CN116138806A - Method and system for analyzing cardiac ejection fraction and ultrasonic imaging system - Google Patents
Method and system for analyzing cardiac ejection fraction and ultrasonic imaging system Download PDFInfo
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Abstract
A method and system for analyzing cardiac ejection fraction and an ultrasound imaging system, the method comprising: acquiring an ultrasonic image corresponding to the end diastole of a ventricle and an ultrasonic image corresponding to the end systole of the ventricle in each cardiac cycle based on the ultrasonic image of at least one scanning section of the heart part of the target object acquired in real time; automatically determining a first ventricular volume at end diastole and a second ventricular volume at end systole of each cardiac cycle based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole of each cardiac cycle; and automatically analyzing and acquiring the heart ejection fraction corresponding to each cardiac cycle in real time based on the first chamber volume and the second chamber volume of each cardiac cycle. According to the scheme, the cardiac ejection fraction corresponding to each cardiac cycle can be automatically analyzed and obtained in real time, and the cardiac function of a patient can be monitored in real time.
Description
Technical Field
The invention relates to the technical field of ultrasonic imaging, in particular to a method and a system for analyzing cardiac ejection fraction and an ultrasonic imaging system.
Background
The heart is a dynamic organ of the human body that maintains normal blood circulation. The left ventricular contractile function is a key index reflecting heart hemodynamics, and has important clinical values for diagnosis, disease monitoring, curative effect evaluation and prognosis judgment of various cardiovascular diseases (including ischemic heart disease, cardiomyopathy, heart valve disease, congenital heart disease and the like). Ejection fraction (Ejection Fractions, EF for short) is the percentage of heart stroke volume to ventricular end-diastole volume, reflecting the efficiency of ventricular pumping, and ejection fraction such as left ventricular ejection fraction (Left Ventricular Ejection Fractions, LVEF for short) is one of the most commonly used and important indicators for evaluating left ventricular overall contractility.
Echocardiography is a current classical imaging method for assessing ventricular function, e.g., left ventricle. The method for measuring the volume of a ventricle such as a left ventricle by using an ultrasonic cardiogram is mainly based on a Simpson single/double plane method at present, wherein the single plane method usually uses an off-line film to trace and calculate EF on the left ventricle manually or semi-automatically or automatically, the accuracy of calculation is low by using the single plane method, the efficiency of clinical diagnosis of the heart function of a doctor is reduced, and the double plane method needs to select 4 sections of systolic and diastolic phases of (A2C) and four-chamber heart of the apex (A4C) simultaneously for operation by using the double plane method, so that the process is complicated, and a large time is required for obtaining the EF value.
Disclosure of Invention
In the summary, a series of concepts in a simplified form are introduced, which will be further described in detail in the detailed description. The summary of the invention is not intended to define the key features and essential features of the claimed subject matter, nor is it intended to be used as an aid in determining the scope of the claimed subject matter.
In one aspect, embodiments of the present invention provide a method of analyzing cardiac ejection fraction, the method comprising: acquiring an ultrasonic image corresponding to the end diastole of a ventricle and an ultrasonic image corresponding to the end systole of the ventricle in each cardiac cycle based on the ultrasonic image of at least one scanning section of the heart part of the target object acquired in real time; automatically determining a first ventricular volume at end diastole and a second ventricular volume at end systole of each cardiac cycle based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole of each cardiac cycle; and automatically analyzing and acquiring the heart ejection fraction corresponding to each cardiac cycle in real time based on the first chamber volume and the second chamber volume of each cardiac cycle.
A second aspect of an embodiment of the invention provides a method of analyzing cardiac ejection fraction, the method comprising: acquiring ejection fraction corresponding to a plurality of cardiac cycles of heart tissue of a target object and ejection fraction confidence corresponding to each ejection fraction; determining, based on the ejection fraction confidence, an ejection fraction of at least one of a plurality of cardiac cycles as an analysis result; and outputting the analysis result.
A third aspect of an embodiment of the present invention provides an ultrasound imaging system, comprising:
an ultrasonic probe;
a transmitting circuit for controlling the ultrasonic probe to transmit ultrasonic waves to a heart part of a target object;
the receiving circuit is used for receiving the ultrasonic echo based on the ultrasonic wave returned from the heart part to obtain an ultrasonic echo signal;
the processor is used for acquiring an ultrasonic image of at least one scanning section of the heart part in real time according to the ultrasonic echo signals;
a memory for storing executable program instructions;
a processor for executing the program instructions stored in the memory, causing the processor to perform the aforementioned method of analyzing cardiac ejection fraction;
And the display is used for displaying the visual information.
A fourth aspect of an embodiment of the invention provides a system for analyzing cardiac ejection fraction, the system comprising:
a memory for storing executable program instructions;
a processor for executing the program instructions stored in the memory, causing the processor to perform the aforementioned method of analyzing cardiac ejection fraction;
and the display is used for displaying the visual information.
According to the method and the system for analyzing the cardiac ejection fraction and the ultrasonic imaging system, the cardiac ejection fraction corresponding to each cardiac cycle can be automatically and real-time analyzed and obtained, the cardiac function of a patient can be monitored in real time, and compared with a traditional single-sided method and a traditional double-sided method, the method and the system for analyzing the cardiac ejection fraction are more convenient and quick, the accuracy of the ejection fraction is higher, and the efficiency of clinical diagnosis of the cardiac function of the patient by a doctor is further improved.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings that are needed in the description of the embodiments will be briefly described below, it being obvious that the drawings in the following description are only some embodiments of the present invention, and that other drawings may be obtained according to these drawings without inventive effort to a person skilled in the art.
In the drawings:
FIG. 1 shows a schematic block diagram of an ultrasound imaging system according to an embodiment of the invention;
FIG. 2 shows a schematic flow chart of a method of analyzing cardiac ejection fraction according to an embodiment of the present invention;
FIG. 3 shows a schematic flow chart of a method of analyzing cardiac ejection fraction according to another embodiment of the present invention;
FIG. 4 shows a schematic view of a tangent plane standard level prompt and endocardial tracing based on the identified standard level, in accordance with an embodiment of the present invention;
FIG. 5 is a schematic diagram showing calculation of volume by a single plane method and updating of curve volume in real time according to an embodiment of the present invention;
FIG. 6 shows a schematic diagram of the standard cut and measurement mode recommended by Simpson single/double planar method according to an embodiment of the invention;
FIG. 7 is a schematic diagram showing a volumetric curve marking ED/ES and prompting current EF confidence and a small window displaying ED/ES views and EF values corresponding to the ejection fraction with the highest current ejection fraction confidence according to an embodiment of the present invention;
FIG. 8 is a diagram showing information displayed by a display interface when calculating a biplane method EF based on the biplane method according to one embodiment of the present invention;
FIG. 9 shows a schematic diagram of an analysis report of output ejection fraction according to an embodiment of the present invention;
FIG. 10 shows a schematic flow chart of a method of analyzing cardiac ejection fraction according to yet another embodiment of the present invention;
FIG. 11 shows a schematic diagram of a system for analyzing cardiac ejection fraction according to an embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, exemplary embodiments according to the present invention will be described in detail with reference to the accompanying drawings. It should be apparent that the described embodiments are only some embodiments of the present invention and not all embodiments of the present invention, and it should be understood that the present invention is not limited by the example embodiments described herein. Based on the embodiments of the invention described in the present application, all other embodiments that a person skilled in the art would have without inventive effort shall fall within the scope of the invention.
In the following description, numerous specific details are set forth in order to provide a more thorough understanding of the present invention. It will be apparent, however, to one skilled in the art that the invention may be practiced without one or more of these details. In other instances, well-known features have not been described in detail in order to avoid obscuring the invention.
It should be understood that the present invention may be embodied in various forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. As used herein, the term "and/or" includes any and all combinations of the associated listed items.
In order to provide a thorough understanding of the present invention, detailed structures will be presented in the following description in order to illustrate the technical solutions presented by the present invention. Alternative embodiments of the invention are described in detail below, however, the invention may have other implementations in addition to these detailed descriptions.
In the following, an ultrasound imaging system according to an embodiment of the invention is first described with reference to fig. 1, fig. 1 showing a schematic block diagram of an ultrasound imaging system 100 according to an embodiment of the invention.
As shown in fig. 1, the ultrasound imaging system 100 includes an ultrasound probe 110, transmit circuitry 112, receive circuitry 114, a processor 116, and a display 118. Further, the ultrasound imaging system may further include a transmit/receive selection switch 120 and a beam synthesis module 122, and the transmit circuit 112 and the receive circuit 114 may be connected to the ultrasound probe 110 through the transmit/receive selection switch 120.
The ultrasonic probe 110 includes a plurality of transducer elements, and the plurality of transducer elements may be arranged in a row to form a linear array or in a two-dimensional matrix to form an area array, and the plurality of transducer elements may also form a convex array. The transducer array elements are used for transmitting ultrasonic waves according to the excitation electric signals or converting received ultrasonic waves into electric signals, so that each transducer array element can be used for realizing the mutual conversion of electric pulse signals and ultrasonic waves, thereby realizing the transmission of ultrasonic waves to tissues of a target area of a tested object, and also can be used for receiving ultrasonic wave echoes reflected by the tissues. In the ultrasonic detection, the transmission sequence and the receiving sequence can control which transducer array elements are used for transmitting ultrasonic waves and which transducer array elements are used for receiving ultrasonic waves, or control the transducer array elements to be used for transmitting ultrasonic waves or receiving echo waves in a time slot mode. The transducer array elements participating in ultrasonic wave transmission can be excited by the electric signals at the same time, so that ultrasonic waves are transmitted at the same time; alternatively, the transducer elements involved in the transmission of the ultrasound beam may also be excited by several electrical signals with a certain time interval, so as to continuously transmit ultrasound waves with a certain time interval.
During ultrasound imaging, the transmit circuit 112 transmits the delay-focused transmit pulse to the ultrasound probe 110 through the transmit/receive selection switch 120. The ultrasonic probe 110 is excited by the emission pulse to emit an ultrasonic beam to the tissue of the target region of the object to be measured, receives the ultrasonic echo with the tissue information reflected from the tissue of the target region after a certain delay, and reconverts the ultrasonic echo into an electrical signal. The receiving circuit 114 receives the electrical signals converted by the ultrasonic probe 110, obtains ultrasonic echo signals, and sends the ultrasonic echo signals to the beam forming module 122, and the beam forming module 122 performs focusing delay, weighting, channel summation and other processes on the ultrasonic echo data, and then sends the ultrasonic echo signals to the processor 116. The processor 116 performs signal detection, signal enhancement, data conversion, logarithmic compression, etc. on the ultrasonic echo signals to form an ultrasonic image. The ultrasound images obtained by the processor 116 may be displayed on the display 118 or may be stored in the memory 124.
Alternatively, the processor 116 may be implemented as software, hardware, firmware, or any combination thereof, and may use single or multiple application specific integrated circuits (Application Specific Integrated Circuit, ASIC), single or multiple general purpose integrated circuits, single or multiple microprocessors, single or multiple programmable logic devices, or any combination of the foregoing circuits and/or devices, or other suitable circuits or devices. Also, the processor 116 may control other components in the ultrasound imaging system 100 to perform the respective steps of the methods in the various embodiments in this specification.
The display 118 is connected with the processor 116, and the display 118 may be a touch display screen, a liquid crystal display screen, or the like; alternatively, the display 118 may be a stand-alone display such as a liquid crystal display, television, or the like that is independent of the ultrasound imaging system 100; alternatively, the display 118 may be a display screen of an electronic device such as a smart phone, tablet, or the like. Wherein the number of displays 118 may be one or more.
The display 118 may display the ultrasound image obtained by the processor 116. In addition, the display 118 may provide a graphical interface for human-computer interaction while displaying the ultrasonic image, one or more controlled objects are provided on the graphical interface, and the user is provided with an operation instruction input by using the human-computer interaction device to control the controlled objects, so as to execute corresponding control operation. For example, icons are displayed on a graphical interface that can be manipulated using a human-machine interaction device to perform specific functions, such as drawing a region of interest box on an ultrasound image, etc.
Optionally, the ultrasound imaging system 100 may further include other human-machine interaction devices in addition to the display 118, which are coupled to the processor 116, for example, the processor 116 may be coupled to the human-machine interaction device through an external input/output port, which may be a wireless communication module, a wired communication module, or a combination of both. The external input/output ports may also be implemented based on USB, bus protocols such as CAN, and/or wired network protocols, among others.
The man-machine interaction device may include an input device for detecting input information of a user, and the input information may be, for example, a control instruction for an ultrasonic wave transmission/reception timing, an operation input instruction for drawing a point, a line, a frame, or the like on an ultrasonic image, or may further include other instruction types. The input device may include one or more of a keyboard, mouse, scroll wheel, trackball, mobile input device (e.g., a mobile device with a touch display, a cell phone, etc.), multi-function knob, etc. The human-machine interaction means may also comprise an output device such as a printer.
The ultrasound imaging system 100 may also include a memory 124 for storing instructions for execution by the processor, storing received ultrasound echoes, storing ultrasound images, and so forth. The memory may be a flash memory card, solid state memory, hard disk, or the like. Which may be volatile memory and/or nonvolatile memory, removable memory and/or non-removable memory, and the like.
It should be understood that the components included in the ultrasound imaging system 100 shown in fig. 1 are illustrative only and may include more or fewer components. The invention is not limited in this regard.
The method of analyzing cardiac ejection fraction according to the embodiment of the present invention is described below with reference to fig. 2, and fig. 2 is a schematic flowchart of a method 200 of analyzing cardiac ejection fraction according to the embodiment of the present invention. The method 200 for analyzing cardiac ejection fraction according to the embodiment of the present invention may be used in an ultrasound imaging system, where the ultrasound imaging system includes an ultrasound probe, a processor, and a display, and the ultrasound imaging system may be implemented as the ultrasound imaging system 100 described above, or the method 200 for analyzing cardiac ejection fraction according to the embodiment of the present invention may be used in a system for analyzing cardiac ejection fraction, where the system may be any computer device with a data processing function, etc., and where the system may obtain a real-time ultrasound image acquired by the ultrasound imaging system, an offline ultrasound image, etc., and specifically, the method 200 for analyzing cardiac ejection fraction according to the embodiment of the present invention includes the following steps:
in step S210, acquiring an ultrasound image corresponding to End Diastole (ED) and an ultrasound image corresponding to End Systole (ES) of a ventricle in each cardiac cycle based on the ultrasound image of at least one scan plane of the heart portion of the target object acquired in real time;
in step S220, a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricles in each cardiac cycle are automatically determined based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole of the ventricles in each cardiac cycle;
In step S230, based on the first ventricular volume and the second ventricular volume of each cardiac cycle, cardiac ejection fraction corresponding to each cardiac cycle is automatically obtained by real-time analysis.
The method 200 for analyzing cardiac ejection fraction of the embodiment of the invention can automatically analyze and acquire cardiac ejection fraction corresponding to each cardiac cycle in real time, is favorable for monitoring cardiac functions of patients in real time, is more convenient and rapid compared with the traditional single-sided method and double-sided method, has higher accuracy of ejection fraction, and further improves efficiency of clinical diagnosis of cardiac functions of patients by doctors.
The embodiment of the invention is used for carrying out real-time quantitative analysis on the cardiac ejection fraction. Ejection fraction EF is the percentage of cardiac stroke volume to ventricular end-diastole volume reflecting the efficiency of ventricular pumping. Generally, EF is related to the myocardial contractility, and the higher the myocardial contractility, the more stroke volume, the greater the EF, and generally, the EF is about 50% or more in a normal state of rest. In clinical anesthesia practice, EF index can reflect the normal or not of heart function earlier than heart stroke volume, cardiovascular operation is carried out on cardiovascular disease patient, and transesophageal echocardiography is applied in anesthesia, so that real-time quantitative analysis can be continuously carried out on heart ejection fraction.
The embodiment of the invention is used for carrying out real-time quantitative analysis on the cardiac ejection fraction, avoids reducing the efficiency of clinical diagnosis of cardiac function by a traditional method of manual operation, and in addition, along with the application of bedside ultrasound (POC) in real-time monitoring of cardiac function of acute and severe patients such as shock, acute dyspnea, sudden cardiac arrest, cardiopulmonary resuscitation and the like and the application of transesophageal ultrasound (TEE) in real-time monitoring of cardiac function in perioperative period, the real-time ejection fraction detection technology is urgently needed, so that the clinical cardiac function monitoring efficiency can be further improved by the real-time intelligent ejection fraction quantitative analysis technology, and the method has great significance for clinical application with real-time new function detection.
In one example, a processor of an ultrasound imaging system may conduct an analysis of ejection fraction in response to instructions for initiating an ejection fraction analysis mode. Optionally, the ultrasound imaging system may also have a key for turning on the ejection fraction analysis mode, which may be a physical key or a hot key, etc., when the processor detects an operation on the key, such as clicking, touching, pressing, etc. Analysis of ejection fraction may be performed based on step S210 to step S230.
In one embodiment, after entering the ejection fraction automatic analysis mode in step S210, the ultrasound probe scans at least one scan slice of the heart site of the target object in real time and acquires real-time ultrasound images, alternatively, taking the analysis of the left ventricular ejection fraction as an example, the scan slice type may be a cardiac apex two-chamber cardiac slice (A2C) or a cardiac apex four-chamber cardiac slice (A4C). The ultrasound images may be acquired in real time by the ultrasound imaging system or read from memory. The ultrasound image may be an ultrasound image of at least one scan slice of a heart site of the target object in real time. The ultrasound image may be any suitable mode image, such as a B-mode ultrasound image, an M-mode ultrasound image, or an image of other suitable mode. In some embodiments, the ultrasound image may be a transthoracic/transesophageal echocardiogram (TTE/TEE) which can display morphological structure, wall motion, and hemodynamic information of the heart in real time, and has advantages of being instant, safe, convenient, inexpensive, bedside-operable, and the like, facilitating tracking and follow-up, and has become a commonly used non-invasive cardiac function assessment technique at present.
In one example, the acquiring ultrasound images corresponding to end diastole and end systole of the heart in each cardiac cycle includes: automatically identifying in real-time a ventricle in the ultrasound image of the at least one scan slice and automatically acquiring in real-time volume data of the identified ventricle, optionally including but not limited to a volume curve; automatically identifying end diastole and end systole of the ventricles of each cardiac cycle based on the volume data; an ultrasound image corresponding to the identified end diastole of the ventricle and an ultrasound image corresponding to the identified end systole of the ventricle are acquired.
It should be noted that, in the present application, when the ventricle is the left ventricle, the at least one scan plane refers to a apical two-chamber heart plane (A2C) or a apical four-chamber heart plane (A4C).
In order to make the analysis result of the ejection fraction more accurate, the method of the present application further includes: before automatically identifying a ventricle in an ultrasonic image corresponding to the scanning section, automatically identifying the standard degree of the ultrasonic image of at least one scanning section in real time, and when the standard degree of the ultrasonic image is within a preset range, automatically identifying the ventricle in the ultrasonic image of the scanning section with the standard degree within the preset range in real time, and acquiring the volume data of the identified ventricle in real time. By identifying and analyzing the standard degree of each obtained ultrasonic image in advance, the negative influence on the subsequent analysis and the calculation of the ejection fraction due to the fact that the type of the section is not in accordance with the requirements can be avoided, and a prompt can be output when the type of the section is not in accordance with the requirements, so that a doctor can conveniently adjust the scanning position even to obtain the ultrasonic image with the section type in accordance with the requirements.
The standard level of the ultrasound image of the scan section may be reasonably set based on prior experience, alternatively, the standard level of the ultrasound image of the scan section may include a plurality of levels, each level being used to characterize a different standard level of the ultrasound image of the scan section, for example, the higher the level is, the higher the characterization standard level is, or the lower the level is, the higher the characterization standard level is, which may be reasonably set as needed. The number of the multiple levels divided by the standard degree can be reasonably set according to prior experience, for example, the multiple levels can be 3 levels, 4 levels, 5 levels, 6 levels, 8 levels and the like, and each level can be further characterized in a scoring form.
In one example, the plurality of levels includes a first level, a second level, a third level, and a fourth level, wherein the standard level of the ultrasound image of the scan plane corresponding to the first level is greater than the standard level of the ultrasound image of the scan plane corresponding to the second level, the standard level of the ultrasound image of the scan plane corresponding to the second level is greater than the standard level of the ultrasound image of the scan plane corresponding to the third level, the standard level of the ultrasound image of the scan plane corresponding to the third level is greater than the standard level of the ultrasound image of the scan plane corresponding to the fourth level, and the preset range is not lower than the third level.
In one example, taking the left ventricle as an example, the automatically identifying in real time the standard level of the ultrasound image of the at least one scan slice includes: when the ultrasonic image of at least one scanning section is identified to meet a first preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the first grade, wherein the first preset condition comprises the following conditions: the section type of the ultrasonic image is a heart apex two-cavity heart section or a heart apex four-cavity heart section, the at least one ultrasonic image of the scanned section presents chambers (namely, the number and the completeness of the presented chambers meet the requirements), for example, all chambers are presented in a complete mode, the imaging of the side walls and the chamber intervals of the chambers is clear, and the level represents the section type standard; when the ultrasonic image of at least one scanning section is identified to meet a second preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the second grade, wherein the second preset condition comprises the following conditions: the section type of the ultrasonic image of the at least one scanning section is a cardiac apex two-cavity section or a cardiac apex four-cavity section, the at least one ultrasonic image of the at least one scanning section presents the chambers (i.e. the number and the completeness of the presented chambers meet the requirements), for example, all the chambers are presented in a whole mode, but the imaging of the outer side wall or the ventricular septum of the ventricle is unclear or partially invisible, imaging noise exceeds the preset requirement, i.e. imaging noise is more, and the like, and the second level represents general standards of the section type. When the ultrasonic image of the at least one scanning section is identified to meet a third preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the third grade, wherein the third preset condition comprises the following conditions: the types of the sections of the ultrasonic image are a three-cavity heart section (A3C), a five-cavity heart section (A5C), a two-cavity heart section (A2C) with invisible atrium, a two-cavity heart section (A2C) with inclined position (namely, askew A2C), a four-cavity heart section (A4C) with invisible atrium or a four-cavity heart section (A4C) with inclined position (namely, askew A4C) and the like, and the third grade indicates that the types of the sections are not standard; when the ultrasonic image of the at least one scanning section is identified to meet a fourth preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the fourth grade, wherein the fourth preset condition comprises the following conditions: the imaging quality is extremely poor, the outline of a part of ventricles is not or only presented in the ultrasonic image of the at least one scanning section, the section types of the ultrasonic image are other section types except for a heart apex two-cavity heart section, a heart apex three-cavity heart section, a heart apex four-cavity heart section and a heart apex five-cavity heart section, such as a short axis, a parasternal long axis and the like, and the fourth grade indicates that the section type is nonstandard, i.e. does not meet the measurement requirement.
The above preset conditions can be reasonably adjusted according to actual needs, and are only examples and not limitations.
In one example, the method of the present application further comprises: and displaying prompt information corresponding to the standard degree of the ultrasonic image of the current scanning section in the display interface, so that a user can acquire the standard degree of the type of the scanning section of the ultrasonic image of the current frame in real time, and when the standard degree of the ultrasonic image of the scanning section does not meet the requirement, the position of the probe is adjusted in time. For example, as shown in fig. 4, in the prompt information 310 corresponding to the standard degree of the currently scanned section of the ultrasound image of the current frame displayed on the display interface, in fig. 4, the prompt information 310 is characterized by a circular pattern with a preset color, where when the standard degree is the aforementioned third level, the circular pattern with the preset color may be a yellow circular pattern, so as to play a role in early warning for the user, so as to prompt the user to appropriately adjust the scanning position of the probe, so as to obtain an ultrasound image with a section type with a higher standard degree, thereby improving the accuracy of the subsequent ejection fraction analysis.
The prompt information corresponding to the standard degree of the ultrasonic image of the current scanning section can be displayed in any suitable display mode, for example, a text description corresponding to the standard degree can be displayed on a display interface of the display, or a preset graph is used for representing, etc., in one example, the standard degree includes a plurality of grades, and the prompt information corresponding to the standard degree of the ultrasonic image of the current scanning section is displayed on the display interface, including: displaying prompt information corresponding to at least part of the grades in a distinguishing display mode in a display interface, wherein the distinguishing display mode comprises at least one of the following modes: at least part of the prompt messages corresponding to the grades are displayed in different colors, at least part of the prompt messages corresponding to the grades are displayed in different graphs, at least part of the prompt messages corresponding to the grades are displayed in different shading, at least part of the prompt messages corresponding to the grades are flash-displayed, and at least part of the prompt messages corresponding to the grades are highlighted. For example, when the standard level includes a plurality of levels including, for example, the aforementioned first level, second level, third level, and fourth level, each level may be displayed in a different display manner, or, alternatively, a level having a similar level and substantially identical effect on the test result may be displayed in the same display manner, and a level having a larger effect on the test result may be displayed in a different display manner, for example, including the aforementioned first level, second level, third level, and fourth level, wherein the first level and second level, which each satisfy the requirement of the section type, may be displayed in the same display manner, for example, displaying a green pattern to characterize the first level and the second level, and the third level, which may also measure the obtained result, may easily cause further deterioration in the standard level of the section type if the ultrasonic probe is changed, so that the third level may use a different display manner, for example, a yellow pattern to characterize the third level, and a fourth level may cause a red pattern to be displayed, for example, and an accurate analysis may be performed to characterize the result of the fourth level, which may not be displayed in the same manner as the red pattern.
In other examples, when the level of the standard level exceeds the preset threshold range, for example, when the level is the third level and/or the fourth level, prompt information corresponding to the level exceeding the preset threshold range is displayed in a distinguishing display mode in the display interface so as to prompt adjustment of the position of the ultrasonic probe. Alternatively, when the level is within the preset threshold, no prompt or the like may be performed.
When the standard level of the scan plane is within the preset range, for example, the standard level is the first level, the second level or the third level, the ventricles in the ultrasonic image of the scan plane with the standard level within the preset range are automatically identified in real time, and the volume data of the identified ventricles are acquired in real time, wherein the volume data comprises the ventricular volume of each frame of ultrasonic image and a volume curve obtained based on the real-time acquired ventricular volume depiction, for example, taking the left ventricle as an example, as shown in fig. 4, the left ventricle endocardial tracing 320 can be automatically performed in real time, and the left ventricle volume can be calculated, and the volume curve can be depicted in real time, wherein one implementation effect of the volume curve 330 is as shown in fig. 4. 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 acquiring of the volume data of the identified ventricle in real time may be the acquiring of the volume data of the ventricle in each frame of the ultrasound image based on the first calculation method described in the present application, or may be the acquiring of the volume data of the ventricle based on other suitable methods.
Alternatively, the volumetric curve is displayed in a predetermined area on the ultrasound image displayed by the display interface, which may be any suitable area on the ultrasound image, such as on the lower, upper, left or right side of the ultrasound image, etc.
The standard degree judgment and ventricular identification of the section in the ultrasonic image can be realized through a multi-task parallel trained deep learning network (wherein the standard degree judgment task is a classification task, the left ventricular endocardiography task is a segmentation task of the left ventricle), and the training process of the deep learning network is to train the two tasks. The main network model of the deep learning network can be implemented by UNet and the like.
As shown in fig. 5, the ventricular volume may be calculated in real time based on the Simpson monoplane method and the volume curve 330 may be updated in real time, and as the volume curve is refreshed, the ventricular end diastole and the ventricular end systole of each cardiac cycle are identified based on the volume data, for example, the maximum volume and the minimum volume in each cardiac cycle in the volume curve are identified, where the maximum volume corresponds to the ventricular end diastole, the minimum volume corresponds to the ventricular end systole, that is, the volume at the end diastole is the maximum value in one cardiac cycle, the volume at the end systole is the minimum value in one cardiac cycle, and in the process of real-time identification, the algorithm for identifying the end diastole and the end systole needs to be activated after exceeding one cardiac cycle, and the ED/ES pair is determined by calculating in real time the maximum value in the first preset curve segment and the minimum value in the second preset curve segment after the first preset curve segment, where the frame number represented by the "first preset curve segment and the second preset curve segment" is proportional to the frame frequency and the maximum value and the minimum value may not be the first preset curve segment and the right and the first preset curve segment and the right side maximum value. The first preset curve segment may be a curve segment corresponding to a preset number of frames, and the second preset curve segment may be a curve segment corresponding to a preset number of frames. By note, the maximum and minimum intervals cannot exceed one cardiac cycle.
The above-mentioned identification of the ventricular end diastole and the ventricular end systole of each cardiac cycle may be performed based on the volume data refreshed in real time, that is, each of the ventricular end diastole and the ventricular end systole of a predetermined number of cardiac cycles is identified, and then the first ventricular volume of the ventricular end diastole and the second ventricular volume of the ventricular end systole of each cardiac cycle are determined based on the ultrasound image corresponding to the ventricular end diastole and the ultrasound image corresponding to the ventricular end systole of each cardiac cycle, so as to perform the calculation of the ejection fraction, where the predetermined number may be reasonably set according to the actual needs, for example, may be 1, 2, or more.
Wherein automatically determining a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricles in each cardiac cycle based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole of the ventricles in each cardiac cycle comprises: identifying a section type of the scanning section at the end diastole of the ventricle in each cardiac cycle based on the ultrasonic image corresponding to the end diastole of the ventricle in each cardiac cycle, and identifying a section type of the scanning section at the end diastole of the ventricle in each cardiac cycle based on the ultrasonic image corresponding to the end systole of the ventricle; the process of identifying the section type can be identified in the previous section type standard degree judgment, the step can directly obtain the identification result, or the identification can be carried out on the ultrasonic images of the end diastole and the end systole again; automatically determining a calculation method for calculating the first chamber volume based on the section type of the scanning section at the end diastole of the ventricle and automatically determining a calculation method for calculating the second chamber volume based on the section type of the scanning section at the end systole of the ventricle, wherein the calculation method comprises a first calculation method and/or a second calculation method, wherein the first calculation method is used for calculating the chamber volume based on the ultrasonic images of the scanning section of the same section type, and the second calculation method is used for calculating the chamber volume based on the ultrasonic images of the scanning section of two different types; based on the determined calculation method, a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricles in each cardiac cycle are automatically calculated. The calculation method of the applicable ventricular volume is automatically determined through the tangent plane type, so that the accuracy of ventricular volume calculation is improved.
For example, when the slice type is the first type of slice or the corresponding slice is the second type of slice, the first calculation method is selected for calculating the first ventricular volume, for example, when the slice type of the scan slice (i.e., the slice presented in the ultrasound image) at the end diastole of the ventricle is the first type of slice; when the slice type of the scanned slice (i.e. the slice presented in the ultrasound image) at the end systole corresponds to a first type of slice or to a second type of slice, the calculation method for calculating the second ventricular volume is automatically determined to be the first calculation method. It should be noted that if the first ventricular volume and the second ventricular volume have been obtained by the calculation of the first calculation method when the volume data is obtained in real time in the foregoing, the calculation of the ejection fraction of the corresponding cardiac cycle may be directly obtained.
For another example, when the slice type is the following, a second calculation method is selected for calculation, for example, when the slice type of the scan slice at the end diastole includes a first type slice and a second type slice, the calculation method for calculating the first ventricular volume is automatically determined to be the second calculation method; when the section type of the scanning section at the end-systole of the ventricle comprises a first type section and a second type section, automatically determining a calculating method for calculating the volume of the second ventricle as a second calculating method; wherein the first type of tangential plane and the second type of tangential plane are perpendicular to each other.
Optionally, in the present application, the first section type is a cardiac apex two-cavity section, the second section type is a cardiac apex four-cavity section, or the first section type is a cardiac apex four-cavity section, the second section type is a cardiac apex two-cavity section, the above-listed section types are only examples, and other section types that can be applied to ejection fraction calculation may also be applied to the present application.
It should be noted that, when the type of the section of the ultrasound image corresponding to the end diastole is the same section type, for example, A2C or A4C, the first calculation method is selected to calculate the first chamber volume, that is, a single plane method, and when the type of the section of the ultrasound image corresponding to the end diastole is different section types, and the type of the section of the ultrasound image corresponding to the at least one frame is A2C, the type of the section of the ultrasound image corresponding to the at least one frame is A4C, the second calculation method is selected to calculate the first chamber volume, that is, a double plane method is selected to calculate the section of the ultrasound image corresponding to the end diastole, and likewise, when the type of the section of the ultrasound image corresponding to the end systole is the same section type, for example, A2C or A4C, the first calculation method is selected to calculate the second chamber volume, and when the type of the section of the ultrasound image corresponding to the end diastole is different section type, that is A2C, that is at least one frame of the ultrasound image corresponding to the end systole is different section type, and at least one frame of the ultrasound image corresponding to the end systole is A4C. For another example, when the second calculation method is selected for calculation, the first calculation method may also be selected for calculation at the same time, for example, an ultrasonic image having A2C and A4C in ultrasonic images corresponding to end diastole and end systole of the ventricle respectively, then the first chamber volume and the second chamber volume are obtained by calculation using the second calculation method, and then the ejection fraction is subsequently calculated, and the first chamber volume and the second chamber volume are obtained by calculation using the first calculation method, and then the ejection fraction is calculated based on an ultrasonic image having A2C in ultrasonic images corresponding to end diastole and end systole of the ventricle respectively, and the first chamber volume and the second chamber volume are obtained by calculation using the first calculation method, and then the ejection fraction is calculated.
Wherein the ultrasound images for different slice types can be obtained by the physician adjusting the probe according to prior experience during scanning, for example, the physician can adjust the scanning slice of the probe at estimated end diastole and end systole of the ventricle according to the contraction state of the ventricle in the ultrasound images displayed in real time, for example, the scanning of the probe A2C or A4C. Alternatively, it is also possible to randomly switch between A2C or A4C slices.
When the computing method is determined to be the first computing method, computing a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricle using the first computing method may include the steps of: identifying a first endocardial contour in an ultrasound image of the same tangent plane type at end diastole and identifying a second endocardial contour in an ultrasound image of the same tangent plane type at end systole; measuring a first long diameter of a ventricle in the first endocardial contour and a second long diameter of the ventricle in the second endocardial contour; dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the first long diameter and dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the second long diameter, and setting the cross section of the disk-shaped blocks to be circular; the first chamber volume is calculated based on a plurality of disk-shaped blocks divided along a direction perpendicular to the first major axis, for example, the volumes of the respective disk-shaped blocks are calculated, the first chamber volume is obtained by summing the volumes of the plurality of disk-shaped blocks, and the second chamber volume is calculated based on a plurality of disk-shaped blocks along a direction perpendicular to the second major axis, for example, the volumes of the respective disk-shaped blocks are calculated, and the second chamber volume is obtained by summing the volumes of the plurality of disk-shaped blocks. Optionally, the plurality of disk-shaped blocks have the same height. Alternatively, the number of the plurality of disc-shaped blocks divided along the first length diameter may be set reasonably according to actual needs, for example, may be 20 disc-shaped blocks with equal height, or 30 disc-shaped blocks with equal height. Optionally, the plurality of disk-shaped blocks have the same height. It should be noted that the first calculation method of the present application may correspond to a Simpson monoplane method, and specifically, the calculation method of the Simpson monoplane method is well known to those skilled in the art, and will not be described in detail herein.
Further, when the computing method is determined to be the second computing method, the second computing method is used to compute the first ventricular volume at end diastole and the second ventricular volume at end systole, where the second computing method may be a Simpson biplane method, or other method capable of computing the first ventricular volume at end diastole and the second ventricular volume at end systole based on two ultrasound images of different slice types, and further computing the ejection fraction, and computing the first ventricular volume at end diastole in each cardiac cycle based on the second computing method may include: acquiring a third endocardial contour in an ultrasonic image with a first surface type at the end diastole of the heart, and acquiring a fourth endocardial contour in an ultrasonic image with a second surface type at the end diastole of the heart; measuring a third long diameter of the ventricle in the third endocardial contour and a fourth long diameter of the ventricle in the fourth endocardial contour; dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the third long diameter and dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the fourth long diameter; setting cross-sections of the plurality of disk-shaped blocks to be elliptical, wherein a size of the elliptical is determined based on the fourth major axis; the first ventricular volume is computationally acquired based on the divided plurality of disk-shaped blocks. Optionally, the plurality of disk-shaped blocks have the same height.
When the computing method is determined to be the second computing method, the second computing method of the present application may be a Simpson biplane method, and calculating a second ventricular volume at an end systole of the ventricle in each cardiac cycle based on the second computing method includes: acquiring a third endocardial contour in an ultrasonic image with a section type of a first section type at the end of ventricular systole, and acquiring a fourth endocardial contour in an ultrasonic image with a section type of a second section type at the end of ventricular systole; measuring a third long diameter of the ventricle in a third endocardial contour and a fourth long diameter of the ventricle in a fourth endocardial contour; dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the third long diameter and dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the fourth long diameter, optionally the plurality of disk-shaped blocks having the same height; setting cross-sections of the plurality of disk-shaped blocks to be elliptical, wherein a size of the elliptical is determined based on the fourth major axis; the second ventricular volume is computationally acquired based on the divided plurality of disk-shaped blocks.
It is noted that in the present application, the first, second, third and fourth long diameters may be lengths from the mitral valve annulus plane to the apex of the heart. Alternatively, the number of the plurality of disk-shaped blocks divided along the third long diameter and the number of the plurality of disk-shaped blocks divided along the fourth long diameter may be reasonably set according to actual needs, and may be, for example, 20 disk-shaped blocks of equal height, or 30 disk-shaped blocks of equal height. For example, as shown in fig. 6, for an A4C section, it is divided into 20 disk-shaped blocks ai of equal height along its long diameter LVL4, the height h=lvl4/20 of each disk-shaped block, and for an A2C section, it is divided into 20 disk-shaped blocks ni of equal height along its long diameter LVL2, the height h=lvl2/20 of each disk-shaped block.
It should be noted that the second calculation method of the present application may be a Simpson biplane method, and specifically, the calculation method of the Simpson biplane method is well known to those skilled in the art, and will not be described in detail herein.
Whether the Simpson monoplane method or the Simpson biplane method is used to calculate EDV and ESV in the cardiac cycle is automatically determined by the above method, and thus the ejection fraction, e.g., left ventricular ejection fraction, is calculated.
Further, in step S230, based on the first ventricular volume and the second ventricular volume of each cardiac cycle, the cardiac ejection fraction, such as the left ventricular ejection fraction, of each cardiac cycle is automatically obtained by real-time analysis, for example, the first ventricular volume (e.g., ventricular end-diastole volume EDV) and the second ventricular volume (i.e., ventricular end-systole volume ESV) of each cardiac cycle may be obtained by each calculation.
Specifically, the Ejection Fraction (EF) can be calculated by the following formula:
because of instability in imaging by doctors, the imaging quality and type of the ultrasonic images in one cardiac cycle may have great difference, and poor imaging quality may affect the tracing of the endocardium of the left ventricle, especially on ED/ES section, and may directly affect the credibility of the final ejection fraction. In addition, the type of frame slice near ED/ES is not A2C/A4C, but also affects ejection fraction. Thus, after the ejection fraction is calculated, the method of the present application further comprises: the ejection fraction confidence coefficient of the ejection fraction corresponding to each cardiac cycle is automatically obtained, and the ejection fraction confidence coefficient is used for representing the accuracy of the ejection fraction, namely, the ejection fraction confidence coefficient of the cardiac cycle is evaluated and replied, for example, after the ejection fraction of one cardiac cycle is calculated, the ejection fraction confidence coefficient of the ejection fraction corresponding to the cardiac cycle is obtained. An evaluation score is made for the confidence in the ejection fraction of the cardiac cycle.
In one example, the automatically obtaining the ejection fraction confidence of the ejection fraction corresponding to each cardiac cycle includes: automatically acquiring a first confidence Qed of a plurality of frames of ultrasound images adjacent to an image frame corresponding to the end diastole of the ventricle and a second confidence Qes of a plurality of frames of ultrasound images adjacent to an image frame corresponding to the end systole of the ventricle in each cardiac cycle; based on the first confidence Qed and the second confidence Qes, an ejection fraction confidence Qef for the ejection fraction corresponding to each cardiac cycle is automatically calculated.
It should be noted that, the image frame corresponding to the end diastole may refer to an ultrasound image frame for calculating the ejection fraction, and the multi-frame ultrasound image adjacent to the image frame corresponding to the end diastole may refer to an ultrasound image of a first preset frame number before the image frame corresponding to the end diastole, or refer to an ultrasound image of a second preset frame number after the image frame corresponding to the end diastole, or refer to an ultrasound image of a first preset frame number before the image frame corresponding to the end diastole and an ultrasound image of a second preset frame number after the image frame corresponding to the end diastole. The image frame corresponding to the end systole may be an ultrasonic image frame for calculating the ejection fraction, and the multi-frame ultrasonic image adjacent to the image frame corresponding to the end systole may be an ultrasonic image of a first preset frame number before the image frame corresponding to the end systole, or an ultrasonic image of a second preset frame number after the image frame corresponding to the end systole, or an ultrasonic image of a first preset frame number before the image frame corresponding to the end systole and an ultrasonic image of a second preset frame number after the image frame corresponding to the end systole, where the first preset frame number and the second preset frame number may be any frame number reasonably set according to actual needs, but it is worth mentioning that the preset frame number may be an image frame in the same cardiac cycle.
For example, the ejection fraction confidence Qef for the ejection fraction of each cardiac cycle may be calculated by the following formula:
the first confidence Qed may be calculated based on any suitable method, for example, the first confidence Qed may be calculated by: automatically acquiring confidence coefficient of each frame of ultrasonic image in multi-frame ultrasonic images adjacent to the image frame corresponding to the end diastole of each heart chamber; the confidence level is used for representing the quality of the ultrasonic images, and the confidence level of each ultrasonic image can be obtained through any suitable intelligent analysis method, and is not particularly limited herein; and then, respectively assigning a corresponding weight value to the confidence level of each frame of ultrasonic image adjacent to the end diastole of the ventricle, wherein the weight value is determined by the distance between each frame of ultrasonic image and the image frame corresponding to the end diastole of the ventricle, and the weight value is smaller when the distance is farther, wherein the distance can be the number of frames or the time interval, for example, the first weight corresponds to the ultrasonic image with the first frame number of frames separated from the image frame corresponding to the end diastole of the ventricle, the second weight corresponds to the ultrasonic image with the second frame number of frames separated from the image frame corresponding to the end diastole of the ventricle, and the first frame number is smaller than the second frame number, and then the first weight is larger than the second weight. Finally, the confidence coefficient of each frame of ultrasonic image is multiplied by the weight value corresponding to each frame of ultrasonic image respectively and then added to obtain a first sum; the first sum is averaged to obtain the first confidence level.
Similarly, a second confidence level of a plurality of frames of ultrasound images adjacent to an image frame corresponding to end systole of the heart chamber in each cardiac cycle may be automatically obtained based on a method substantially similar to the first confidence level, including: automatically acquiring confidence coefficient of each frame of ultrasonic image in a plurality of frames of ultrasonic images adjacent to the image frame corresponding to the end systole of each heart chamber; the confidence level of each frame of ultrasonic image in the multi-frame ultrasonic images adjacent to the image frame corresponding to the ventricular end systole is respectively endowed with a corresponding weight value, wherein the weight value is determined by the distance between each frame of ultrasonic image and the image frame corresponding to the ventricular end systole, and the weight value is smaller when the distance is farther; multiplying the confidence coefficient of each frame of ultrasonic image by the weight value corresponding to each frame of ultrasonic image respectively, and adding to obtain a second confidence coefficient sum; and averaging the second confidence sum to obtain the second confidence.
Specifically, the first and second confidence levels Qed and Qes may be calculated by the following formula:
wherein score i Representing confidence level of ultrasonic image of frame near ED/ES, MAXSCORE is 1, weights i And the weight value of the ultrasonic image of the frame near the ED/ES is represented.
In one example, the method of the present application further comprises displaying a hint of the ejection fraction confidence of at least one cardiac cycle. The confidence in the ejection fraction is displayed to reflect the confidence in the calculated ejection fraction to the doctor, so as to prompt the doctor whether the EF value is available. For example, as shown in FIG. 7, the current EF confidence is prompted.
The prompt of the ejection fraction of one cardiac cycle and the ejection fraction confidence corresponding to the ejection fraction obtained by each calculation can be displayed in real time, or the prompt of the ejection fraction of one cardiac cycle and the ejection fraction confidence corresponding to the ejection fraction calculated by the latest calculation can be displayed, or the prompt of the ejection fraction of all cardiac cycles and the ejection fraction confidence corresponding to the ejection fraction calculated by the calculation can be displayed, or the prompt of the ejection fraction of the cardiac cycle with the highest current ejection fraction confidence and the ejection fraction confidence corresponding to the ejection fraction in real time can be displayed.
The cues of ejection fraction confidence may be characterized in any suitable way, e.g. comprise text and/or values and/or graphics describing ejection fraction confidence of the at least one cardiac cycle, or be implemented by distinguishing between curve segments of the volume curve corresponding to the at least one cardiac cycle, wherein the distinguishing comprises at least one of the following ways of displaying: in differentiated colors, in differentiated line segment shapes. Alternatively, the at least one cardiac cycle may also be a cardiac cycle for which the ejection fraction confidence meets a preset condition, which may be a preset threshold or the like, e.g. for which the ejection fraction confidence is greater than the preset threshold, the confidence that the ejection fraction meets the requirement may provide a relatively accurate ejection fraction for the doctor to refer to. With the real-time monitoring, the multiple ejection scores may have been calculated and obtained before the current time, and then the ejection score with the highest ejection score confidence in the multiple ejection scores may be displayed in real time, and meanwhile, the line segments of the volumetric curve corresponding to the ejection score with the highest ejection score confidence may be displayed in a distinguishing manner, for example, as shown in fig. 8, the line segments of the volumetric curve corresponding to the ejection score with the highest ejection score confidence may be displayed in a green color.
It should be noted that the ejection fraction with the highest ejection fraction confidence may be one or a plurality, and when the ejection fraction is a plurality, any one of them may be selected for display, or the ejection fraction indicated by the selection instruction may be displayed in response to the selection instruction.
In one example, the method of the present application further comprises: marking information of end diastole and end systole of the ventricle in at least one cardiac cycle on the volume curve; the volume curve and the marking information are displayed, which may be any suitable marking, such as a graphic or text, for example, as shown in fig. 7, the volume curve is marked ED/ES, for example, in a cross. The EDV/ESV for each cardiac cycle can be identified, then the corresponding location of the volume curve is marked.
In one example, the method of the present application further comprises: displaying in real time a first ultrasound image at end diastole and a second ultrasound image at end systole of a heart cycle, which may be the heart cycle corresponding to the ejection fraction with the highest confidence in the current ejection fraction, the first ultrasound image and the second ultrasound image being displayed on top of a third ultrasound image displayed in real time at the current moment, wherein the first ultrasound image and the second ultrasound image are smaller in size than the third ultrasound image, e.g. the first ultrasound image and the second ultrasound image are displayed in a separate display window. The display positions of the first ultrasound image and the second ultrasound image may be any region that is placed on the third ultrasound image without obscuring key image information of the third ultrasound image, such as a lower right corner, an upper left corner, and the like. Alternatively, for example
Optionally, the first ultrasound image includes a first slice type ultrasound image and/or a second slice type ultrasound image, and the second ultrasound image includes a first slice type ultrasound image and/or a second slice type ultrasound image, where the first ultrasound image and the second ultrasound image may be ultrasound images used to calculate a ejection fraction of the cardiac cycle, for example, as shown in fig. 7, a window displays an ED/ES view and an EF value in the cardiac cycle with a highest confidence in the ejection fraction, and with a refresh of the confidence, the EF value and the displayed ED/ES view may also be refreshed, and when the ejection fraction of the cardiac cycle is calculated based on the ultrasound image of A2C or A4C, the ultrasound image of A2C or A4C at the end of the corresponding ventricular systole and the ultrasound image of A2C or A4C at the end of the ventricular diastole are displayed; when the ejection fraction of the cardiac cycle is obtained based on the ultrasound images of A2C and A4C, the ultrasound images of A2C and A4C at the end systole of the corresponding ventricle and the ultrasound images of A2C and A4C at the end diastole of the ventricle are displayed, and as shown in fig. 8, the cardiac cycle may be the cardiac cycle with the highest confidence in the current ejection fraction, and with the refreshing of the confidence, the EF value and the displayed ED/ES view may also be refreshed.
In one example, the method of the present application further comprises: the analysis of the ejection fraction corresponding to at least one cardiac cycle (e.g., the at least one cardiac cycle may be the cardiac cycle corresponding to the ejection fraction with the highest confidence in the current ejection fraction) is displayed in real time, wherein the ejection fraction comprises a first ejection fraction obtained based on a first calculation method and/or a second ejection fraction obtained based on a second calculation method, e.g., as shown in fig. 8, a first ejection fraction EF-A2C obtained by the first calculation method based on an ultrasound image of an A2C section, e.g., EF-A2C is 60%, and a first ejection fraction EF-A4C obtained by the first calculation method based on an ultrasound image of an A4C section, e.g., EF-A2C is 52%, and a second ejection fraction EF-impson obtained by the second calculation method based on an ultrasound image of an A2C section and an ultrasound image of an A4C section, e.g., EF-BPSimpson is 57%.
In one example, the method of the present application further comprises: an analysis report of the analysis results of the ejection fraction of at least one cardiac cycle (for example) is output, either after the whole ejection fraction analysis is completed or during the analysis. An analysis report of the analysis result of the blood fraction is automatically output, for example, in response to a freeze instruction of the ultrasound image, and may be as shown in fig. 9. By outputting the report, the doctor is assisted to judge the heart function of the tested patient according to the report.
The analysis including output may be stored in memory or may be output directly through an output device such as a printer.
In one example, the analysis report of the analysis results includes at least one of the following information: a first ejection fraction obtained based on the first calculation method, a second ejection fraction obtained based on the second calculation method. Optionally, the analysis report of the analysis result further includes at least one of the following information: the first chamber volume obtained based on a first calculation method, the second chamber volume obtained based on a first calculation method, the first chamber volume obtained based on a second calculation method, the second chamber volume obtained based on a second calculation method, and the end systole of the ventricle. Optionally, the analysis report may also output ultrasound images used to calculate the ejection fraction, for example, when the ejection fraction of the cardiac cycle is calculated based on the ultrasound images of A2C and A4C, then the corresponding ultrasound images of A2C and A4C at end systole and the ultrasound images of A2C and A4C at end diastole are displayed.
An exemplary description of the analysis of left ventricular ejection fraction is described below with reference to fig. 3: firstly inputting an ultrasonic image in real time, then identifying the type of the section of the image in real time, judging whether the identified section type is A2C or A4C, if not, performing no processing, if not, dividing the heart chamber of the heart tissue in the ultrasonic image in real time, calculating the single plane volume (namely the ventricular volume) and the Left Ventricle Length (LVL), herein the length is also called as the long diameter, outputting a volume curve in real time, then automatically identifying the cardiac cycle, scoring the cycle quality score (namely the confidence degree), outputting the single plane method A2C-EF/A4C-EF in real time, then automatically screening the A2C/A4C (such as screening the optimal A2C/A4C) in the cardiac cycle, outputting the biplane method EF in real time, freezing after obtaining the result, outputting an EF analysis report, and if not, performing analysis calculation in real time.
In summary, the method of the present application can automatically analyze and acquire the cardiac ejection fraction corresponding to each cardiac cycle in real time, which is favorable for real-time monitoring of the cardiac function of the patient, and compared with the traditional single-sided method and double-sided method, the method is more convenient and rapid, and the accuracy of the ejection fraction is higher, thereby improving the efficiency of clinical diagnosis of the cardiac function of the patient by doctors.
Yet another embodiment of the present application further provides a method for analyzing cardiac ejection fraction, as shown in fig. 10, the method 1000 includes steps S1010 to S1030: in step S1010, ejection fraction corresponding to a plurality of cardiac cycles of cardiac tissue of a target object and ejection fraction confidence corresponding to each ejection fraction are acquired; in step S1020, based on the ejection fraction confidence, determining ejection fraction of at least one cardiac cycle of the plurality of cardiac cycles as an analysis result, for example, the confidence meets a preset condition, or alternatively, the at least one cardiac cycle is a cardiac cycle corresponding to the highest ejection fraction confidence; in step S1030, the analysis result is output.
Some details of the individual steps in this embodiment may be specifically referred to the relevant description hereinbefore and will not be repeated here.
Based on the method of the embodiment of the application, the confidence level of the ejection fraction is obtained, so that the reliability of the ejection fraction is evaluated, a doctor can determine whether the ejection fraction is available according to the confidence level, the analysis result of the ejection fraction is more reliable and accurate, and the doctor can judge the heart function of a patient reasonably and accurately according to the analysis result of the ejection fraction.
Embodiments of the present invention also provide an ultrasound imaging system for implementing the above-described method 200 of analyzing cardiac ejection fraction or method 1000 of analyzing cardiac ejection fraction. The ultrasound imaging system includes an ultrasound probe, a transmit circuit, a receive circuit, a processor, and a display. Referring back to fig. 1, the ultrasound imaging system may be implemented as the ultrasound imaging system 100 shown in fig. 1, the ultrasound imaging system 100 may include an ultrasound probe 110, a transmitting circuit 112, a receiving circuit 114, a processor 116, and a display 118, and optionally, the ultrasound imaging system 100 may further include a transmit/receive selection switch 120 and a beam forming module 122, where the transmitting circuit 112 and the receiving circuit 114 may be connected to the ultrasound probe 110 through the transmit/receive selection switch 120, and the related descriptions of the respective components may be referred to the related descriptions above and are not repeated herein.
Wherein the transmitting circuit 112 is configured to control the ultrasound probe 110 to transmit ultrasound waves to a target area including a heart valve; the receiving circuit 114 is used for controlling the ultrasonic probe 110 to receive the echo of the ultrasonic wave returned by the target area so as to obtain an ultrasonic echo signal; the processor 116 is configured to perform ultrasound imaging based on the ultrasound echo signals; the processor 116 is also configured to perform the method 200 of analyzing cardiac ejection fraction or the method 1000 of analyzing cardiac ejection fraction described above; when the processor 116 performs the method 200 of analyzing cardiac ejection fraction or the method 1000 of analyzing cardiac ejection fraction, the display 118 is used to display any visual information, such as at least the ejection fraction, but also the ultrasound image of the current frame, etc.
Only the main functions of the components of the ultrasound imaging system are described above, and for more details, reference is made to the description of the method 200 of analyzing cardiac ejection fraction or the method 1000 of analyzing cardiac ejection fraction.
The ultrasonic imaging system provided by the embodiment of the invention can automatically analyze and acquire the heart ejection fraction corresponding to each cardiac cycle in real time, is favorable for monitoring the heart function of a patient in real time, is more convenient and quicker compared with the traditional single-sided method and double-sided method, has higher accuracy of the ejection fraction, and further improves the efficiency of clinical diagnosis of the heart function of the patient by doctors.
The present application also provides a system for analyzing cardiac ejection fraction, as shown in fig. 11, the system 1100 comprising: memory 1101, processor 1102, and display 1103, as well as communication interfaces, etc. These components are interconnected by a bus system and/or other forms of connection mechanisms (not shown). It should be noted that the components and structures of the system 1100 for analyzing cardiac ejection fraction shown in fig. 11 are exemplary only and not limiting, as the system 1100 for analyzing cardiac ejection fraction may have other components and structures as desired.
The memory 1101 is used to store various data and executable programs generated during the relevant analysis of cardiac ejection fraction, such as system programs for the system 1100 for analyzing cardiac ejection fraction, various application programs, or algorithms implementing various specific functions. May include one or more computer program products that may include various forms of computer-readable storage media, such as volatile memory and/or non-volatile memory.
The processor 1102 may be a Central Processing Unit (CPU), an image processing unit (GPU), an Application Specific Integrated Circuit (ASIC), a Field Programmable Gate Array (FPGA), or other form of processing unit with data processing capabilities and/or instruction execution capabilities, and may control other components in the system 1100 for analyzing cardiac ejection fraction to perform desired functions.
In one example, the system 1100 for analyzing cardiac ejection fraction further includes a communication interface (not shown) for communication between various components of the system 1100 for analyzing cardiac ejection fraction and between various components of the quality control management system 100 and other devices outside of the system (e.g., an ultrasound imaging system, etc.). For example, the ultrasonic image output by the ultrasonic imaging system is acquired through a communication interface, and the ultrasonic image can be output in real time or off-line.
The display 1103 is used for displaying and visualizing, and the display 1103 can be a touch display screen, a liquid crystal display screen, or the like, or can be an independent display such as a liquid crystal display, a television, or the like, which is independent of a system, or can be a display screen on an electronic device such as a mobile phone, a tablet computer, or the like. The display 1103 may be used to display information entered by or provided to a user as well as various graphical user interfaces of the system, which may be composed of graphics, text, icons, video, and any combination thereof.
Further, the processor 1102 is configured to execute the program instructions stored in the memory 1101, so that the processor 1102 executes the foregoing method for analyzing cardiac ejection fraction, specifically, only the main functions of the components of the system for analyzing cardiac ejection fraction are described above, and for more details, reference is made to the related description of the method 200 for analyzing cardiac ejection fraction or the method 1000 for analyzing cardiac ejection fraction, which are not described herein.
The ultrasonic imaging system provided by the embodiment of the invention can automatically analyze and acquire the heart ejection fraction corresponding to each cardiac cycle in real time, is favorable for monitoring the heart function of a patient in real time, is more convenient and quicker compared with the traditional single-sided method and double-sided method, has higher accuracy of the ejection fraction, and further improves the efficiency of clinical diagnosis of the heart function of the patient by doctors.
Although the illustrative embodiments have been described herein with reference to the accompanying drawings, it is to be understood that the above illustrative embodiments are merely illustrative 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 invention. All such changes and modifications are intended to be included within the scope of the present invention as set forth in the appended claims.
Those of ordinary skill in the art will appreciate that the various illustrative elements and algorithm steps described in connection with the embodiments disclosed herein may be implemented as electronic hardware, or combinations of computer software and electronic hardware. Whether such functionality is implemented as hardware or software depends upon the particular application and design constraints imposed on the solution. Skilled artisans may implement the described functionality in varying ways for each particular application, but such implementation decisions should not be interpreted as causing a departure from the scope of the present invention.
In the several embodiments provided by the present invention, it should be understood that the disclosed apparatus and method may be implemented in other ways. For example, the above-described device embodiments are merely illustrative, e.g., the division of the elements is merely a logical functional division, and there may be additional divisions when actually implemented, e.g., multiple elements or components may be combined or integrated into another device, or some features may be omitted or not performed.
In the description provided herein, numerous specific details are set forth. However, it is understood that embodiments of the invention may be practiced without these specific details. In some instances, well-known methods, structures and techniques have not been shown in detail in order not to obscure an understanding of this description.
Similarly, it should be appreciated that in order to streamline the invention and aid in understanding one or more of the various inventive aspects, various features of the invention are sometimes grouped together in a single embodiment, figure, or description thereof in the description of exemplary embodiments of the invention. However, the method of the present invention should not be construed as reflecting the following intent: i.e., the claimed invention requires more features than are expressly recited in each claim. Rather, as the following claims reflect, inventive aspects lie in less than all features of a single disclosed embodiment. Thus, the claims following the detailed description are hereby expressly incorporated into this detailed description, with each claim standing on its own as a separate embodiment of this invention.
It will be understood by those skilled in the art that all of the features disclosed in this specification (including any accompanying claims, abstract and drawings), and all of the processes or units of any method or apparatus so disclosed, may be combined in any combination, except combinations where the features are mutually exclusive. Each feature disclosed in this specification (including any accompanying claims, abstract and drawings), may be replaced by alternative features serving the same, equivalent or similar purpose, unless expressly stated otherwise.
Furthermore, those skilled in the art will appreciate that while some embodiments described herein include some features but not others included in other embodiments, combinations of features of different embodiments are meant to be within the scope of the invention and form different embodiments. For example, in the claims, any of the claimed embodiments may be used in any combination.
Various component embodiments of the invention may be implemented in hardware, or in software modules running on one or more processors, or in a combination thereof. Those skilled in the art will appreciate that some or all of the functions of some of the modules according to embodiments of the present invention may be implemented in practice using a microprocessor or Digital Signal Processor (DSP). The present invention can also be implemented as an apparatus program (e.g., a computer program and a computer program product) for performing a portion or all of the methods described herein. Such a program embodying the present invention may be stored on a computer readable medium, or may have the form of one or more signals. Such signals may be downloaded from an internet website, provided on a carrier signal, or provided in any other form.
It should be noted that the above-mentioned embodiments illustrate rather than limit the invention, and that those skilled in the art will be able to design alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses shall not be construed as limiting the claim. The invention may be implemented by means of hardware comprising several distinct elements, and by means of a suitably programmed computer. In the unit claims enumerating several means, several of these means may be embodied by one and the same item of hardware. The use of the words first, second, third, etc. do not denote any order. These words may be interpreted as names.
The foregoing description is merely illustrative of specific embodiments of the present invention and the scope of the present invention is not limited thereto, and any person skilled in the art can easily think about variations or substitutions within the scope of the present invention. The protection scope of the invention is subject to the protection scope of the claims.
Claims (35)
1. A method of analyzing cardiac ejection fraction, the method comprising:
Acquiring an ultrasonic image corresponding to the end diastole of a ventricle and an ultrasonic image corresponding to the end systole of the ventricle in each cardiac cycle based on the ultrasonic image of at least one scanning section of the heart part of the target object acquired in real time;
automatically determining a first ventricular volume at end diastole and a second ventricular volume at end systole of each cardiac cycle based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole of each cardiac cycle;
and automatically analyzing and acquiring the heart ejection fraction corresponding to each cardiac cycle in real time based on the first chamber volume and the second chamber volume of each cardiac cycle.
2. The method of claim 1, wherein the acquiring an ultrasound image corresponding to end diastole and an ultrasound image corresponding to end systole of the ventricle in each cardiac cycle comprises:
automatically identifying a ventricle in the ultrasound image of the at least one scan slice in real time, and automatically acquiring volume data of the identified ventricle in real time;
automatically identifying end diastole and end systole of the ventricles of each cardiac cycle based on the volume data;
An ultrasound image corresponding to the identified end diastole of the ventricle and an ultrasound image corresponding to the identified end systole of the ventricle are acquired.
3. The method of claim 2, wherein automatically identifying a ventricle in the ultrasound image of the at least one scan slice in real time and automatically acquiring volume data of the identified ventricle in real time, further comprises:
automatically identifying in real time the standard degree of the ultrasound image of the at least one scan section;
and when the standard degree is within a preset range, automatically identifying the ventricles in the ultrasonic image of the scanning section of which the standard degree is within the preset range in real time, and acquiring the volume data of the identified ventricles in real time.
4. A method as claimed in claim 3, wherein the standard level comprises a plurality of levels, wherein each level is used to characterize a different standard level of the ultrasound image of the scan plane.
5. The method of claim 4, wherein the plurality of levels includes a first level, a second level, a third level, and a fourth level, wherein the first level corresponds to a level of standardization of ultrasound images of the scan plane that is greater than the second level corresponds to a level of standardization of ultrasound images of the scan plane that is greater than the third level corresponds to a level of standardization of ultrasound images of the scan plane that is greater than the fourth level corresponds to a level of standardization of ultrasound images of the scan plane, the predetermined range being no less than the third level.
6. The method of claim 5, wherein automatically identifying in real time a standard level of the ultrasound image of the at least one scan slice comprises:
when the ultrasonic image of the at least one scanning section is identified to meet a first preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the first grade, wherein the first preset condition comprises the following conditions: the section type of the ultrasonic image is a heart apex two-cavity heart section or a heart apex four-cavity heart section, a cavity is shown in the ultrasonic image of the at least one scanning section, and the imaging of the side wall and the room interval of the cavity is clear;
when the ultrasonic image of the at least one scanning section is identified to meet a second preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the second grade, wherein the second preset condition comprises the following conditions: the section type of the ultrasonic image is a heart apex two-cavity heart section or a heart apex four-cavity heart section, and the at least one ultrasonic image of the scanning section presents a cavity, but the imaging of the outer side wall or the inter-chamber space of the ventricle is not clear or partially invisible;
when the ultrasonic image of the at least one scanning section is identified to meet a third preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the third grade, wherein the third preset condition comprises the following conditions: the section types of the ultrasonic image are a three-cavity heart section of the apex, a five-cavity heart section of the apex, a two-cavity heart section of the apex invisible in the atrium, a two-cavity heart section of the apex inclined in position, a four-cavity heart section of the apex invisible in the atrium or a four-cavity heart section of the apex inclined in position;
When the ultrasonic image of the at least one scanning section is identified to meet a fourth preset condition, determining the standard degree of the ultrasonic image of the at least one scanning section as the fourth grade, wherein the fourth preset condition comprises the following conditions: the outline of part of the ventricle is not presented or presented in the ultrasonic image of the at least one scanning section, and the section type of the ultrasonic image is the section type except for the two-chamber heart section of the apex, the three-chamber heart section of the apex, the four-chamber heart section of the apex and the five-chamber heart section of the apex.
7. A method as claimed in claim 3, wherein the method further comprises: and displaying prompt information corresponding to the standard degree of the ultrasonic image of the current scanning section in the display interface.
8. The method of claim 7, wherein the standard level comprises a plurality of levels, the displaying in the display interface a hint message corresponding to the standard level of the ultrasound image of the current scan plane, comprising:
displaying prompt information corresponding to at least part of the grades in a distinguishing display mode in a display interface, wherein the distinguishing display mode comprises at least one of the following modes: at least part of the prompt messages corresponding to the grades are displayed in different colors, at least part of the prompt messages corresponding to the grades are displayed in different graphs, at least part of the prompt messages corresponding to the grades are displayed in different shading, at least part of the prompt messages corresponding to the grades are flash-displayed and at least part of the prompt messages corresponding to the grades are highlighted.
9. The method of claim 7, wherein displaying in the display interface a hint message corresponding to a standard level of an ultrasound image of a current scan plane comprises:
displaying prompt information corresponding to the level exceeding the preset threshold range in a distinguishing display mode in a display interface so as to prompt and adjust the position of the ultrasonic probe.
10. The method of claim 2, wherein the volume data comprises a volume curve, the identifying end diastole and end systole of the ventricles of each cardiac cycle based on the volume data comprising:
a maximum volume and a minimum volume in each cardiac cycle in the volume curve are identified, wherein the maximum volume corresponds to the end diastole of the ventricle and the minimum volume corresponds to the end systole of the ventricle.
11. The method of claim 10, wherein the method further comprises:
marking information of end diastole and end systole of the ventricle in at least one cardiac cycle on the volume curve;
displaying the volume curve and the marking information.
12. The method of claim 1, wherein automatically determining a first ventricular volume at end diastole and a second ventricular volume at end systole for each cardiac cycle based on the ultrasound image corresponding to end diastole and the ultrasound image corresponding to end systole for each cardiac cycle comprises:
Identifying a section type of the scanning section at the end diastole of the ventricle in each cardiac cycle based on the ultrasonic image corresponding to the end diastole of the ventricle in each cardiac cycle, and identifying a section type of the scanning section at the end diastole of the ventricle in each cardiac cycle based on the ultrasonic image corresponding to the end systole of the ventricle;
automatically determining a calculation method for calculating the first chamber volume based on the section type of the scanning section at the end diastole of the ventricle and automatically determining a calculation method for calculating the second chamber volume based on the section type of the scanning section at the end systole of the ventricle, wherein the calculation method comprises a first calculation method and/or a second calculation method, wherein the first calculation method is used for calculating the chamber volume based on the ultrasonic images of the scanning section of the same section type, and the second calculation method is used for calculating the chamber volume based on the ultrasonic images of the scanning section of two different types;
based on the determined calculation method, a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricles in each cardiac cycle are automatically calculated.
13. The method of claim 12, wherein the automatically determining a calculation method for calculating the first ventricular volume based on the type of the surface of the end-diastole scan surface and the automatically determining a calculation method for calculating the second ventricular volume based on the type of the surface of the end-diastole scan surface comprises:
When the section type of the scanning section at the end diastole of the ventricle is a first type section or a second type section, automatically determining a calculation method for calculating the first ventricular volume as a first calculation method;
and when the section type of the scanning section at the end of ventricular systole is a first type section or a second type section, automatically determining a calculation method for calculating the volume of the second ventricle as a first calculation method.
14. The method of claim 12, wherein the automatically determining a calculation method for calculating the first ventricular volume based on the type of the surface of the end-diastole scan surface and the automatically determining a calculation method for calculating the second ventricular volume based on the type of the surface of the end-diastole scan surface comprises:
when the section type of the scanning section at the end diastole of the ventricle comprises a first type section and a second type section, automatically determining a calculating method for calculating the first ventricular volume as a second calculating method;
when the section type of the scanning section at the end of ventricular systole comprises a first type section and a second type section, automatically determining a calculation method for calculating the second ventricular volume as a second calculation method; wherein the first type of tangential plane and the second type of tangential plane are perpendicular to each other.
15. A method according to claim 12 or 13, wherein when the calculation method is determined to be the first calculation method, calculating a first ventricular volume at end diastole and a second ventricular volume at end systole of the ventricle in each cardiac cycle based on the determined calculation method, comprises:
identifying a first endocardial contour in an ultrasound image of the same tangent plane type at end diastole and identifying a second endocardial contour in an ultrasound image of the same tangent plane type at end systole;
measuring a first long diameter of a ventricle in the first endocardial contour and a second long diameter of the ventricle in the second endocardial contour;
dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the first long diameter and dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the second long diameter, and setting the cross section of the disk-shaped blocks to be circular;
the first ventricular volume is computationally acquired based on a plurality of disk-shaped blocks divided along a direction perpendicular to the first long diameter, and the second ventricular volume is computationally acquired based on a plurality of disk-shaped blocks along a direction perpendicular to the second long diameter.
16. The method of claim 14, wherein when the determined calculation method is the second calculation method, calculating the first ventricular volume at end diastole of the ventricle in each cardiac cycle based on the determined calculation method comprises:
acquiring a third endocardial contour in an ultrasonic image with a first surface type at the end diastole of the heart, and acquiring a fourth endocardial contour in an ultrasonic image with a second surface type at the end diastole of the heart;
measuring a third long diameter of the ventricle in the third endocardial contour and a fourth long diameter of the ventricle in the fourth endocardial contour;
dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the third long diameter and dividing the ventricle into a plurality of disk-shaped blocks along a direction perpendicular to the fourth long diameter;
setting cross-sections of the plurality of disk-shaped blocks to be elliptical, wherein a size of the elliptical is determined based on the fourth major axis;
the first ventricular volume is computationally acquired based on the divided plurality of disk-shaped blocks.
17. The method of claim 14, wherein the first facet type is a biapical cardiac facet, the second facet type is a biapical four-chamber cardiac facet, or the first facet type is a biapical four-chamber cardiac facet, and the second facet type is a biapical cardiac facet.
18. The method of claim 1, wherein the method further comprises: and automatically acquiring the ejection fraction confidence coefficient of the ejection fraction corresponding to each cardiac cycle, wherein the ejection fraction confidence coefficient is used for representing the accuracy of the ejection fraction.
19. The method of claim 18, wherein automatically obtaining a confidence in the ejection fraction of the ejection fraction for each cardiac cycle comprises:
automatically acquiring a first confidence coefficient of a plurality of frames of ultrasonic images adjacent to the image frames corresponding to the end diastole of the heart chamber and a second confidence coefficient of a plurality of frames of ultrasonic images adjacent to the image frames corresponding to the end systole of the heart chamber in each cardiac cycle;
based on the first confidence and the second confidence, an ejection fraction confidence for the ejection fraction corresponding to each cardiac cycle is automatically calculated.
20. The method of claim 19, wherein automatically acquiring a first confidence level for a plurality of frames of ultrasound images in each cardiac cycle adjacent to an image frame corresponding to end diastole of the ventricle comprises:
automatically acquiring confidence coefficient of each frame of ultrasonic image in a plurality of frames of ultrasonic images adjacent to the image frame corresponding to the end diastole of the ventricle in each cardiac cycle;
The confidence level of each frame of ultrasonic image in the multi-frame ultrasonic images adjacent to the image frame corresponding to the end diastole of the ventricle is respectively assigned with a corresponding weight value, the weight value is determined by the distance between each frame of ultrasonic image and the image frame corresponding to the end diastole of the ventricle, and the weight value is smaller when the distance is farther;
multiplying the confidence coefficient of each frame of ultrasonic image by the weight value corresponding to each frame of ultrasonic image respectively, and adding to obtain a first confidence coefficient sum;
and averaging the first confidence sum to obtain the first confidence.
21. The method of claim 19, wherein automatically acquiring a second confidence level for a plurality of frames of ultrasound images in each cardiac cycle adjacent to an image frame corresponding to end systole of the heart chamber comprises:
automatically acquiring confidence coefficient of each frame of ultrasonic image in a plurality of frames of ultrasonic images adjacent to the image frame corresponding to the end systole of each heart chamber;
respectively assigning corresponding weight values to the confidence degrees of the ultrasonic images of each frame in the multi-frame ultrasonic images adjacent to the image frame corresponding to the ventricular end systole, wherein the weight values are determined by the distance between the ultrasonic images of each frame and the image frame corresponding to the ventricular end systole, and the weight values are smaller when the distance is farther;
Multiplying the confidence coefficient of each frame of ultrasonic image by the weight value corresponding to each frame of ultrasonic image respectively, and adding to obtain a second confidence coefficient sum;
and averaging the second confidence sum to obtain the second confidence.
22. The method of claim 19, wherein the method further comprises:
a hint of the ejection fraction confidence of at least one cardiac cycle is displayed.
23. The method of claim 22, wherein the displaying a hint of the ejection fraction confidence of at least one cardiac cycle comprises:
the prompting is achieved by distinguishing a curve segment corresponding to the at least one cardiac cycle in the volume curve, wherein the distinguishing display comprises at least one of the following display modes: in differentiated colors, in differentiated line segment shapes.
24. The method of claim 22, wherein the cues comprise text and/or numerical values and/or graphics describing a confidence in the ejection fraction of the at least one cardiac cycle.
25. The method of claim 19, wherein the method further comprises:
The first ultrasound image at end diastole of the ventricle and the second ultrasound image at end systole of the ventricle in at least one cardiac cycle are displayed in real time.
26. The method of claim 25, wherein the first ultrasound image comprises a first cut-plane type ultrasound image and/or a second cut-plane type ultrasound image, the second ultrasound image comprising a first cut-plane type ultrasound image and/or a second cut-plane type ultrasound image.
27. The method of claim 1, wherein the method further comprises: displaying analysis results of ejection fraction corresponding to at least one cardiac cycle in real time, wherein the ejection fraction comprises a first ejection fraction obtained based on a first calculation method and/or a second ejection fraction obtained based on a second calculation method.
28. The method of claim 1, wherein the method further comprises: an analysis report of the analysis results of the ejection fraction of at least one cardiac cycle is output.
29. The method of claim 28, wherein the analysis report of the analysis results includes at least one of the following information: a first ejection fraction obtained based on the first calculation method, a second ejection fraction obtained based on the second calculation method.
30. The method of claim 29, wherein the analysis report of the analysis results further comprises at least one of the following information: the first chamber volume obtained based on a first calculation method, the second chamber volume obtained based on a first calculation method, the first chamber volume obtained based on a second calculation method, the second chamber volume obtained based on a second calculation method, and the end systole of the ventricle.
31. The method of any one of claims 22 to 30, wherein the at least one cardiac cycle is the cardiac cycle with the highest confidence in ejection fraction.
32. A method of analyzing cardiac ejection fraction, the method comprising:
acquiring ejection fraction corresponding to a plurality of cardiac cycles of heart tissue of a target object and ejection fraction confidence corresponding to each ejection fraction;
determining, based on the ejection fraction confidence, an ejection fraction of at least one of a plurality of cardiac cycles as an analysis result;
and outputting the analysis result.
33. The method of claim 32, wherein the at least one cardiac cycle is the cardiac cycle for which the highest confidence in ejection fraction corresponds.
34. An ultrasound imaging system, the ultrasound imaging system comprising:
an ultrasonic probe;
a transmitting circuit for controlling the ultrasonic probe to transmit ultrasonic waves to a heart part of a target object;
the receiving circuit is used for receiving the ultrasonic echo based on the ultrasonic wave returned from the heart part to obtain an ultrasonic echo signal;
the processor is used for acquiring an ultrasonic image of at least one scanning section of the heart part in real time according to the ultrasonic echo signals;
a memory for storing executable program instructions;
a processor for executing the program instructions stored in the memory, causing the processor to perform the method of analyzing cardiac ejection fraction as recited in one of claims 1 to 33;
and the display is used for displaying the visual information.
35. A system for analyzing cardiac ejection fraction, the system comprising:
a memory for storing executable program instructions;
a processor for executing the program instructions stored in the memory, causing the processor to perform the method of analyzing cardiac ejection fraction as recited in one of claims 1 to 33;
and the display is used for displaying the visual information.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117547306A (en) * | 2024-01-09 | 2024-02-13 | 深圳华声医疗技术股份有限公司 | Left ventricular ejection fraction measurement method, system and device based on M-type ultrasound |
| CN117918889A (en) * | 2024-03-20 | 2024-04-26 | 中国医学科学院北京协和医院 | Automatic calculation method and device for left ventricular cardiac output of transesophageal echocardiography four-chamber cardiac tangential plane |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117547306A (en) * | 2024-01-09 | 2024-02-13 | 深圳华声医疗技术股份有限公司 | Left ventricular ejection fraction measurement method, system and device based on M-type ultrasound |
| CN117547306B (en) * | 2024-01-09 | 2024-03-15 | 深圳华声医疗技术股份有限公司 | Left ventricular ejection fraction measurement method, system and device based on M-type ultrasound |
| CN117918889A (en) * | 2024-03-20 | 2024-04-26 | 中国医学科学院北京协和医院 | Automatic calculation method and device for left ventricular cardiac output of transesophageal echocardiography four-chamber cardiac tangential plane |
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