-computer interaction device may also include an output device such as a printer.

[0050] The ultrasound imaging system 100 may further include a memory 124 for storing instructions executed by the processor, storing received ultrasound echoes, storing ultrasound images, etc. The memory may be a flash memory card, a solid-state memory, a hard disk, etc. It may be a volatile memory and / or a non-volatile memory, a removable memory and / or a non-removable memory, etc.

[0051] It should be understood that Figure 1 The components included in the ultrasonic imaging system 100 are only exemplary, and the ultrasonic imaging system 100 may include more or fewer components, and the present invention is not limited thereto.

[0052] Refer to the following Figure 2 The parameter measurement method based on cardiac ultrasound proposed in an embodiment of the present invention is described. Figure 2 2 is a schematic flow chart of a parameter measurement method 200 based on cardiac ultrasound according to an embodiment of the present invention. The parameter measurement method based on cardiac ultrasound according to an embodiment of the present invention can be used in an ultrasound imaging system, which includes an ultrasound probe, a processor, and a display. The ultrasound imaging system can be implemented as the ultrasound imaging system 100 as described above. Alternatively, the parameter measurement method 200 based on cardiac ultrasound according to an embodiment of the present invention can be based on a parameter measurement system based on cardiac ultrasound, which can be any computer device with data processing function, etc. The system can obtain real-time ultrasound images or offline ultrasound images collected by the ultrasound imaging system, etc.

[0053] The current method for measuring left ventricular volume by echocardiography is mainly based on the Simpson single / double plane method. Among them, the double plane method has a relatively high accuracy rate, can correct ventricular deformation, and reduce the error of geometric model assumptions. It is the measurement method unanimously recommended by the current ultrasound expert consensus and guidelines.

[0054] The biplane method requires collecting standard apical two-chamber heart and apical four-chamber heart section data at two times, tracing the left ventricular end-diastolic and end-systolic endocardial contours, measuring the apical long-axis diameter, and calculating the volume and EF value. When the two data are not in the same phase, the large differences in heart rate and apical long-axis diameter will affect the measurement accuracy, making the EF value unreliable. In clinical practice, doctors generally manually select the period of matching two sections for parameter measurement based on experience. The operation is cumbersome and the credibility of the measurement results cannot be intuitively displayed.

[0055] Based on the myocardial stress-strain analysis of data from three cardiac sections (A2C, A3C, and A4C), doctors also recommend selecting a period with similar heart rate and apical long-axis diameter for analysis and calculation. The measured GLS (Global Longitudinal Strain) is the most reliable.

[0056] The ultrasound images of different section types can be obtained by adjusting the probe according to the doctor's prior experience during the scan. For example, the doctor can adjust the scanning section of the probe at the estimated end-diastole and end-systole of the ventricle according to the contraction state of the ventricle in the real-time ultrasound image, for example, the probe scans A2C, A4C or A3C. Alternatively, the sections A2C, A4C or A3C can be switched randomly.

[0057] In view of the above technical problems, Figure 2 As shown, a parameter measurement method 200 based on cardiac ultrasound provided by an embodiment of the present invention includes the following steps:

[0058] In step S210, a plurality of first ultrasound images of a first scanning section of a heart portion of a target object are acquired;

[0059] In step S220, based on the multiple frames of the first ultrasound image of the first scanning section, the duration of the first cardiac cycle corresponding to the first scanning section is determined;

[0060] In step S230, based on the duration of the first cardiac cycle, a first heart rate corresponding to the first cardiac cycle is determined;

[0061] In step S240, a plurality of frames of second ultrasound images of a second scanning section of a heart portion of the target object are acquired, wherein the second scanning section is different from the first scanning section;

[0062] In step S250, based on the multiple frames of second ultrasound images of the second scanning section, the duration of the second cardiac cycle corresponding to the second scanning section is determined;

[0063] In step S260, based on the duration of the second cardiac cycle, a second heart rate corresponding to the second cardiac cycle is determined;

[0064] In step S270, based on the first heart rate and the second heart rate, the heart rate variability between the first scanning plane and the second scanning plane is determined.

[0065] The parameter measurement method 200 based on cardiac ultrasound of the embodiment of the present invention provides a basis for judging the reliability of parameter measurement results by calculating the heart rate variability between different scanning sections, thereby improving the measurement accuracy and reliability of parameter measurement.

[0066] The method of the embodiment of the present invention can be used to perform real-time quantitative analysis on the cardiac ejection fraction. The ejection fraction EF is the percentage of the cardiac stroke volume to the ventricular end-diastolic volume, reflecting the efficiency of the ventricular pumping function. Usually EF is related to myocardial contractility. The stronger the myocardial contractility, the greater the stroke volume and the greater the EF. Generally, the EF of a normal person in a quiet state is about 50% or more. In clinical anesthesia practice, the EF index can reflect the normality of heart function earlier than the stroke volume. When patients with cardiovascular diseases undergo cardiovascular surgery, transesophageal echocardiography can be used during anesthesia to continuously perform real-time quantitative analysis of the cardiac ejection fraction.

[0067] In one example, the processor of the ultrasound imaging system may perform cardiac function analysis in response to an instruction for starting cardiac function analysis. Optionally, taking ejection fraction analysis as an example, the ultrasound imaging system may also have a key for starting ejection fraction analysis mode, which may be a physical key or a hot key, etc. When the processor detects an operation on the key, the operation may be, for example, clicking, touching, pressing, etc. Parameters related to cardiac function may be measured based on steps S210 to S270.

[0068] Cardiac function analysis includes but is not limited to ejection fraction analysis or myocardial stress and strain analysis, wherein, in ejection fraction analysis mode, the scanning section type may be apical two-chamber heart view (A2C) and apical four-chamber heart view (A4C), while the scanning section type for myocardial stress and strain analysis may be apical two-chamber heart view (A2C), apical four-chamber heart view (A4C) and apical three-chamber heart view (A3C). Hereinafter, the method of the present application is mainly explained and illustrated by taking ejection fraction analysis as an example, but the method of the present application may also be applicable to myocardial stress and strain analysis.

[0069] In one embodiment, in step S210 and step S240, multiple frames of first ultrasound images of a first scanning section of the heart part of the target object are obtained and multiple frames of second ultrasound images of a second scanning section of the heart part of the target object are obtained, wherein the second scanning section is different from the first scanning section, and optionally, the first scanning section and the second scanning section can be an apical two-chamber heart view (A2C) and an apical four-chamber heart view (A4C). The multiple frames of first ultrasound images and the multiple frames of second ultrasound images can be acquired in real time by an ultrasound imaging system or read from a memory. The multiple frames of first ultrasound images and the multiple frames of second ultrasound images can be obtained by scanning the heart part of the target object in real time. The multiple frames of first ultrasound images and the multiple frames of second ultrasound images can be any suitable mode images, such as B-mode ultrasound images, M-mode ultrasound images or images of other suitable modes. In some embodiments, the ultrasound image may be a transthoracic / transesophageal echocardiogram (TTE / TEE). Transthoracic / transesophageal echocardiogram (TTE / TEE) can display the heart's morphological structure, ventricular wall motion, and hemodynamic information in real time. It has the advantages of being instant, safe, convenient, inexpensive, and operable at bedside, making it easy to track and follow up. It has become a commonly used non-invasive cardiac function assessment technology.

[0070] In order to make the result of parameter measurement more accurate, the method of the present application also includes: identifying the first ultrasound image, and determining the standard degree of the first ultrasound image according to the preset conditions satisfied by the identification result, and identifying the second ultrasound image, and determining the standard degree of the second ultrasound image according to the preset conditions satisfied by the identification result, wherein the standard degree includes multiple levels, each level corresponds to a different preset condition, and each level is used to characterize the different standard degrees of the first ultrasound image and the second ultrasound image. By pre-identifying and analyzing the standard degree of each acquired ultrasound image, it is possible to avoid the negative impact on the calculation of subsequent cardiac function analysis due to the section type not meeting the requirements, and it is also possible to output a prompt when the section type does not meet the requirements, so that the doctor can adjust the scanning position in time to obtain an ultrasound image with a section type that meets the requirements.

[0071] The standard degree of the ultrasound image of the scanned section can be reasonably set based on prior experience. Optionally, the standard degree of the ultrasound image of the scanned section can include multiple levels, each level is used to represent a different standard degree of the ultrasound image of the scanned section, for example, a higher level represents a higher standard degree, or a lower level represents a higher standard degree, which can be reasonably set according to needs. The number of multiple levels divided by the standard degree can be reasonably set based on prior experience, for example, it can be 3 levels, 4 levels, 5 levels, 6 levels, 8 levels, etc., and each level can also be represented in the form of a score.

[0072] In one example, the multiple levels include a first level, a second level, a third level, and a fourth level, wherein the standard degree of the ultrasonic image of the scanning section corresponding to the first level is greater than the standard degree of the ultrasonic image of the scanning section corresponding to the second level, the standard degree of the ultrasonic image of the scanning section corresponding to the second level is greater than the standard degree of the ultrasonic image of the scanning section corresponding to the third level, the standard degree of the ultrasonic image of the scanning section corresponding to the third level is greater than the standard degree of the ultrasonic image of the scanning section corresponding to the fourth level, and the preset range is not lower than the third level.

[0073] In one example, taking the left ventricle as an example, a first ultrasound image is identified, and the standard degree of the first ultrasound image is determined according to the preset conditions satisfied by the identification result, and a second ultrasound image is identified, and the standard degree of the second ultrasound image is determined according to the preset conditions satisfied by the identification result, including: when it is identified that the ultrasound image (such as the first ultrasound image, the second ultrasound image, the third ultrasound image, etc.) of each scanning section (such as the first scanning section, the second scanning section, the third scanning section, etc.) satisfies the first preset condition, then the standard degree of the corresponding ultrasound image is determined to be the first level, and the first preset condition includes the following conditions: the scanning section type corresponding to the ultrasound image is a first predetermined type, for example, the section type of the ultrasound image is an apical two-chamber heart section or an apical four-chamber heart section, and the chamber ( That is, the number and completeness of the presented chambers meet the requirements) for example, all chambers are presented roughly completely, and the side walls and ventricular septum of the chambers are clearly imaged, and this level represents the section type standard; when it is identified that the ultrasound image of at least one scanning section meets the second preset condition, the standard degree of the ultrasound image of at least one scanning section is determined to be the second level, and the second preset condition includes the following conditions: the section type of the ultrasound image of at least one scanning section is the apical two-chamber view or the apical four-chamber view, and the chambers are presented in the ultrasound image of at least one scanning section (that is, the number and completeness of the presented chambers meet the requirements), for example, all chambers are presented roughly completely, but the outer wall of the ventricle or the ventricular septum is not clearly imaged or partially invisible, and the imaging noise exceeds the preset requirement, that is, the imaging noise is relatively large, etc. The second level represents the general standard of the section type. When it is identified that the ultrasound image of at least one scanned section meets the third preset condition, the standard degree of the ultrasound image of at least one scanned section is determined to be the third level, and the third preset condition includes the following conditions: the section type of the ultrasound image is the apical three-chamber view (A3C), the apical five-chamber view (A5C), the apical two-chamber view (A2C) with invisible atria, the tilted apical two-chamber view (A2C) (i.e., the crooked A2C), the apical four-chamber view (A4C) with invisible atria, or the tilted apical four-chamber view (A4C) (i.e., the crooked A2C). crooked A4C), etc., the third level indicates that the section type is no longer standard; when it is identified that the ultrasound image meets the fourth preset condition, the standard degree of the ultrasound image is determined to be the fourth level, and the fourth preset condition includes the following conditions: extremely poor imaging quality, the ultrasound image does not present or only presents part of the ventricular outline, the ultrasound image section type is other section types except the apical two-chamber view, the apical three-chamber view, the apical four-chamber view, and the apical five-chamber view, such as short axis, parasternal long axis, etc. The fourth level indicates that the section type has no standard, that is, it no longer meets the measurement requirements.

[0074] The above preset conditions can also be reasonably adjusted according to actual needs. They are only used as examples and do not constitute limitations.

[0075] In one example, the method of the present application further includes: displaying prompt information corresponding to the standard degree of the first ultrasound image and the standard degree of the second ultrasound image, so that the user can obtain the standard degree of the scanning section type of the ultrasound image of the current frame in real time, and adjust the probe position in time when the standard degree of the ultrasound image of the scanning section does not meet the requirements. Figure 3 As shown, the prompt information 310 corresponding to the standard degree of the current scanning section of the ultrasound image of the current frame (such as the first ultrasound image, the second ultrasound image, the third ultrasound image, etc.) displayed on the display interface is displayed. Figure 3 In the figure, the prompt information 310 is represented by a circular pattern of a preset color, wherein when the standard degree is the aforementioned third level, the circular pattern of the preset color may be a yellow circular pattern, thereby serving as a warning to the user, so as to prompt the user to appropriately adjust the scanning position of the probe to obtain an ultrasound image with a higher standard degree of the section type, thereby improving the accuracy of the subsequent ejection fraction analysis.

[0076] The prompt information corresponding to the standard degree of the ultrasound image of the current scanned section can be displayed in any suitable display manner, for example, a text description corresponding to the standard degree can be displayed on the display interface of the display, or represented by a preset graphic, etc. In one example, the standard degree includes multiple levels, and the prompt information corresponding to the standard degree of the ultrasound image of the current scanned section is displayed in the display interface, including: displaying the prompt information corresponding to at least some of the levels in a differentiated display manner in the display interface, wherein the differentiated display manner includes at least one of the following manners: the prompt information corresponding to at least some of the levels is displayed in different colors, the prompt information corresponding to at least some of the levels is displayed in different graphics, the prompt information corresponding to at least some of the levels is displayed in different background patterns, the prompt information corresponding to at least some of the levels is displayed in flashing, and the prompt information corresponding to at least some of the levels is displayed in highlighting. For example, when the standard degree includes multiple levels, such as the aforementioned first level, second level, third level and fourth level, each level can be displayed in a different display mode, or levels with similar levels and basically the same impact on the test results can use the same display mode, while levels with greatly different impact on the test results can use different display modes. For example, including the aforementioned first level, second level, third level and fourth level, wherein the first level and the second level both meet the section type requirements, the same display mode can be used, such as displaying a green pattern to represent the first level and the second level, and although the third level can also measure and obtain results, if the ultrasound probe changes again, it is easy to cause the standard degree of the section type to further deteriorate, so the third level can use a display mode different from the first level and the second level, such as using a yellow pattern to represent the third level, and because the fourth level may cause the obtained ejection fraction analysis result to be inaccurate, a display mode different from the aforementioned levels can be used, such as using a red pattern to represent the fourth level.

[0077] In other examples, when the level of the standard degree exceeds the preset threshold range, for example, when the level is the aforementioned third level and / or fourth level, a prompt message corresponding to the level exceeding the preset threshold range may be displayed in a differentiated display manner in the display interface to prompt the user to adjust the position of the ultrasound probe. Alternatively, when the level is within the preset threshold range, no prompt may be given.

[0078] When the standard degree of the scanned section meets the requirements, the steps of identification based on ultrasound images can be performed. In step S220, based on the multiple frames of the first ultrasound image of the first scanned section, the duration of the first cardiac cycle corresponding to the first scanned section is determined, including: identifying the ventricle in the first ultrasound image, determining the volume curve representing the ventricular volume; based on the volume curve, determining the duration of the first cardiac cycle corresponding to the first scanned section. In step S250, based on the multiple frames of the second ultrasound image of the second scanned section, the duration of the second cardiac cycle corresponding to the second scanned section is determined, including: identifying the ventricle in the second ultrasound image, determining the volume curve representing the ventricular volume; based on the volume curve, determining the duration of the second cardiac cycle corresponding to the second scanned section. It is worth mentioning that in the present application, when the ventricle is the left ventricle, the first scanned section and the second scanned section refer to the apical two-chamber heart section (A2C) and the apical four-chamber heart section (A4C).

[0079] For example, taking the left ventricle as an example, continue to refer to Figure 3 As shown, the left ventricular endocardial recording 320 can be automatically performed in real time, and the left ventricular volume can be calculated, and the volume curve can be drawn in real time, wherein an implementation effect of the volume curve 330 is as follows Figure 3 It is worth mentioning that the left ventricular endocardial tracing 320 may not be displayed in the ultrasound image. It is worth mentioning that the volume curve of the ventricle may be obtained by obtaining the volume of the ventricle in each frame of ultrasound image based on the calculation method described below in this application, or may be calculated based on other suitable methods.

[0080] Optionally, the volume curve is displayed in a predetermined area on the ultrasound image displayed on the display interface. The predetermined area may be any suitable area on the ultrasound image, such as the lower side, upper side, left side or right side of the ultrasound image.

[0081] Among them, the standard degree judgment of the section presented in the ultrasound image and the ventricle identification such as left ventricular endocardial tracing can be realized by a multi-task parallel trained deep learning network (wherein the task of standard degree judgment is a classification task, and the task of left ventricular endocardial tracing is a left ventricular segmentation task), and the training process of the deep learning network is to train the above two tasks. The main network model of the deep learning network can be implemented by UNet and the like.

[0082] The ventricular volume can be calculated in real time based on the Simpson single plane method or other suitable methods to obtain a volume curve. Specifically, the calculation method of the Simpson single plane method is well known to those skilled in the art. For example, the ventricular volume corresponding to each frame of ultrasound image is calculated using the Simpson single plane method, which may include the following steps: identifying the endocardial contour in each frame of ultrasound image, and measuring the apical long axis diameter of the ventricle in the endocardial contour; dividing the ventricle into a plurality of disc-shaped blocks along a direction perpendicular to the apical long axis diameter, and setting the cross section of the disc-shaped block to a circle; based on the plurality of disc-shaped blocks, calculating and obtaining the ventricular volume, for example, calculating the volume of each disc-shaped block, and summing the volumes of the plurality of disc-shaped blocks to obtain the ventricular volume. Optionally, the plurality of disc-shaped blocks have the same height. Optionally, the number of the plurality of disc-shaped blocks divided along the apical long axis diameter can be reasonably set according to actual needs, for example, it can be 20 disc-shaped blocks of equal height, or, 30 disc-shaped blocks of equal height. Optionally, the plurality of disc-shaped blocks have the same height.

[0083] It is worth mentioning that the apical long axis diameter refers to the length from the mitral valve annulus plane to the apex.

[0084] For each scanning section, such as the first scanning section, the second scanning section, and the third scanning section, the method for determining the duration of the cardiac cycle corresponding to each scanning section is generally the same. In some embodiments, based on the volume curve corresponding to each scanning section, the duration of the cardiac cycle corresponding to each scanning section is determined, including: based on the volume curve, identifying the ventricular end diastole (ED) and the ventricular end systole (ES) of each cardiac cycle, for example, identifying the maximum volume and the minimum volume in each cardiac cycle in the volume curve, wherein the maximum volume corresponds to the ventricular end diastole, and the minimum volume corresponds to the ventricular end systole, that is, the volume at the end of diastole. The volume at the end of systole is the maximum value within a cardiac cycle, and the volume at the end of systole is the minimum value within a cardiac cycle. In the process of real-time identification, the algorithm for identifying the end of diastole and the end of systole will be activated only after more than one cardiac cycle. The ED / ES pair is determined by the process of real-time calculation of the maximum value in the first preset curve segment in the volume curve and the minimum value in the second preset curve segment after the first preset curve segment, wherein the number of frames represented by the "first preset curve segment and the second preset curve segment" is proportional to the setting of the frame rate, and the maximum value and the minimum value cannot be the leftmost and rightmost values ​​of the "first preset curve segment and the second preset curve segment". The first preset curve segment may refer to the curve segment corresponding to the preset number of frames, and the second preset curve segment may refer to the curve segment corresponding to the preset number of frames. It is worth mentioning that the interval between the maximum value and the minimum value cannot exceed one cardiac cycle. In some embodiments, the duration of each cardiac cycle can also be determined based on the time interval between the image frame corresponding to the end of ventricular diastole of the next ventricle and the image frame corresponding to the end of ventricular diastole of the previous ventricle, and the heart rate refers to the number of heartbeats per minute, which can be equal to the number of cardiac cycles included in one minute. In some embodiments, the heart rate can also be calculated based on the following method, for example, HR=60s / t, t is the duration of the cardiac cycle, t=(ED2-ED1) / FPS, where ED2 is the frame sequence number of the image frame corresponding to the next ventricular diastole, ED1 is the frame sequence number of the image frame corresponding to the previous ventricular diastole, and FPS is the number of frames transmitted per second, for example, ED2 is the 20th frame, ED1 is the 10th frame, and FPS is 10 frames per second, then t is 1s, and HR is 60. By analogy, the heart rate (HR) corresponding to each cardiac cycle can be calculated by calculating the duration of each cardiac cycle.

[0085] By using the aforementioned heart rate calculation method, a first heart rate corresponding to the first cardiac cycle and a second heart rate corresponding to the second cardiac cycle can be determined, and then step S270 is performed to determine the heart rate variability between the first scanning section and the second scanning section based on the first heart rate and the second heart rate. For example, the heart rate variability is calculated based on the following formula:

[0086] HR_erro=|HR1-HR2| / max(HR1,HR2)

[0087] Wherein, HR_erro is the heart rate variability, HR1 is the first heart rate of the first cardiac cycle corresponding to the first scanning section, and HR2 is the second heart rate of the second cardiac cycle corresponding to the second scanning section.

[0088] Among them, the number of first cardiac cycles can be 1, the number of second cardiac cycles can be 1, then a heart rate variability can be calculated, and when the number of first cardiac cycles is multiple, the number of second cardiac cycles is multiple, the number of heart rate variability is multiple.

[0089] In some embodiments, the method of the present application also includes displaying heart rate variability so that the user can intuitively view the heart rate variability, thereby determining whether the first cardiac cycle and the second cardiac cycle used for parameter measurement meet the requirements, and determining whether the results obtained from the parameter measurement based on the first cardiac cycle and the second cardiac cycle, such as the ejection fraction value, are reliable, thereby providing the accuracy and precision of the parameter measurement, wherein generally, the smaller the heart rate variability, the more it represents a match between the first cardiac cycle and the second cardiac cycle, and the higher the accuracy of the calculated corresponding parameters and the higher the credibility.

[0090] In some embodiments, the method of the present application further includes outputting a first prompt message when the heart rate variability exceeds a first preset threshold, such as Figure 4A As shown, the first prompt information may be a text description and / or a graphic prompt, etc., and the first prompt information may also be highlighted by adding a background color to the text description, for example, Figure 4A As shown, the first prompt information is "HRVariation>10%", and is prompted with a yellow background. The first prompt information can also be displayed on the presented ultrasound image or outside the ultrasound image, for example, the prompt information area of ​​the main interface displays the second prompt information. In some embodiments, Figure 4A As shown, it is also possible to indicate through graphic prompts that the heart rate variability exceeds the first preset threshold, such as changing the color, shape or thickness of the curve segment of the corresponding cardiac cycle in the presented volume curve, for example, presenting the curve segment in yellow, while if it is normal, the volume curve is green.

[0091] Optionally, the first preset threshold may be reasonably set according to actual needs. For example, the first preset threshold may be less than or equal to 15%, such as 15%, 10%, 5%, etc.

[0092] In some embodiments, the method further includes: determining a first apical long axis diameter of the ventricle based on a first ultrasound image corresponding to a specific frame in a first cardiac cycle, and determining a second apical long axis diameter of the ventricle based on a second ultrasound image corresponding to a specific frame in a second cardiac cycle; and calculating the amount of apical shortening between the first apical long axis diameter and the second apical long axis diameter. By calculating the amount of apical shortening between different scanning sections, the measurement accuracy of parameter measurement is improved, and the reliability of the measurement result is improved.

[0093] Optionally, the specific frame may be any suitable image frame, for example, the specific frame may be an image frame corresponding to the end of ventricular diastole, or other suitable image frames. Based on the aforementioned method, specific frames in the first cardiac cycle and the second cardiac cycle, such as image frames at the end of ventricular diastole, may be determined, and endocardial tracing may be performed on the ventricles in the ultrasound images corresponding to the specific frames (such as the first ultrasound image, the second ultrasound image, the third ultrasound image, etc.) to obtain the endocardial contour, and the apical long axis diameter (LVLd) of the ventricles may be measured in the endocardial contour.

[0094] For example, the amount of apical shortening is calculated based on the following formula:

[0095] LVLd_erro=|LVLd 1-LVLd 2| / max(LVLd 1,LVLd 2)

[0096] Wherein, LVLd_erro is the amount of apical shortening, LVLd 1 is the first apical long-axis diameter corresponding to the first cardiac cycle of the first scanning section, and LVLd 2 is the second apical long-axis diameter corresponding to the second cardiac cycle of the second scanning section.

[0097] In some embodiments, the method of the present application further includes: displaying the amount of apical shortening. By displaying the amount of apical shortening, the user can be assisted in judging the reliability of the measured parameters such as the ejection fraction value, so as to re-measure in time when there is a problem with the reliability. The amount of apical shortening can be displayed on an ultrasound image or in other suitable locations.

[0098] In other embodiments, the method of the present application further includes: when the amount of apical shortening exceeds a second preset threshold, outputting a second prompt message. The second prompt message may be a text description or an icon, etc., and the second prompt message may be highlighted by adding a background color to the text description. The second prompt message may also be displayed on the presented ultrasound image or outside the ultrasound image, for example, the second prompt message may be displayed in the prompt message area of ​​the main interface, etc. Figure 4BAs shown, the second prompt information is "LVL Variation>10%", and is prompted by a yellow background. Displaying the amount of apical shortening can assist the user in judging the reliability of measured parameters such as ejection fraction values, so that the user can re-measure in time when there is a problem with the reliability, thereby improving the accuracy and precision of parameter measurement.

[0099] Optionally, the second preset threshold may be reasonably set according to actual needs. For example, the first preset threshold may be less than or equal to 15%, such as 15%, 10%, 5%, etc.

[0100] In some embodiments, the method of the present application further includes: outputting third prompt information that the first apical long axis diameter is too small or the second apical long axis diameter is too small, and the third prompt information can be represented in any suitable form, for example, the third prompt information can be represented in text, graphics or other suitable ways, or the marking line of the first apical long axis diameter or the second apical long axis diameter with a small diameter on the ultrasound image can be highlighted, for example, the color of the marking line can be changed or the marking line can be thickened, for example, yellow or red can be used for marking, such as Figure 4B As shown, if the long axis diameter of the first apex corresponding to the A2C section is too small, its marking line 410 is presented in yellow, while if the long axis diameter of the second apex corresponding to the A4C section is normal, its marking line is presented in a color different from yellow, such as green.

[0101] It is worth mentioning that in Figure 4A and Figure 4B In the interface shown, hot keys such as "Accept" or "Cancel" may also be displayed, and the user may trigger the corresponding process by operating these hot keys. For example, operating the "Accept" hot key means accepting the test result, while "Cancel" may trigger re-measurement, or any other suitable process may be used.

[0102] In some embodiments, there are multiple first cardiac cycles, multiple second cardiac cycles, multiple heart rate variability, and multiple apical shortening amounts, wherein each heart rate variability is obtained based on a first heart rate corresponding to any first cardiac cycle and a second heart rate corresponding to any second cardiac cycle, and each apical shortening amount is obtained based on a first apical long-axis diameter corresponding to any first cardiac cycle and a second apical long-axis diameter corresponding to any second cardiac cycle. The method of the present application also includes: based on multiple groups of heart rate variability and apical shortening amounts, determining multiple corresponding matching scores, wherein each group of heart rate variability and apical shortening amounts includes a heart rate variability and an apical shortening amount corresponding to the same any first cardiac cycle and any second cardiac cycle, and each matching score is used to indicate the degree of matching between any first cardiac cycle and any second cardiac cycle; based on multiple matching scores, determining the first cardiac cycle and the second cardiac cycle whose matching scores meet preset conditions among the multiple first cardiac cycles and the multiple second cardiac cycles. By matching the cardiac cycles between different scanning sections through heart rate variability and apical shortening, a matched first cardiac cycle and a matched second cardiac cycle are obtained, thereby improving the measurement accuracy of cardiac function analysis and the reliability of measurement results. In addition, by automatically matching the cardiac cycles between different scanning sections for parameter measurement, the operation is simpler and the credibility of the measurement results is high.

[0103] In some embodiments, the matching score between any first cardiac cycle and any second cardiac cycle can be calculated using the following formula:

[0104] scores=w1*(1-HR_erro)+w2*(1-LVLd_erro)

[0105] Among them, scores is the matching score, HR_erro is the heart rate variability, LVLd_erro is the apical shortening, W1 and W2 are weight coefficients respectively. The specific coefficients of W1 and W2 can be reasonably set according to actual needs. At this time, the first and second cardiac cycles whose matching scores meet the preset conditions can be the first and second cardiac cycles corresponding to the highest matching scores.

[0106] In other embodiments, the matching score between any first cardiac cycle and any second cardiac cycle may be calculated using the following formula:

[0107] scores=w1*HR_erro+w2*LVLd_erro

[0108] Among them, scores is the matching score, HR_erro is the heart rate variability, LVLd_erro is the apical shortening, W1 and W2 are weight coefficients respectively. Then, the first cardiac cycle and the second cardiac cycle whose matching scores meet the preset conditions can be the first cardiac cycle and the second cardiac cycle corresponding to the lowest matching score.

[0109] The imaging quality of an image within a cardiac cycle will affect the recording effect of the left ventricular endocardium, especially for the ED / ES section, and ultimately affect the accuracy of the measurement result. Therefore, the image quality of the ultrasound image corresponding to each cardiac cycle (for example, the first cardiac cycle, the second cardiac cycle, the third cardiac cycle, etc.) can also be scored. Taking the scoring of multiple frames of first ultrasound images corresponding to the first scanning section as an example, the quality of the first ultrasound image is analyzed to determine a first evaluation score of the first ultrasound image corresponding to each first cardiac cycle in the multiple first cardiac cycles, including: obtaining a first image quality confidence of multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular diastole in each first cardiac cycle in the multiple first cardiac cycles, and a second image quality confidence of multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular systole; based on the first image quality confidence and the second image quality confidence, calculating the first evaluation score of the first ultrasound image corresponding to each first cardiac cycle in the multiple first cardiac cycles.

[0110] It is worth mentioning that the image frame corresponding to the end-diastole of the ventricle may refer to the ultrasound image frame used to calculate the ejection fraction, and the multiple frames of ultrasound images adjacent to the image frame corresponding to the end-diastole of the ventricle may refer to the ultrasound images of the first preset frame number before the image frame corresponding to the end-diastole of the ventricle, or, refer to the ultrasound images of the second preset frame number after the image frame corresponding to the end-diastole of the ventricle, or, refer to the ultrasound images of the first preset frame number before the image frame corresponding to the end-diastole of the ventricle and the ultrasound images of the second preset frame number after the image frame corresponding to the end-diastole of the ventricle. The image frame corresponding to the end of ventricular contraction may refer to an ultrasonic image frame used to calculate the ejection fraction, and the multiple frames of ultrasonic images adjacent to the image frame corresponding to the end of ventricular contraction may refer to ultrasonic images of the first preset frame number before the image frame corresponding to the end of ventricular contraction, or, ultrasonic images of the second preset frame number after the image frame corresponding to the end of ventricular contraction, or, ultrasonic images of the first preset frame number before the image frame corresponding to the end of ventricular contraction and ultrasonic images of the second preset frame number after the image frame corresponding to the end of ventricular contraction, wherein the first preset frame number and the second preset frame number can be any frame numbers that can be reasonably set according to actual needs, but it is worth mentioning that the preset frame number can be image frames within the same cardiac cycle.

[0111] For example, the first evaluation score Qef of the first ultrasound image corresponding to each first cardiac cycle in the plurality of first cardiac cycles may be calculated by the following formula:

[0112]

[0113] The first image quality confidence Qed can be calculated based on any suitable method, for example, the first image quality confidence Qed can be calculated by the following steps: automatically obtaining the confidence of each frame of ultrasound image in multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular diastole in each cardiac cycle; wherein the confidence is used to characterize the quality of the ultrasound image, and the image quality confidence of each ultrasound image can be obtained by any suitable intelligent analysis method, which is not specifically limited herein; then, the image quality confidence of each frame of ultrasound image adjacent to the end of ventricular diastole is respectively assigned a corresponding weight value, the weight value is determined by the distance between each frame of ultrasound image and the image frame corresponding to the end of ventricular diastole, and the farther the distance, the smaller the weight value, wherein the distance can refer to the number of intervals or the time intervals, for example, an ultrasound image with a first number of frames interval from the image frame corresponding to the end of ventricular diastole corresponds to a first weight, and an ultrasound image with a second number of frames interval from the image frame corresponding to the end of ventricular diastole corresponds to a second weight, wherein if the first number of frames is less than the second number of frames, then the first weight is greater than the second weight. Finally, the confidence of each frame of ultrasound image is multiplied by the weight value corresponding to each frame of ultrasound image and then added to obtain a first sum; the first sum is averaged to obtain a first confidence.

[0114] Similarly, based on a method substantially similar to the first image quality confidence, a second image quality confidence of multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular contraction in each cardiac cycle can be automatically obtained, including: automatically obtaining the image quality confidence of each frame of ultrasound image in the multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular contraction in each cardiac cycle; assigning corresponding weight values ​​to the confidence of each frame of ultrasound image in the multiple frames of ultrasound images adjacent to the image frame corresponding to the end of ventricular contraction, wherein the weight value is determined by the distance between each frame of ultrasound image and the image frame corresponding to the end of ventricular contraction, and the farther the distance, the smaller the weight value; multiplying the confidence of each frame of ultrasound image by the weight value corresponding to each frame of ultrasound image, and then adding the results to obtain the sum of the second image quality confidence; averaging the sum of the second image quality confidence to obtain the second image quality confidence.

[0115] Specifically, the first image quality confidence Qed and the second image quality confidence Qes can be calculated by the following formula:

[0116]

[0117] Among them, score i Indicates the image quality confidence of the ultrasound image of the frame near ED / ES, MAXSCORE is 1, weights iRepresents the weight value of the ultrasound image of the frame near ED / ES.

[0118] In some embodiments, there are multiple first cardiac cycles, multiple second cardiac cycles, multiple heart rate variability, and multiple apical shortening amounts, wherein each heart rate variability is obtained based on a first heart rate corresponding to any first cardiac cycle and a second heart rate corresponding to any second cardiac cycle, and each apical shortening amount is obtained based on a first apical long-axis diameter corresponding to any first cardiac cycle and a second apical long-axis diameter corresponding to any second cardiac cycle. The method also includes: analyzing the quality of the first ultrasound image to determine a first evaluation score of the first ultrasound image corresponding to each of the multiple first cardiac cycles, and analyzing the quality of the second ultrasound image to determine a first evaluation score of each of the multiple second cardiac cycles. a second evaluation score of the second ultrasound image corresponding to the second cardiac cycle; based on multiple groups of heart rate variability, apical shortening, first evaluation score and second evaluation score, determine multiple corresponding matching scores, each group of heart rate variability, apical shortening, first evaluation score and second evaluation score includes: a heart rate variability, an apical shortening, a first evaluation score and a second evaluation score corresponding to the same any first cardiac cycle and any second cardiac cycle, and each matching score is used to indicate the degree of matching between any first cardiac cycle and any second cardiac cycle; based on multiple matching scores, determine the first cardiac cycle and the second cardiac cycle whose matching scores meet the preset conditions in the multiple first cardiac cycles and the multiple second cardiac cycles. Matching of cardiac cycles between different scanning sections is performed through heart rate variability, apical shortening, first evaluation score and second evaluation score to obtain matched first cardiac cycle and second cardiac cycle, thereby improving the measurement accuracy of cardiac function analysis and the reliability of measurement results, and by automatically matching cardiac cycles between different scanning sections for parameter measurement, the operation is simpler and the reliability of measurement results is high.

[0119] In some embodiments, the matching score can be calculated based on the following formula: scores = w1*(1-HR_erro)+w2*(1-LVLd_erro)+w3*Qcycle

[0120] Among them, scores is the matching score, HR_erro is the heart rate variability, LVLd_erro is the amount of apical shortening, Qcycle is the sum of the first evaluation score and the second evaluation score, and W1, W2, and W3 are weight coefficients. The specific values ​​of the weight coefficients can be reasonably set according to actual needs. Among them, the first and second cardiac cycles that are matched can be the cardiac cycles corresponding to the highest matching scores among multiple matching scores.

[0121] It is worth mentioning that in the present application, before calculating the matching score, heart rate variability and / or apical shortening can be used for screening, for example, heart rate variability less than a first preset threshold is screened out, and then the matching score is calculated in combination with the corresponding apical shortening, etc., or, apical shortening less than a second preset threshold is screened out, and then the matching score is calculated in combination with the corresponding heart rate variability area, or, corresponding to the same group of first cardiac cycle and second cardiac cycle, or, corresponding to the same group of first cardiac cycle, second cardiac cycle and third cardiac cycle, and the heart rate variability less than the first preset threshold and the apical shortening less than the second preset threshold, etc. are used to calculate the matching score.

[0122] Further, after matching the first cardiac cycle and the second cardiac cycle that meet the preset conditions, the method of the present application further includes: calculating the first ventricular volume of the ventricle at the end of ventricular diastole based on the first ultrasound image corresponding to the end of ventricular diastole in the matched first cardiac cycle and the second ultrasound image corresponding to the end of ventricular diastole in the matched second cardiac cycle; calculating the second ventricular volume of the ventricle at the end of ventricular systole based on the first ultrasound image corresponding to the end of ventricular systole in the matched first cardiac cycle and the second ultrasound image corresponding to the end of ventricular systole in the matched second cardiac cycle; calculating the ejection fraction based on the first ventricular volume and the second ventricular volume; and displaying the ejection fraction. The matched first cardiac cycle and the second cardiac cycle are also the first cardiac cycle and the second cardiac cycle whose matching scores meet the preset conditions.

[0123] Further, based on the first ultrasound image corresponding to the end of ventricular diastole in the matched first cardiac cycle and the second ultrasound image corresponding to the end of ventricular diastole in the matched second cardiac cycle, calculating the first ventricular volume of the ventricle at the end of ventricular diastole may include: obtaining the first endocardial contour in the first ultrasound image corresponding to the end of ventricular diastole, and obtaining the second endocardial contour in the first ultrasound image corresponding to the end of ventricular diastole; measuring the first apical long axis diameter of the ventricle in the first endocardial contour and measuring the second apical long axis diameter of the ventricle in the second endocardial contour; dividing the ventricle into a plurality of disc-shaped blocks along a direction perpendicular to the first apical long axis diameter and dividing the ventricle into a plurality of disc-shaped blocks along a direction perpendicular to the second apical long axis diameter; setting the cross-sections of the plurality of disc-shaped blocks to an ellipse, wherein the size of the ellipse is determined based on the second apical long axis diameter; and calculating and obtaining the first ventricular volume based on the divided plurality of disc-shaped blocks. Optionally, the plurality of disc-shaped blocks have the same height. The second ventricular volume may be calculated based on a similar method, which will not be described in detail herein.

[0124] The number of the plurality of disk-shaped blocks can be reasonably set according to actual needs, for example, it can be 20 disk-shaped blocks of equal height, or 30 disk-shaped blocks of equal height. Figure 5As shown, for the A4C section, it is divided into 20 disk-shaped blocks ai along its apical long axis diameter LVL4, and the height of each disk-shaped block is H=LVL4 / 20. For the A2C section, it is divided into 20 disk-shaped blocks bi along its apical long axis diameter LVL2, and the height of each disk-shaped block is H=LVL2 / 20.

[0125] It is worth mentioning that the specific calculation method of the Simpson biplane method is well known to those skilled in the art and will not be described in detail here.

[0126] Furthermore, the first ventricular volume (eg, ventricular end-diastolic volume EDV) and the second ventricular volume (ie, ventricular end-systolic volume ESV) of each cardiac cycle may be calculated, and then the cardiac ejection fraction of the cardiac cycle, such as the left ventricular ejection fraction, may be calculated.

[0127] Specifically, the ejection fraction (EF) can be calculated by the following formula:

[0128]

[0129] The ejection fraction may be displayed in any suitable form, such as displaying the ejection fraction simultaneously with the image frames used to calculate the ejection fraction.

[0130] In addition to being applicable to ejection fraction, the method of the present application can also be applied to the calculation of stress and strain such as global longitudinal strain (GLS) using the three-section method. For example, the method of the present application further includes: obtaining multiple frames of third ultrasound images of the third scanning section of the heart of the target object; determining the duration of the third cardiac cycle corresponding to the third scanning section based on the multiple frames of the third ultrasound images of the third scanning section; determining the third heart rate corresponding to the third cardiac cycle based on the duration of the third cardiac cycle; determining the heart rate variability between the first cardiac cycle, the second cardiac cycle and the third cardiac cycle based on the first heart rate, the second heart rate and the third heart rate. By calculating the heart rate variability between the three sections, medical staff can be assisted in judging the reliability of parameter measurement results.

[0131] Optionally, the third scanning section may refer to A3C or other suitable sections, wherein the calculation method of the third heart rate may refer to the relevant description above and will not be repeated here.

[0132] Optionally, the heart rate variability between the three heart rates can be obtained by calculating the absolute values ​​of the differences between the two hearts, summing them up, and then averaging them, or other suitable calculation methods can be used.

[0133] Furthermore, the method of the present application also includes: determining the first apical long axis diameter of the ventricle based on the first ultrasound image corresponding to the specific frame in the first cardiac cycle, determining the second apical long axis diameter of the ventricle based on the second ultrasound image corresponding to the specific frame in the second cardiac cycle, and determining the third apical long axis diameter of the ventricle based on the third ultrasound image corresponding to the specific frame in the third cardiac cycle; calculating the apical shortening amount between the first apical long axis diameter, the second apical long axis diameter and the third apical long axis diameter. The calculation method of the third apical long axis diameter can refer to the relevant description in the previous text and will not be repeated here.

[0134] Optionally, the amount of apical shortening between the three apical long-axis diameters can be obtained by calculating the absolute values ​​of the differences between the two values, summing them up, and then averaging them, or other suitable calculation methods can be used.

[0135] Further, in some embodiments, the number of first cardiac cycles is multiple, the number of second cardiac cycles is multiple, the number of third cardiac cycles is multiple, the number of heart rate variability is multiple, the number of apical shortening is multiple, each heart rate variability is obtained based on a first heart rate corresponding to any first cardiac cycle, a second heart rate corresponding to any second cardiac cycle, and a third heart rate corresponding to any third cardiac cycle, and each apical shortening is obtained based on a first apical long-axis diameter corresponding to any first cardiac cycle, a second apical long-axis diameter corresponding to any second cardiac cycle, and a third apical long-axis diameter corresponding to any third cardiac cycle. The method of the present application also includes: analyzing the quality of the first ultrasound image to determine a first evaluation score of the first ultrasound image corresponding to each first cardiac cycle in the multiple first cardiac cycles; analyzing the quality of the second ultrasound image to determine a second evaluation score of the second ultrasound image corresponding to each second cardiac cycle in the multiple second cardiac cycles; analyzing the quality of the third ultrasound image to determine a third ultrasound image corresponding to each third cardiac cycle in the multiple third cardiac cycles. a third evaluation score; based on multiple groups of heart rate variability, apical shortening, first evaluation scores, second evaluation scores and third evaluation scores, corresponding matching scores are determined, each group of heart rate variability, apical shortening, first evaluation score, second evaluation score and third evaluation score includes: a heart rate variability, an apical shortening, a first evaluation score, a second evaluation score and a third evaluation score corresponding to the same any first cardiac cycle, any second cardiac cycle and any third cardiac cycle, each matching score is used to represent the degree of matching between any first cardiac cycle, any second cardiac cycle and any third cardiac cycle; based on multiple matching scores, a first cardiac cycle, a second cardiac cycle and a third cardiac cycle whose matching scores meet a preset condition are determined from among multiple first cardiac cycles, multiple second cardiac cycles and multiple third cardiac cycles; based on a first ultrasonic image corresponding to the determined first cardiac cycle, a second ultrasonic image corresponding to the determined second cardiac cycle and a third ultrasonic image corresponding to the determined third cardiac cycle, myocardial stress and strain of the target object are analyzed. By matching the cardiac cycles between different scanning sections through heart rate variability, apical shortening, the first evaluation score, the second evaluation score, and the third evaluation score, the matched first cardiac cycle, the second cardiac cycle, and the third cardiac cycle are obtained, thereby improving the measurement accuracy of cardiac function analysis and the reliability of measurement results. In addition, by automatically matching the cardiac cycles between different scanning sections for parameter measurement, the operation is simpler and the credibility of the measurement results is high.

[0136] Specifically, the calculation method of the matching score may refer to the relevant description above. When there are three slices, Qcycle may be the sum of the first evaluation score, the second evaluation score and the third evaluation score.

[0137] Specifically, the myocardial stress strain analysis method may use any suitable method, which will not be described in detail here.

[0138] In summary, the parameter measurement method based on cardiac ultrasound and the ultrasonic imaging system according to the embodiments of the present invention provide a basis for judging the reliability of the parameter measurement results by calculating the heart rate variability between different scanning sections, thereby improving the measurement accuracy and reliability of the parameter measurement. Compared with traditional methods, the method of the present application is more convenient and faster, and the accuracy of the measured parameters is higher, thereby improving the efficiency of doctors in clinically diagnosing patients' cardiac function.

[0139] Another embodiment of the present application also provides a parameter measurement method based on cardiac ultrasound, such as Figure 6 As shown, the method 600 includes steps S610 to S640:

[0140] Step S610, acquiring a plurality of frames of first ultrasound images of a first scanning section of a heart portion of a target object;

[0141] Step S620: acquiring multiple frames of second ultrasound images of a second scanning section of the heart of the target object;

[0142] Step S630 determines a first apical long-axis diameter of the ventricle based on a first ultrasound image corresponding to a specific frame in a first cardiac cycle corresponding to the first scanning section, and determines a second apical long-axis diameter of the ventricle based on a second ultrasound image corresponding to a specific frame in a second cardiac cycle corresponding to the second scanning section;

[0143] Step S640 calculates the apical shortening amount between the first apical major axis diameter and the second apical major axis diameter.

[0144] In some embodiments, the method of the present application further includes: displaying the amount of apical shortening; and / or, when the amount of apical shortening exceeds a second preset threshold, outputting a second prompt message.

[0145] In some embodiments, the method of the present application further includes: outputting third prompt information that the first apex long axis diameter is too small or the second apex long axis diameter is too small.

[0146] In some embodiments, the method of the present application further comprises:

[0147] Acquire multiple frames of third ultrasound images of a third scanning section of the heart of the target object;

[0148] determining a third apical long-axis diameter of the ventricle based on a third ultrasound image corresponding to a specific frame in a third cardiac cycle corresponding to a third scanning section;

[0149] The amount of apical shortening between the first apical long-axis diameter, the second apical long-axis diameter, and the third apical long-axis diameter was calculated.

[0150] For details of each step in this embodiment, please refer to the relevant description above and will not be repeated here.

[0151] According to the cardiac ultrasound-based parameter measurement method and ultrasound imaging system of the embodiments of the present invention, by calculating the amount of apical shortening between different scanning sections, a basis is provided for judging the reliability of parameter measurement results, thereby improving the measurement accuracy and reliability of parameter measurement.

[0152] The embodiment of the present invention further provides an ultrasound imaging system, which is used to implement the above-mentioned parameter measurement method 200 based on cardiac ultrasound or the parameter measurement method 600 based on cardiac ultrasound. The ultrasound imaging system includes an ultrasound probe, a transmitting circuit, a receiving circuit, a processor and a display. Figure 1 , the ultrasound imaging system can be implemented as follows Figure 1 The ultrasound imaging system 100 shown may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116 and a display 118. Optionally, the ultrasound imaging system 100 may also include a transmit / receive selection switch 120 and a beamforming module 122. The transmitting circuit 112 and the receiving circuit 114 may be connected to the ultrasound probe 110 via the transmit / receive selection switch 120. The relevant description of each component may refer to the relevant description above and will not be repeated here.

[0153] Among them, the transmitting circuit 112 is used to control the ultrasonic probe 110 to transmit ultrasonic waves to the target area including the heart valve; the receiving circuit 114 is used to control the ultrasonic probe 110 to receive the echo of the ultrasonic wave returned from the target area to obtain an ultrasonic echo signal; the processor 116 is used to perform ultrasonic imaging based on the ultrasonic echo signal; the processor 116 is also used to execute the above-mentioned cardiac ultrasound-based parameter measurement method 200 or the cardiac ultrasound-based parameter measurement method 600; when the processor 116 executes the cardiac ultrasound-based parameter measurement method 200 or the cardiac ultrasound-based parameter measurement method 600, the display 118 is used to display any visual information, such as at least displaying the ejection fraction, and can also be used to display the ultrasonic image of the current frame, etc.

[0154] The above only describes the main functions of the components of the ultrasound imaging system. For more details, please refer to the relevant description of the parameter measurement method 200 based on cardiac ultrasound or the parameter measurement method 600 based on cardiac ultrasound, which will not be repeated here.

[0155] Although example embodiments have been described herein with reference to the accompanying drawings, it should be understood that the above example embodiments are merely exemplary and are not intended to limit the scope of the present invention thereto. Various changes and modifications may be made therein by one of ordinary skill in the art without departing from the scope and spirit of the present invention. All such changes and modifications are intended to be included within the scope of the present invention as required by the appended claims.

[0156] Those skilled in the art will appreciate that the units and algorithm steps of each example described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of the present invention.

[0157] In the several embodiments provided by the present invention, it should be understood that the disclosed devices and methods can be implemented in other ways. For example, the device embodiments described above are only schematic, for example, the division of units is only a logical function division, and there may be other division methods in actual implementation, such as multiple units or components can be combined or integrated into another device, or some features can be ignored or not executed.

[0158] In the description provided herein, a large number of specific details are described. However, it is understood that embodiments of the present invention can be practiced without these specific details. In some instances, well-known methods, structures and techniques are not shown in detail so as not to obscure the understanding of this description.

[0159] Similarly, it should be understood that in order to streamline the present invention and help understand one or more of the various inventive aspects, in the description of the exemplary embodiments of the present invention, the various features of the present invention are sometimes grouped together into a single embodiment, figure, or description thereof. However, the method of the present invention should not be interpreted as reflecting the following intention: the claimed invention requires more features than the features explicitly stated in each claim. More specifically, as reflected in the corresponding claims, the inventive point is that the corresponding technical problem can be solved with less than all the features of a single disclosed embodiment. Therefore, the claims following the specific embodiment are hereby expressly incorporated into the specific embodiment, wherein each claim itself serves as a separate embodiment of the present invention.

[0160] It will be understood by those skilled in the art that, except for mutually exclusive features, all features disclosed in this specification (including the accompanying claims, abstracts and drawings) and all processes or units of any method or device disclosed in this specification may be combined in any combination. Unless otherwise expressly stated, each feature disclosed in this specification (including the accompanying claims, abstracts and drawings) may be replaced by an alternative feature that provides the same, equivalent or similar purpose.

[0161] In addition, those skilled in the art will appreciate that, although some embodiments herein include certain features included in other embodiments but not other features, the combination of features of different embodiments is meant to be within the scope of the present invention and form different embodiments. For example, in the claims, any one of the claimed embodiments may be used in any combination.

[0162] The various component embodiments of the present invention can be implemented in hardware, or in software modules running on one or more processors, or in a combination thereof. It should be understood by those skilled in the art that a microprocessor or digital signal processor (DSP) can be used in practice to implement some or all of the functions of some modules according to embodiments of the present invention. The present invention can also be implemented as a device program (e.g., a computer program and a computer program product) for executing part or all of the methods described herein. Such a program implementing the present invention can be stored on a computer-readable medium, or can have the form of one or more signals. Such a signal can be downloaded from an Internet website, or provided on a carrier signal, or provided in any other form.

[0163] It should be noted that the above embodiments illustrate rather than limit the invention, and that those skilled in the art may devise alternative embodiments without departing from the scope of the appended claims. In the claims, any reference symbol between brackets shall not be construed as a limitation on the claims. The present invention may be implemented by means of hardware comprising a number of different elements and by means of a suitably programmed computer. In a unit claim enumerating a number of means, several of these means may be embodied by the same hardware item. The use of the words first, second, and third, etc., does not indicate any order. These words may be interpreted as names.

[0164] The above is only a specific embodiment or description of a specific embodiment of the present invention, and the protection scope of the present invention is not limited thereto. Any person skilled in the art who is familiar with the technical field can easily think of changes or substitutions within the technical scope disclosed by the present invention, which should be included in the protection scope of the present invention. The protection scope of the present invention shall be based on the protection scope of the claims.

Claims

1. A parameter measurement method based on cardiac ultrasound, characterized in that: The method comprises: Acquire a plurality of frames of first ultrasound images of a first scanning section of a heart portion of a target object; Determining the duration of a first cardiac cycle corresponding to the first scanning section based on the multiple frames of the first ultrasound image of the first scanning section; Determining a first heart rate corresponding to the first cardiac cycle based on the duration of the first cardiac cycle; Acquire multiple frames of second ultrasound images of a second scanning section of a heart portion of the target object, wherein the second scanning section is different from the first scanning section; Determining the duration of a second cardiac cycle corresponding to the second scanning section based on the multiple frames of second ultrasound images of the second scanning section; determining a second heart rate corresponding to the second cardiac cycle based on the duration of the second cardiac cycle; Based on the first heart rate and the second heart rate, the heart rate variability between the first scanning plane and the second scanning plane is determined.

2. The method according to claim 1, characterized in that The method further includes: displaying the heart rate variability; and / or, when the heart rate variability exceeds a first preset threshold, outputting a first prompt message.

3. The method according to claim 1, characterized in that The method further comprises: Determine a first apical long-axis diameter of the ventricle based on the first ultrasound image corresponding to a specific frame in the first cardiac cycle, and determine a second apical long-axis diameter of the ventricle based on the second ultrasound image corresponding to the specific frame in the second cardiac cycle; An amount of apical shortening between the first apical major axis diameter and the second apical major axis diameter is calculated.

4. The method according to claim 3, characterized in that The method further includes: displaying the apical shortening amount; and / or, when the apical shortening amount exceeds a second preset threshold, outputting a second prompt message.

5. The method according to claim 3, characterized in that The method further includes: outputting third prompt information that the first apex long-axis diameter is too small or the second apex long-axis diameter is too small.

6. The method according to claim 3, characterized in that There are multiple first cardiac cycles, multiple second cardiac cycles, multiple heart rate variability, and multiple apical shortening amounts, wherein each heart rate variability is obtained based on the first heart rate corresponding to any one of the first cardiac cycles and the second heart rate corresponding to any one of the second cardiac cycles, and each apical shortening amount is obtained based on the first apical long-axis diameter corresponding to any one of the first cardiac cycles and the second apical long-axis diameter corresponding to any one of the second cardiac cycles, and the method further includes: Based on multiple groups of the heart rate variability and the apical shortening, a corresponding plurality of matching scores are determined, wherein each group of the heart rate variability and the apical shortening includes a heart rate variability and an apical shortening corresponding to the same any one of the first cardiac cycles and any one of the second cardiac cycles, and each matching score is used to indicate a matching degree between any one of the first cardiac cycles and any one of the second cardiac cycles; Based on the plurality of matching scores, a first cardiac cycle and a second cardiac cycle whose matching scores satisfy a preset condition are determined from among the plurality of the first cardiac cycles and the plurality of the second cardiac cycles.

7. The method according to claim 3, characterized in that There are multiple first cardiac cycles, multiple second cardiac cycles, multiple heart rate variability, and multiple apical shortening amounts, wherein each heart rate variability is obtained based on the first heart rate corresponding to any one of the first cardiac cycles and the second heart rate corresponding to any one of the second cardiac cycles, and each apical shortening amount is obtained based on the first apical long-axis diameter corresponding to any one of the first cardiac cycles and the second apical long-axis diameter corresponding to any one of the second cardiac cycles, and the method further includes: Analyzing the quality of the first ultrasound image to determine a first evaluation score of the first ultrasound image corresponding to each of the plurality of first cardiac cycles, and analyzing the quality of the second ultrasound image to determine a second evaluation score of the second ultrasound image corresponding to each of the plurality of second cardiac cycles; Based on multiple groups of the heart rate variability, the apical shortening, the first evaluation score and the second evaluation score, a corresponding plurality of matching scores are determined, each group of the heart rate variability, the apical shortening, the first evaluation score and the second evaluation score comprising: one heart rate variability, one apical shortening, one first evaluation score and one second evaluation score corresponding to the same any one of the first cardiac cycles and any one of the second cardiac cycles, each matching score being used to indicate the degree of matching between any one of the first cardiac cycles and any one of the second cardiac cycles; Based on the plurality of matching scores, a first cardiac cycle and a second cardiac cycle whose matching scores satisfy a preset condition are determined from among the plurality of the first cardiac cycles and the plurality of the second cardiac cycles.

8. The method according to claim 7, characterized in that Analyzing the quality of the first ultrasound image to determine a first evaluation score of the first ultrasound image corresponding to each first cardiac cycle in the plurality of first cardiac cycles includes: Acquire a first image quality confidence of a plurality of ultrasound image frames adjacent to an image frame corresponding to the end of ventricular diastole in each of a plurality of the first cardiac cycles, and a second image quality confidence of a plurality of ultrasound image frames adjacent to an image frame corresponding to the end of ventricular systole; A first evaluation score of a first ultrasound image corresponding to each of the first cardiac cycles in a plurality of the first cardiac cycles is calculated based on the first image quality confidence level and the second image quality confidence level.

9. The method according to claim 6 or 7, characterized in that The method further comprises: Calculate a first ventricular volume of the ventricle at the end of ventricular diastole based on a first ultrasound image corresponding to the end of ventricular diastole in the first cardiac cycle and a second ultrasound image corresponding to the end of ventricular diastole in the second cardiac cycle in which the matching scores meet a preset condition; Calculate the second ventricular volume of the ventricle at the end of ventricular contraction based on the first ultrasound image corresponding to the end of ventricular contraction in the first cardiac cycle and the second ultrasound image corresponding to the end of ventricular contraction in the second cardiac cycle in the first cardiac cycle whose matching scores meet the preset condition; calculating an ejection fraction based on the first ventricular volume and the second ventricular volume; The ejection fraction is displayed.

10. The method according to any one of claims 1 to 9, characterized in that Determining the duration of a first cardiac cycle corresponding to the first scanning section based on a plurality of frames of first ultrasound images of a first scanning section of a heart portion of the target object obtained includes: identifying a ventricle in the first ultrasound image and determining a volume curve representing the volume of the ventricle; Based on the volume curve, a duration of a first cardiac cycle corresponding to the first scanning section is determined.

11. The method according to any one of claims 1 to 10, characterized in that Also includes: Identify the first ultrasonic image and determine the standard degree of the first ultrasonic image according to the preset conditions satisfied by the identification result, and identify the second ultrasonic image and determine the standard degree of the second ultrasonic image according to the preset conditions satisfied by the identification result, wherein the standard degree includes multiple levels, each level corresponds to a different preset condition, and each level is used to represent a different standard degree of the first ultrasonic image and the second ultrasonic image; Prompt information corresponding to the standard degree of the first ultrasound image and the standard degree of the second ultrasound image is displayed.

12. The method according to any one of claims 1 to 11, characterized in that The method further comprises: Acquire multiple frames of third ultrasound images of a third scanning section of the heart of the target object; Determining the duration of a third cardiac cycle corresponding to the third scanning section based on the multiple frames of third ultrasound images of the third scanning section; Determining a third heart rate corresponding to the third cardiac cycle based on the duration of the third cardiac cycle; The step of determining the heart rate variability between the first scanning section and the second scanning section based on the first heart rate and the second heart rate includes: Based on the first heart rate, the second heart rate and the third heart rate, heart rate variability between the first cardiac cycle, the second cardiac cycle and the third cardiac cycle is determined.

13. The method according to claim 12, characterized in that The method further comprises: determining a first apical long-axis diameter of the ventricle based on the first ultrasound image corresponding to the specific frame in the first cardiac cycle, determining a second apical long-axis diameter of the ventricle based on the second ultrasound image corresponding to the specific frame in the second cardiac cycle, and determining a third apical long-axis diameter of the ventricle based on the third ultrasound image corresponding to the specific frame in the third cardiac cycle; The apical shortening amount between the first apical long-axis diameter, the second apical long-axis diameter, and the third apical long-axis diameter is calculated.

14. The method according to claim 13, characterized in that The number of the first cardiac cycles is multiple, the number of the second cardiac cycles is multiple, the number of the third cardiac cycles is multiple, the number of the heart rate variability is multiple, the number of the apical shortening is multiple, each of the heart rate variability is obtained based on the first heart rate corresponding to any one of the first cardiac cycles, the second heart rate corresponding to any one of the second cardiac cycles, and the third heart rate corresponding to any one of the third cardiac cycles, and each of the apical shortening is obtained based on the first apical long axis diameter corresponding to any one of the first cardiac cycles, the second apical long axis diameter corresponding to any one of the second cardiac cycles, and the third apical long axis diameter corresponding to any one of the third cardiac cycles, and the method further includes: Analyze the quality of the first ultrasound image to determine a first evaluation score of the first ultrasound image corresponding to each first cardiac cycle in the plurality of first cardiac cycles; Analyze the quality of the second ultrasound image to determine a second evaluation score of the second ultrasound image corresponding to each of the second cardiac cycles in a plurality of the second cardiac cycles; Analyze the quality of the third ultrasound image to determine a third evaluation score of the third ultrasound image corresponding to each of the third cardiac cycles in the plurality of third cardiac cycles; Based on multiple groups of the heart rate variability, the apical shortening, the first evaluation score, the second evaluation score and the third evaluation score, corresponding matching scores are determined, each group of the heart rate variability, the apical shortening, the first evaluation score, the second evaluation score and the third evaluation score comprises: one heart rate variability, one apical shortening, one first evaluation score, one second evaluation score and one third evaluation score corresponding to the same any one of the first cardiac cycle, any one of the second cardiac cycle and any one of the third cardiac cycle, each matching score is used to indicate the degree of matching between any one of the first cardiac cycle, any one of the second cardiac cycle and any one of the third cardiac cycle; Based on the plurality of matching scores, determining a first cardiac cycle, a second cardiac cycle, and a third cardiac cycle whose matching scores meet a preset condition from among the plurality of the first cardiac cycles, the plurality of the second cardiac cycles, and the plurality of the third cardiac cycles; The myocardial stress and strain of the target object are analyzed based on the determined first ultrasound image corresponding to the first cardiac cycle, the determined second ultrasound image corresponding to the second cardiac cycle, and the determined third ultrasound image corresponding to the third cardiac cycle.

15. The method according to any one of claims 1 to 14, characterized in that The first scanning section is an apical two-chamber heart section, and the second scanning section is an apical four-chamber heart section.

16. A parameter measurement method based on cardiac ultrasound, characterized in that: The method comprises: Acquire a plurality of frames of first ultrasound images of a first scanning section of a heart portion of a target object; Acquire multiple frames of second ultrasound images of a second scanning section of the heart of the target object; Determine a first apical long-axis diameter of the ventricle based on the first ultrasound image corresponding to a specific frame in a first cardiac cycle corresponding to the first scanning section, and determine a second apical long-axis diameter of the ventricle based on the second ultrasound image corresponding to the specific frame in a second cardiac cycle corresponding to the second scanning section; An amount of apical shortening between the first apical major axis diameter and the second apical major axis diameter is calculated.

17. The method according to claim 16, characterized in that The method further includes: displaying the apical shortening amount; and / or, when the apical shortening amount exceeds a second preset threshold, outputting a second prompt message.

18. The method according to claim 16, characterized in that The method further includes: outputting third prompt information that the first apex long-axis diameter is too small or the second apex long-axis diameter is too small.

19. The method according to claim 16, characterized in that The method further comprises: Acquire multiple frames of third ultrasound images of a third scanning section of the heart of the target object; Determine a third apical long-axis diameter of the ventricle based on the third ultrasound image corresponding to the specific frame in the third cardiac cycle corresponding to the third scanning section; The apical shortening amount between the first apical long-axis diameter, the second apical long-axis diameter, and the third apical long-axis diameter is calculated.

20. An ultrasonic imaging system, characterized in that: The ultrasonic imaging system comprises: Ultrasound probe; A transmitting circuit, used for controlling the ultrasonic probe to transmit ultrasonic waves toward the heart of the target object; A receiving circuit, used for receiving an ultrasonic echo based on the ultrasonic wave returned from the heart part to obtain an ultrasonic echo signal; A processor, configured to acquire ultrasound images of at least two scanning sections of a heart portion of a target object according to the ultrasound echo signal; A memory for storing executable program instructions; A processor, configured to execute the program instructions stored in the memory, so that the processor executes the parameter measurement method based on cardiac ultrasound according to any one of claims 1 to 19; A display for displaying visual information.

Images