CN114762611A - Processing method of multiple dynamic parameters of body and application of processing method in ejection fraction - Google Patents

Abstract

The method for processing multiple dynamic parameters of the human body and the application of the method to ejection fraction acquire myoelectric, sound and M-ultrasonic signals by equipment which simultaneously acquires myoelectric signals, sound signals and M-ultrasonic images and comprehensively analyze the signals to obtain the accurate motion state of the human body. Particularly, by monitoring the electrocardiosignals, the cardiac ultrasonic images and the heartbeat sounds simultaneously and processing the electrocardiosignals, the cardiac ultrasonic images and the heartbeat sound signals to align time, the minimum distance and the maximum distance between the front wall and the rear wall of the left ventricle of the heart can be found in the cardiac ultrasonic images more accurately, and the minimum volume of contraction of the left ventricle of the heart and the maximum volume of the left ventricle of the heart during expansion are obtained through calculation so as to calculate the ejection fraction of the heart.

Description

The processing method of multiple dynamic parameters of the body and its application in ejection fraction

technical field

The present invention relates to a medical device, a signal processing method and its application.

Background technique

The human body (including other animal bodies) will generate muscle electricity through the command of the brain during exercise, hereinafter referred to as myoelectricity. Myoelectricity stimulates the movement of the human body. ECG is also a type of electromyography, which makes the heart beat.

The current technology can effectively monitor the generation of myoelectricity and the amount of electricity. The intensity of the EMG signal was recorded. For example, an electrocardiogram, you can know the waveform of the electrocardiogram.

At the same time, through ultrasound images, we can also know the shape and position of human muscles. When the body is in motion, it also produces sound, such as the sound of bone contact, the sound of the heart beating, etc. And when the human body moves, the above-mentioned myoelectric generation, muscle morphological changes, and sound generation are all synergistic and should be generated accordingly. For example, the beating of the heart first generates electrocardiogram, which drives the heart to produce changes in beating, and then the heart collides to produce sound (heartbeat sound).

Existing medical equipment can monitor EMG, morphological images, and sound separately, but there is currently no technology to monitor the three at the same time. For example, existing equipment can use morphological images to assist in the analysis of ejection fraction.

Ejection fraction refers to the percentage of stroke volume in the end-diastolic volume of the ventricle (ie, cardiac preload). The normal value is 50-70%. It can be checked by echocardiography and is one of the important indicators for judging the type of heart failure. The ventricular ejection fraction is the ratio of the stroke volume of the ventricle to the end-diastolic volume of the ventricle.

Ejection fraction is a volume ratio indicator that reflects the ejection function of the ventricle in terms of volume.

However, since only image information is provided for medical personnel, the above analysis of ejection fraction requires medical personnel to measure the image information, and then mark by their own hand movements in the image, and then calculate to obtain the ejection fraction, which is inconvenient to provide medical solutions quickly.

Therefore, in order to quickly obtain the relevant state information of the human body, to better assist the medical staff, and for the accuracy of the monitoring information of the human body by medical equipment, it is necessary to make full use of the electromyography and morphology generated and monitored when the human body moves. image, sound information.

SUMMARY OF THE INVENTION

In order to solve the above problems, the present invention provides a method for collecting multiple dynamic parameters of the body and the application of the method in the analysis of cardiac ejection fraction.

Among them, a method for collecting multiple dynamic parameters of the body is provided:

At least two of the ultrasonic signal, the electromyography signal, and the audio signal are collected from the same body by using a collection device with at least two collection functions of the ultrasonic signal collection function, the EMG signal collection function, and the audio signal collection function. The collected signals are displayed on the display device synchronously; the synchronization is that each signal is projected on the display device in real time, and the time difference between the signals projected on the display device is equal to the time difference between the signals projected on the display device The acquisition time difference of the signal.

The synchronous display, the specific method is:

S1: first obtain the required duration for the respective processing of ultrasonic signals, myoelectric signals, and audio signals; obtain the maximum duration among them, then compare the duration of the remaining signal processing with this maximum duration, and obtain the contrast duration; the described processing required duration, It is the required time from the acquisition to the acquisition of the signal until the signal is displayed on the display device.

S2: After processing the signal whose processing required duration is the maximum duration, it is displayed immediately;

The remaining signals are displayed immediately after the processing is completed and the comparison time has elapsed.

The above-mentioned method for collecting multiple dynamic parameters of the body is further described as follows: the ultrasound signal is a cardiac M-ultrasound image signal; the electromyographic signal is an electrocardiogram QRS wave signal, the audio signal for the heart sound.

The above-mentioned method for collecting multiple dynamic parameters of the body is further described as follows: the ECG QRS wave signal has a maximum duration; The specific comparison time is: 0.125S.

Among them, a method for obtaining cardiac ejection fraction using multi-dynamic parameter processing is provided:

Distribute the ECG QRS waves continuously collected from the same body during the same time period, and the M-ultrasound images of the cardiac morphological changes that occur synchronously with the ECG, and distribute them on the same time axis and align to the same starting time point;

In the M ultrasound image, at a time point after a first specific time period after one of the Q wave, R wave, and S wave in the electrocardiographic QRS wave is generated, the first longitudinal pixel column of the M ultrasound image is obtained, and the first longitudinal pixel column is obtained at the first longitudinal direction. Find the minimum value of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle in the pixel column;

In the M ultrasound image, at a time point after a second specific time period after one of the Q wave, R wave, and S wave in the electrocardiographic QRS wave is generated, the second longitudinal pixel column of the M ultrasound image is obtained, and the second longitudinal pixel column is obtained at the second longitudinal direction. Find the maximum value of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle in the pixel column;

And through the minimum and maximum values, the cardiac ejection fraction is calculated.

The above-mentioned method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing is further described as: the alignment to the same starting time point, specifically, using the method described in any one of the above claims 1-4. method, the collected ultrasonic signals and EMG signals are displayed on the display device synchronously; the display time difference of the ultrasonic signals and EMG signals projected to the display device in real time is equal to the collection time difference of the collected signals.

The above-mentioned method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing is further described as follows: the ECG QRS wave and the M-ultrasound image are obtained by a device having both the ECG QRS wave and the M-ultrasound image acquisition function. collected;

A continuous time axis and a real-time state axis are provided on the display device.

The above-mentioned method for obtaining cardiac ejection fraction using multi-dynamic parameter processing is further described as follows: the calculation method of the first specific time period and the second specific time period is: analyzing a plurality of binarized M ultrasound images, marking Calculate the time when the minimum value of the distance between the anterior intima of the left ventricle and the intima of the posterior wall of the left ventricle appears, and calculate the time difference between the time when one of the Q wave, R wave, and S wave appears and the time when the minimum value appears. , get the first specific duration;

And calculate the time difference between the time when one of the Q wave, the R wave, and the S wave appears and the time when the maximum value appears, to obtain a second specific time length.

The above-mentioned method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing is further described as follows: after obtaining the minimum and maximum values of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle, the following steps are used: The calculation formula EF=(EDV-ES)*100% calculates the cardiac ejection fraction, where EF is the cardiac ejection fraction, EDV is the maximum volume of the left ventricle of the heart at the maximum distance between the anterior and posterior intima of the left ventricle of the heart; ES left ventricle of the heart The minimum volume of the left ventricle of the heart at the minimum distance between the anterior and posterior intima;

Among them, the maximum volume of the left ventricle of the heart is calculated through the minimum distance between the anterior and posterior intima of the left ventricle of the heart;

The above-mentioned method for obtaining cardiac ejection fraction using multi-dynamic parameter processing is further described as follows: the M-ultrasound image is composed of horizontal pixel rows parallel to the time axis and vertical pixel rows perpendicular to the time axis.

Beneficial effects of the present invention:

The invention can accurately obtain the maximum distance and the minimum distance between the anterior and posterior walls of the left ventricle during the beating of the heart, so that the ejection fraction of the heart can be automatically obtained.

By continuously obtaining the left ventricle, the maximum distance between the anterior and posterior walls, the average and current values of the cardiac ejection fraction, as well as the maximum and minimum values of the cardiac ejection fraction can be dynamically known.

Description of drawings

FIG. 1 is a structural diagram of a multifunctional acquisition device for realizing the acquisition of ultrasound image information, heartbeat sound, and electrocardiogram by the same device in Example 1.

FIG. 2 is a schematic diagram of the control principle of the multi-function acquisition device introduced in Example 1 and Example 2.

FIG. 3 is a structural diagram of a multifunctional acquisition device for realizing the acquisition of ultrasound image information, heartbeat sound, and electrocardiogram by the same device in Example 2.

FIG. 4 is a schematic diagram of the control principle of the acquisition device for acquiring and processing ultrasound image information in Example 3. FIG.

FIG. 5 is a structural diagram of an acquisition device for acquiring and processing ultrasound image information in Example 3. FIG.

FIG. 6 is a schematic diagram of a specific method for synchronous display according to the present invention.

Detailed ways

The apparatus and method of the present invention are mainly used for the human body, and the body of the present invention mainly refers to the human body. Of course, it can also be applied to other animals besides the human body. The "human body" described below is a term used to refer to.

The realization of the present invention is preferably realized in the form of software codes, the steps of the present invention are edited into software codes, and installed in a computer with computing functions, for example, in the form of software codes, installed in smart phones, tablet computers, The mobile phone and tablet computer have the function of recognizing and reading M-mode echocardiography images.

Those of ordinary skill in the art can realize that each example algorithm step described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Skilled artisans may implement the described functionality using different methods for each particular application, but such implementations should not be considered beyond the scope of the present invention.

The implementation of the present invention is accomplished by installing a corresponding computer program in a computer with relevant hardware, the computer program can be stored in a computer-readable storage medium, and when the computer program is executed by the processor, it can realize the various steps required. Wherein, the computer program includes computer program code, and the computer program code may be in the form of source code, object code, executable file or some intermediate form, and the like. The computer-readable medium may include: any entity or device capable of carrying the computer program code, a recording medium, a U disk, a removable hard disk, a magnetic disk, an optical disk, a computer memory, a read-only memory (ROM, Read-Only Memory) , Random Access Memory (RAM, RandomAccess Memory), electric carrier signal, telecommunication signal and software distribution medium, etc. It should be noted that the content contained in the computer-readable media may be appropriately increased or decreased according to the requirements of legislation and patent practice in the jurisdiction, for example, in some jurisdictions, according to legislation and patent practice, the computer-readable media Excluded are electrical carrier signals and telecommunication signals.

In the computer of the present invention, the main hardware structure still includes the following main parts: central processing unit, memory, chipset, I/O bus, I/O equipment, power supply, chassis and related software, related software refers to the ability to The software that puts the M-mode echocardiography (M-echo) image on the display screen, of course, the M-mode echocardiogram can also not be displayed in the form of images, but the computer background processes and processes the images by itself. calculation, and finally only the calculation result is displayed on the display.

Example one:

The body information of the human body is collected through a multi-functional collecting device provided with a probe for transmitting and collecting ultrasonic signals, a sound collecting head and an electromyographic collecting electrode. Ultrasound image information, sound information and electromyography information are collected respectively. Specifically, the heartbeat information of the human body is collected through a multi-functional collection device provided with a probe for transmitting and collecting ultrasonic signals, a sound collection head, and an ECG collection electrode, and the cardiac ultrasound image information, heartbeat sound, ECG, and ECG are respectively collected. .

Referring to the following devices, the same device can separately collect ultrasound image information, heartbeat sound, and electrocardiogram.

Referring to FIG. 1 , the present embodiment provides a multifunctional stethoscope, including a device main body 5 , a single-array element ultrasonic probe 2 is arranged on the device main body 5 , an ECG sensor is arranged on the device main body 5 , and a charging interface is arranged at the lower end of the device main body 5 ; The device main body 5 is provided with a control circuit board for controlling the operation of the device main body 5, interactively transmitting data with the mobile client terminal, and a power supply module for supplying power to the entire stethoscope main body. The charging interfaces are respectively connected to the power supply modules, and the power supply modules include rechargeable batteries.

The single-array element ultrasound probe 2 and the ECG sensor are integrated into a device body 5, so that the probe can realize the functions of ultrasound and ECG.

The device body 5 is provided with a pickup 4, the ECG sensor is a three-lead ECG electrode, and the three-lead ECG electrode is composed of three ECG electrodes 3 evenly arranged on the front end of the device body 5, and a single-array element ultrasonic probe 2 Located in the middle of the front end surface of the device body 5 , the pickup 4 is located on one side of the front end surface of the device body 5 .

The detection function of heart sound, fetal heart rate monitoring, breathing sound and bowel sound can be realized through the pickup 4. During the actual operation, the sound output of the stethoscope can be through the speaker of the mobile client terminal, or through the Bluetooth headset connected with the stethoscope, and the waveform graph can be displayed on the display of the mobile client terminal at the same time.

The device main body 5 includes an upper casing 6, a main casing 7 and a lower casing which are connected in sequence from top to bottom. The control circuit board is located inside the main casing 7. The upper end of the device main body 5 is provided with a protective cover 1 covering it. The surface of the casing 6 is provided with teeth 601 that can clamp the inner side of the protective cover 1 , the upper casing 6 is screwed with a hollow cover 401 , and the inner side of the hollow cover 401 is provided with a membrane 402 located above the pickup 4 .

The structure of the device control circuit board, the ECG sensor, the single-element ultrasonic probe 2, and the pickup 4 is shown in Figure 2.

The shell part of the device body 5 is divided into an upper shell 6, a main shell 7 and a lower shell, which can reduce the difficulty of the production process. Avoid contamination of the pickup 4, the ECG electrodes 3 and the membrane sheet 402 by foreign objects.

There is a main control chip on the control circuit board, which is used to process the detection data of the single-element ultrasonic probe 2, the ECG sensor and the pickup 4, and convert it into readable data in the form of numerical values and curves; data transmission module It is used to transmit the data generated by the main control chip to the mobile client terminal. The flash memory chip FLASH is used to store all the data generated by the main control chip, and the flash memory chip FLASH is connected with the main control chip.

The single-element ultrasonic probe 2 is connected to the main control chip through an ultrasonic channel, the pickup 4 and the ECG sensor are connected to the main control chip through a composite channel, and the mobile client terminal of the client terminal is connected to the main control chip through a data transmission module.

In this embodiment, the multi-functional stethoscope can simultaneously use the single-element ultrasonic probe to collect ultrasonic image information, the pickup 4 to collect the heartbeat sound, and the electrocardiogram sensor to collect the electrocardiogram information. At the same time, the three collecting heads collect the above-mentioned information at the same time and basically at the same position (for example, at the heart of the left chest of a human body). Therefore, the collected information is real-time and aimed at the same body.

Example two:

Referring to the device of the following Chinese patent CN209695222U, the same device can separately collect ultrasound image information, heartbeat sound, and electrocardiogram.

Its structure includes, with reference to Figure 2 and Figure 3:

1. Single-element ultrasound probe, used to detect cardiac ejection fraction (LVEF). The cardiopulmonary function probe includes an ECG sensor for detecting heart rate ECG, the ECG sensor is a three-lead ECG electrode, and the respiration rate sensor is a capacitive respiration sensor. Respiratory rate sensor that detects respiratory rate RR. The single-element ultrasonic probe is connected to the main control chip through the ultrasonic channel, the ECG sensor and the respiratory rate sensor on the cardiopulmonary function probe are connected to the main control chip through the composite channel, and the mobile client terminal of the client terminal is connected to the main control chip through the data transmission module. , the single-array element ultrasound probe and the cardiopulmonary function probe are located on the front face of the stethoscope main body, and the ECG sensor and the respiratory rate sensor are fixed side by side as a whole. Single-element ultrasound probes include:

(1) Ultrasonic transducer, the single-array element ultrasonic probe includes a device for transmitting ultrasonic waves to the human body and receiving echo signals; (2) a transmitting circuit for controlling the ultrasonic transducer to transmit ultrasonic waves to the human body; (3) a receiving circuit, It is used to receive the echo signal of the ultrasonic transducer; (4) the interface circuit is used to connect with the main control chip in the main body of the stethoscope through the ultrasonic channel; (5) the controller is used to control the operation of the transmitting circuit and detect the receiving circuit Whether there is an echo signal and store the echo signal. The controller includes a transmission control module, a data storage module, a reception control module and an interface control module. The transmission control module is connected to the transmission circuit through the transmission control bus, the data storage module is connected to the reception circuit, and the reception circuit is connected to the reception control module through the reception control bus. , the interface control module is connected with the interface circuit. (6) and transmit control bus, receive switch circuit and receive control bus.

2. The main control chip, referring to Fig. 2, is used to process the detection data of the single-element ultrasonic probe, the ECG sensor and the respiratory rate sensor, and convert it into readable numerical value and data in the form of a curve.

3. The data transmission module is used to transmit the data generated by the main control chip to the mobile client terminal.

4. The power module is used to supply power to the entire stethoscope body.

5. The power switch is used to turn on or off the power supply of the power module.

6. The flash memory chip FLASH used to store all the data generated by the main control chip, and the flash memory chip FLASH is connected with the main control chip.

The data transmission module is a USB interface and/or a Bluetooth module. The mobile client terminal is a mobile phone terminal. There are no less than two cardiopulmonary function probes. The stethoscope body is cylindrical.

During the implementation process, the front surface of the stethoscope body is pressed against the parts of the patient's lungs and heart that need to be auscultated, so that the single-array ultrasonic probe, ECG sensor and respiratory rate sensor on the front surface of the stethoscope body are in contact with the surface of the auscultation site, and the main control chip Send electrical signals for detection to the single-array element probe, ECG sensor, and respiratory rate sensor respectively. The single-array element probe, ECG sensor, and respiratory rate sensor detect the body part and return the detection data to the main control chip. The control chip processes the detection data returned by the single-array element probe, ECG sensor and respiratory rate sensor respectively to obtain the values of ejection fraction LVEF, heart rate ECG and respiratory rate RR in real time, and converts the continuously obtained specific values into curve. The main control chip will obtain the values of ejection fraction LVEF, heart rate ECG and respiratory rate RR and the corresponding curves, and transmit them to the mobile client through the data transmission module. The doctor can view and obtain the respiratory rate RR, heart rate ECG and The specific value of the cardiac ejection fraction LVEF. The flash memory chip FLASH stores all the values and curves generated by the main control chip. The main control chip can transmit the values and curves stored in the flash memory chip FLASH to the mobile client terminal for detailed viewing and analysis through the data transmission module. Detects data loss in the event of an unexpected power outage.

When using the device of CN209695222U, the respiratory rate sensor needs to be changed to the microphone 4 in Example 1, so as to realize the heartbeat sound collection function required by the present invention.

In this embodiment, the multifunctional stethoscope can simultaneously use the single-array ultrasonic probe to collect ultrasonic image information, the pickup to collect the heartbeat sound, and the electrocardiographic sensor to collect the electrocardiographic information. At the same time, the three collecting heads collect the above-mentioned information at the same time and basically at the same position (for example, at the heart of the left chest of a human body). Therefore, the collected information is real-time and aimed at the same body.

Example three:

In the above examples 1 and 2, ultrasonic image information needs to be processed and ultrasonic image information is collected, and the device of the following Chinese patent CN209751086U can be referred to, which can collect ultrasonic image information and process ultrasonic image information. Refer to Figure 4 and Figure 5.

This embodiment includes an ultrasonic transducer for sending out a scanning beam, a digital control processing chip for controlling the ultrasonic transducer to send out a scanning beam and collecting echo signals, for sending control instructions to the digital control processing chip and viewing the scanned image The portable control terminal, and transmit-receive multiplexing circuit, transmit-receive switching circuit, transmit circuit, receive circuit, USB interface circuit, low power module and ultrasound instrument shell.

The transmit-receive switching circuit, the transmit-receive multiplexing circuit and the ultrasonic transducer are connected in series in sequence, and the transmit circuit and the receive circuit are respectively connected with the transmit-receive switch circuit. The receiving switching circuit, the transmitting circuit, the receiving circuit and the USB interface circuit are all encapsulated in the ultrasonic instrument shell. The ultrasonic transducer is located at the front end of the ultrasonic instrument case. The front end of the ultrasonic instrument case is a coupling plane, and the USB interface circuit is located in the ultrasonic instrument case. rear end of the body.

The low power module is provided with:

1. The digital power supply is used to provide suitable power for the digital control processing chip, the transmitting and receiving switching circuit, the transmitting circuit and the transmitting and receiving multiplexing circuit. The digital power supply is provided with a linear voltage regulator to protect its voltage stability, and the digital control The processing chip, the transmitting and receiving switching circuit, the transmitting circuit and the transmitting and receiving multiplexing circuit are respectively connected with the digital power supply;

2. The analog power supply is used to provide suitable power for the transmitting and receiving multiplexing circuit and the receiving circuit. The analog power supply is provided with a linear voltage regulator to protect its voltage stability. The transmitting and receiving multiplexing circuit and the receiving circuit are respectively connected with the analog power supply. connect;

3. The adjustable high-voltage DC converter is used to provide a suitable high voltage for the transmitting circuit, and the transmitting circuit is connected with the adjustable high-voltage DC converter;

4. The overcurrent protector is used to limit the current intensity provided to the digital power supply, the analog power supply and the adjustable high voltage DC converter. The digital power supply, the analog power supply and the adjustable high voltage DC converter pass through the overcurrent protector and the USB interface circuit respectively. connect.

The front surface of the ultrasonic instrument shell is a coupling plane, and the digital control processing chip is provided with:

1. The transmit beam control module is used to control the transmit and receive switching circuit to open the transmit circuit channel and close the receive circuit channel, and to control the ultrasonic transducer to send out scanning beams. The transmit beam control module is connected to the transmit circuit through the transmit control bus.

2. The receiving control module is used to detect whether there is an echo signal in the transmitting and receiving multiplexing circuit, and to control the transmitting and receiving switching circuit to open the receiving circuit channel and close the transmitting circuit channel, and the transmitting and receiving switching circuit and the transmitting and receiving multiplexing circuit pass through the receiving circuit. The control bus is respectively connected with the receiving control module.

3. The data processing module is used to receive and collect echo signals, and the data processing module is connected to the receiving circuit;

4. The interface control module is used to control the alternate operation of the transmit beam control module and the receive control module, and to send the echo signals collected by the data processing module to the portable control terminal. The transmit beam control module and the receive control module are respectively connected to the interface control module , the interface control module is connected with the portable control terminal through the USB interface circuit.

The digital control processing chip is an FPGA programmable digital gate array processing chip. The portable control terminal is a mobile phone terminal.

In the implementation process, the portable control terminal supplies power to the ultrasound instrument through the USB interface circuit, the digital power supply can provide suitable power for the digital control processing chip, the transmit-receive switching circuit, the transmit circuit and the transmit-receive multiplexing circuit, and the analog power supply can provide power for the transmit and receive multiplexing circuits. The receiving multiplexing circuit and the receiving circuit provide suitable electrical energy, the adjustable high-voltage DC converter provides suitable high voltage for the transmitting circuit, and both the digital power supply and the analog power supply are provided with linear voltage regulators to protect their voltage stability.

Send an instruction to scan to the ultrasound machine through the portable control terminal, and the digital control processing chip controls the transmit-receive switching circuit to open the transmit circuit channel and close the receive circuit channel through the transmit circuit, thereby controlling the ultrasonic transducer to send out a scanning beam, and the ultrasonic transducer will The obtained echo signal is sent to the transmit-receive multiplexing circuit. When the digital control processing chip detects that the transmitting and receiving multiplexing circuit has an echo signal, the digital control processing chip controls the transmitting and receiving switching circuit to open the receiving circuit channel and close the transmitting circuit channel, and the echo signal is sent to the transmitting and receiving switching circuit and the receiving circuit in turn. The digital control processing chip collects the echo signals, and the collected echo signals are sequentially sent to the portable control terminal through the USB interface circuit, and the portable control terminal processes the collected echo signals to obtain ultrasonic images and display them come out.

The voltage of the portable control terminal to power the ultrasound instrument does not exceed 5V and the current does not exceed 1500mA. The overcurrent protector limits the voltage of the portable control terminal input to the low power module not to exceed 500mA. The digital power supply can output 3.3V, 300mA and 1.2V, 460mA. A kind of adaptable power supply, the analog power supply can output 3.3V, 400mA adaptable power supply.

It can be seen from the foregoing that the ultrasound instruments are powered by portable control terminals, and the low power module in the ultrasound instruments can convert the electric energy input by the portable control terminal into suitable electric energy, so it can meet the miniaturization requirements of the ultrasound instruments.

According to scanning requirements, a command for scanning is sent to the ultrasound machine through the portable control terminal, the convex array scanning is used to scan the abdomen of the human body, and the scanning is used to scan the superficial parts of the human body. The transmitting beam control module controls the transmitting and receiving switching circuit to open the transmitting circuit channel and close the receiving circuit channel through the transmitting circuit. The transmitting beam control module controls the ultrasonic transducer to send out a scanning beam, and the ultrasonic transducer sends the obtained echo signal to the transmitting and receiving complex. use circuit. When the receiving control module detects that there is an echo signal in the transmitting and receiving multiplexing circuit, the receiving control module controls the transmitting and receiving switching circuit to open the receiving circuit channel and close the transmitting circuit channel, and the echo signal is sent to the data processing through the transmitting and receiving switching circuit and the receiving circuit in turn. module, the data processing module collects the echo signals, and the collected echo signals are sequentially sent to the portable control terminal through the interface control module and the USB interface circuit, and the portable control terminal processes the collected echo signals to obtain ultrasonic images and display them come out.

After the portable control terminal sends an instruction to scan to the ultrasound machine, the transmit beam control module controls the ultrasound transducer to send out scanning beams, and the interface control module controls the transmit beam control module and the receive control module to operate alternately, so that the ultrasound machine can realize ultrasound scanning. Function.

Example four:

The method of obtaining cardiac ejection fraction using multi-dynamic parameter processing is as follows:

1. Using the acquisition device provided in Examples 1, 2, and 3, which has both ultrasonic signal acquisition functions and EMG signal acquisition functions, the ultrasonic signals and EMG signals are collected from the same body, and the collected signals are displayed synchronously on the display device.

The same organism here refers to the human body or the human heart. The ultrasound signal information is M echocardiography, and the electromyographic information is an electrocardiogram signal, which is shown in the electrocardiogram QRS wave electrocardiogram. Since the beating of the heart is the contraction movement of the heart stimulated by the heart, therefore, one ECG information corresponds to the periodic beating of the heart, and therefore, the corresponding synchronization between the ECG signal and the cardiac cycle beating, the corresponding synchronization here is not It means to proceed simultaneously, but to follow accordingly.

2. The synchronous display described in the above step 1 is as follows: the collected ECG QRS waves and the M-ultrasound images of the cardiac morphological changes that occur synchronously with the ECG are distributed on the same time axis and aligned together. start time point. The collected ultrasonic signals and EMG signals are displayed on the display device synchronously; the display time difference of the ultrasonic signals and EMG signals projected to the display device in real time is equal to the collection time difference of the collected signals.

The details are as follows: Since the acquisition device is completed on the same body by using the acquisition device with both the ultrasonic signal acquisition function and the electromyographic signal acquisition function, and is displayed on the same display device (display), therefore, the acquisition part of the acquisition device (refer to Fig. 1, for example, single-array element ultrasonic probe 2, pickup 4, ECG sensor/electrode electrode 3) obtain the above-mentioned signals, because the human heartbeat is excited by ECG, therefore, within a heartbeat cycle (from the early stage of cardiac systole to the Before diastole), the ECG signal is generated first, and then the cardiac morphological change is generated. Therefore, there is a time difference between the ECG signal collected by the acquisition part of the acquisition device and the cardiac morphological change (because there is ECG first, and then there is cardiac/heart morphology. Change), this time difference should be accurately reflected on the display device, so this time difference should be calculated by the method, and correspondingly and faithfully respond, so that the real-time projection of the ultrasonic signal and the EMG signal on the display device The display time difference is equal to the collected data. The acquisition time difference of the signal.

3. In the M ultrasound image, at a time point after the first specific time period after one of the Q wave, R wave, and S wave in the QRS wave of the ECG is generated, the first longitudinal pixel column of the M ultrasound image is obtained, and in the first Find the minimum value of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle in a longitudinal pixel column. In the M ultrasound image, at a time point after a second specific time period after one of the Q wave, R wave, and S wave in the QRS wave of the electrocardiogram is generated, the first longitudinal pixel column of the M ultrasound image is obtained, and the second longitudinal pixel column is obtained. Find the maximum value of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle in the pixel column.

The calculation method of the first specific time period and the second specific time period is: analyze several M ultrasound images processed by binarization, and mark the occurrence of the minimum value of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle. time, and calculate the time difference between the time when one of the Q wave, R wave, and S wave appears and the time when the minimum value appears, and obtain the first specific duration; and calculate the time when one of the Q wave, R wave, and S wave appears. The time difference between the time when the maximum value occurs and the time when the maximum value occurs, the second specific duration is obtained. It is necessary to take into account that different organisms may have different ECG cycles, and within a cycle, each wavelength is slightly different. ECG has QRS complex, which is composed of Q wave, R wave and S wave. For example, the heart of a certain body is as follows: after the occurrence of ECG R wave, after the first specific time period of 0.40s, the heart enters contraction At the end of the period, the minimum volume is reached, which is the rapid ejection period; after the R wave occurs, and after a second specific period of 0.80s, the heart enters the end of the diastolic period and reaches the maximum volume. Here, the occurrence time of the R wave is used as the starting point, because the characteristic point of the R wave is the most obvious, that is, the peak value of the wave is the largest, and it is easiest to identify. Of course, other Q waves, S waves, T waves, and P waves can also be used as the starting point. These peaks are all in one heartbeat cycle, and each heartbeat cycle has these waves. Therefore, which wave peak is used as the starting point it is not important. When the R wave is used as the starting point: after the first specific period of 0.40s, the heart enters the end of systole and reaches the minimum volume; and after the second specific period of 0.80s, the heart enters the end of diastole and reaches the maximum volume; the Q wave As a starting point: after the Q wave occurs, the heart enters the end of systole and reaches the minimum volume after the first specific period of 0.36s; and after the second specific period of 0.76s, the heart enters the end of diastole and reaches the maximum volume. The images of the smallest and largest volumes will be captured by ultrasound, producing an M echocardiogram.

Through the stated minimum and maximum values, through the following calculation formula:

EF=(EDV-ES)*100% to calculate the cardiac ejection fraction, where EF is the cardiac ejection fraction, EDV is the maximum volume of the left ventricle at the maximum distance between the anterior and posterior walls of the left ventricle of the heart; ES The minimum volume of the left ventricle of the heart at the minimum intimal distance;

Among them, the maximum volume of the left ventricle of the heart is calculated through the minimum distance between the anterior and posterior intima of the left ventricle of the heart;

M-ultrasound image of the present invention: M-ultrasound image is an image composed of a number of dense pixel points. These pixel points are arranged in a matrix and divided into horizontal pixel rows parallel to the time axis and vertical pixel rows perpendicular to the time axis. Both a vertical pixel row and the first vertical pixel row are one of many vertical pixel rows.

On this basis, in order to find the minimum and maximum values of the distance between the left ventricular anterior intima and the left ventricular posterior intima in a frame of M ultrasound images, the ECG QRS complex time can be used to Relationship with the end of systole and end of diastole.

When relying on this relationship, it is satisfied that: each signal is projected on the display device in real time, and the time difference between the signals projected on the display device is equal to the acquisition time difference of the acquired signals; In one frame of M ultrasound image, the time difference between the electrocardiogram and the ultrasound image projected to the display device is equal to the acquisition time difference between the electrocardiogram signal and the ultrasound signal being transmitted to the acquisition head. For example, the ECG R-wave signal is generated from the body, and is collected by the EMG acquisition electrode in Example 1 at 0s, and when the R-wave signal is generated from the body, the heart enters the end of systole after the first specific time period of 0.40s. That is to say, the single-array element ultrasound probe collects the image of the heart entering the end of systole in 0.40s, so the time when the ultrasound image and the R-wave signal are collected, there is a 0.40s acquisition time difference, that is to say, the acquisition time difference is 0.40 s. However, it takes 0.5s to collect the R-wave signal from the EMG acquisition electrode and project it to the display. It only takes 0.37s to collect the cardiac image from the single-element ultrasound probe to the image is projected on the display. If the ECG R-wave signal is Direct projection with the ultrasound image signal will cause the R-wave signal seen on the monitor to generate 0.37s after the heart enters the end of systole. Therefore, this time difference is wrong, and the actual time difference between the ECG and the image on the body must be reflected on the monitor to avoid calculation errors.

After processing the acquisition time difference and the display time difference, the QRS wave of the ECG can be strictly mapped to the ultrasound image to find the end of the heart entering the diastolic phase (maximum volume, or the maximum value), for example, when the R wave occurs first After a specific time period of 0.40, the corresponding row of pixels (the first longitudinal pixel row) on the M ultrasound image is the end of the systole of the heart, reaching the minimum volume and the minimum value. After the R wave occurs for a first specific duration of 0.80s, the corresponding row of pixels (the second longitudinal pixel row) on the M ultrasound image is the end of the diastolic phase of the heart, that is, the maximum volume and the maximum value.

Example five:

As mentioned in Example 4: The actual time difference between the ECG and the image on the body is reflected on the display to avoid calculation errors. The method is as follows:

Using the acquisition devices provided in Examples 1, 2, and 3, which simultaneously have at least two acquisition functions among the three functions of ultrasonic signal acquisition, EMG signal acquisition, and audio signal acquisition, the ultrasonic signals, At least two kinds of signals in the electromyography signal and the audio signal, and the collected signals are displayed on the display device synchronously.

A continuous time axis and a real-time state axis are provided on the display device. The time axis referred to in the present invention is the horizontal axis projected on the display device; the real-time state axis can also be called the changing state axis, the real-time state axis is the vertical axis that is put on the display device, and the time axis and the changing state axis are embodied in On the display device, you can see the relationship between the changing state of the signal and time.

The synchronous display here is as follows: each signal is projected onto the display device in real time, and the time difference between the signals projected onto the display device is equal to the acquisition time difference of the acquired signals.

Due to the collected ultrasonic signal, EMG signal, and audio signal, at least one signal is affected by the processing circuit, so that the display time lags behind the rest of the signals; therefore, the time when the signal affected by the processing circuit is put on the display device lags behind the rest of the signals. Specifically, due to the circuit reasons of various electronic original devices and the reason why the software processes the collected information, there is a time difference between the signal acquisition and the signal presentation, and different information sources have different time differences, for example: the sound of the heartbeat passes through the circuit And software processing can be very fast, ultrasound images can also be fast, but the ECG signal is relatively slow from acquisition to presentation, about 0.125S. Therefore, in order to make the presented information consistent, the presented information needs to be adjusted. This is the so-called "synchronization".

The delay time brought by the same circuit and the same software for signal processing is consistent, so we can calculate the delay time of electrical signal processing according to the characteristics of the circuit and software. Even better is to actually test the software and the circuit to get the time required by the software and the circuit to process the signal. We record this time. The ultrasonic signal, the heartbeat sound signal and the electrocardiogram signal have the same processing steps and have different required processing times. We recorded the ultrasound signal, the heartbeat sound, the signal and the ECG signal. The processing time required for each of the three is the longest time required to process the ECG signal. Therefore, when we present the three signals, when the heartbeat sound After the ultrasound signal is processed, we do not present it immediately, but delay and wait until the processing of the ECG signal is completed. The waiting time is the delay difference between the ECG signal recorded in advance and the other two (ultrasound signal, sound signal). After the sound signal and the ultrasound image signal are processed, the sound signal and the ultrasound signal can be presented after waiting for the above delay difference; at the same time, the ECG signal is also processed and presented immediately; thus the presented ultrasound The signal heart, the electrical signal and the sound signal are synchronized and aligned in time (ie, the acquisition state).

The specific method of synchronous display is, refer to Figure 6:

S1: First obtain the time required for the respective processing of the ultrasonic signal, the EMG signal, and the audio signal, for example: the ultrasonic signal processing time is 0.5s, the EMG signal is 0.625s, and the audio signal is 0.5s; the maximum time obtained is the EMG signal 0.625 s, and then compare the duration of the remaining signal processing with the maximum duration, subtract 0.5s of the audio signal (or ultrasound) from the maximum duration of 0.625, and obtain a comparison duration of 0.125s; the duration required for the processing is from the acquisition to the signal Acquisition time until the signal is displayed on the display device. For example, the ECG R-wave signal is generated from the body, and is collected by the EMG acquisition electrode in Example 1 at 0s, and it needs to be projected on the display. 0.625s.

S2: After the processing of the signal with the maximum duration required for processing is completed, it is displayed immediately; the remaining signals are displayed immediately after the processing is completed and the comparison time has passed. That is to say, after the ECG signal is processed, it will be displayed on the display immediately, and the delay of putting it on the display is 0.625s. After the processing of the rest of the signals is completed, and the comparison time has passed for 0.125s, it will be displayed immediately and put on the display. The delay to the display is 0.625s, so the time difference (delay) put into the display is equal. Make the time difference situation of the ECG and image seen on the monitor complete to be the real time difference situation.

The ultrasound signal is a cardiac M-ultrasound image signal; the electromyographic signal is an electrocardiographic QRS wave signal, and the audio signal is a heart sound.

Example six:

For the calculation method of calculating the minimum volume and the maximum volume of the heart through the image pixels required in Example 4, please refer to the following example.

In the analysis of cardiac ejection fraction, it is necessary to know the minimum volume of the heart during systole and the maximum volume of the heart during expansion.

When the device software is used for automatic identification, since the device software cannot accurately identify the maximum volume and the minimum volume of the heart through the ultrasound image, we inject the heartbeat sound and the ECG waveform into the device software. When the device software obtains the ECG waveform After the image (and the heartbeat sound), from the continuously changing ECG waveform, corresponding to the corresponding continuously changing ultrasound image, to find the most appropriate cross-sectional shape of the distance between the anterior and posterior walls of the heart. E.g:

It can be 0.04 seconds after the ECG R wave, which corresponds to the continuously changing ultrasound image. This section is the minimum value of the anterior and posterior walls of the left ventricle of the heart. , since the section has delineated a very small area, it is very easy to find the distance between the front and rear walls in this very small area through image recognition. The method of image recognition can be various methods: for example, the color block identification method and device provided by CN201310125145.X disclosed by Chinese patent, by performing edge detection on the image to be recognized, extracting the contour of the color block in the image to be recognized to determine the color block The shape of the color block is calculated according to the contour of the extracted color block to obtain the position of the color block, and the color of a point in the color block is selected to determine the color of the color block. Therefore, it can identify the shape, position and color of the color block at the same time, so that the information of the color block can be extracted more comprehensively. The method of image recognition can be various methods: such as grayscale recognition.

The method of image recognition can be various methods, for example, Chinese patent CN202010409334.X can be used for a lung ultrasound image recognition method and some methods in the system.

A normalized grayscale image is obtained after graying and normalizing the image of the effective area respectively.

Use the following formula to grayscale the image in the effective area:

Gray=R*0.299+G*0.587+B*0.114, where R, G, and B are red, green and blue components, respectively.

The normalized grayscale images are respectively scaled to a uniform size and an image to be recognized is formed.

The normalized grayscale image is scaled to a uniform size, for example, an image to be tested with a size of 256*256. Preferably, bilinear interpolation, cubic spline interpolation, or Lanczos interpolation is used for scaling.

The minimum value of the distance between the anterior and posterior walls of the left ventricle can be found by the method of graphic recognition, and the heart volume can be obtained when the heart contracts to the minimum. volume. The ejection fraction can be obtained by taking the injected blood fraction analysis formula.

Example seven:

For the calculation method of calculating the minimum volume and maximum volume of the heart through the image pixels required in Examples 4 and 6, you can refer to the following example.

1. To calculate the minimum and maximum cardiac volumes, a method for determining the intimal boundary of the left ventricular septum and the intimal boundary of the posterior wall of the left ventricle is required on echocardiography. as follows:

S1: Set a virtual centerline from the echocardiogram, and the virtual centerline is approximately at the same distance from the upper boundary to the lower boundary;

From the virtual centerline, the echocardiograms are: upper echocardiogram with mitral valve image and left ventricular septal endometrial image; and echocardiogram lower image with left ventricular posterior wall intima border;

S2: The upper image of the echocardiogram is processed to obtain the border of the left ventricular septum. The echocardiogram below was processed to obtain the intimal border of the posterior left ventricular wall.

2. Among them, the method of processing the upper image of the echocardiogram to obtain the boundary of the left ventricular septum is as follows:

S01: On an echocardiogram with images of the mitral valve and the intima of the left ventricular septum, determine the approximate extent of the intima of the left ventricle and the adjacent areas of the mitral valve by:

(1): On echocardiography, take the continuous edge close to the mitral valve side as the upper boundary of echocardiography, and set the pixel row below the upper boundary and 30 pixels away from the upper boundary as the calculation starting line :

(2): At the calculation starting point line, downward, count the percentage of black pixels in each pixel row parallel to the calculation starting point line;

(3): When the first pixel row with at least 35% black pixels is obtained, it is the upper edge of the approximate range;

(4): Obtain the bottom line of the approximate range as follows: (1) Continue to count the percentage of black pixels in each pixel row along the top line of the mitral pixel block domain. When the proportion of the pixel row is the largest, the corresponding pixel row is the lower edge of the approximate range; (II) when a plurality of pixel rows are obtained that satisfy the above condition (I), then the first one closest to the upper edge of the range is obtained. A pixel row that satisfies the above condition (I) is the lower boundary line of the approximate range.

S02: Within a rough range, find the pixel block domain of the adjacent regions of the left ventricular septum intima and the mitral valve, the method is: within the rough range, search line by line from the upper range line to the lower range line, and at least satisfy The search conditions are as follows: (I) In the same column of pixels, the gray value of the pixel increases by at least ten pixels from the upper range line to the lower range line; (II) The first one found has the above (I) characteristics The range is the pixel block domain of the left ventricular septal intima and the adjacent areas of the mitral valve. When the search conditions are satisfied, in the pixel block domain of the found adjacent regions of the left ventricular septum intima and the mitral valve, one and only one of the following situations is allowed, and this situation is regarded as noise: (I) There is no The gray value of more than 2 pixels stops increasing compared to the previous pixel; (II) the gray value of one pixel decreases compared to the previous pixel.

S03: Set the gray value of the pixel block domain of the adjacent area to 0;

S04: Perform binarization processing on the echocardiogram including the adjacent regions where the pixel block domain gray value is set to 0, and obtain the echocardiogram in which the adjacent region and the mitral valve region are both excluded from the left ventricular septal intima Valued echocardiography.

S05: Delineate the region of interest on the binarized echocardiogram, and the region of interest includes all the images of the left ventricular septal intima boundary; the calculation method of the region of interest: on the echocardiography, the region close to the mitral valve The continuous edge on the side is the upper boundary of the echocardiogram, and the pixel row below the upper boundary and 30 pixels away from the upper boundary is set as the first boundary of the region of interest. Obtain the second boundary of the region of interest as follows: (1) Continue to count down the first boundary of the region of interest and count down the percentage of black pixels in each pixel row. When the proportion of black pixels in the pixel row is the largest, The corresponding pixel row is the second boundary of the region of interest; (II) when a plurality of pixel rows are obtained that satisfies the above condition (I), the first one closest to the first boundary of the region of interest satisfies the above condition (I). ) is the second boundary of the region of interest.

The region of interest is between the first boundary of the region of interest and the second boundary of the region of interest.

S06: Perform morphological opening operation on the region of interest to make the binarized echocardiogram smoother; then perform edge detection to obtain the left ventricular septal intima border;

S07: Perform a closing operation on the obtained left ventricular septal intima boundary, and make the obtained left ventricular septal intima boundary a connected domain. This is the final left ventricular septal endometrial border.

3. Among them, the method for obtaining the intimal boundary of the posterior wall of the left ventricle by processing the following echocardiogram is as follows:

1: Binarized ultrasound image; the continuous edge on the side close to the mitral valve is the upper boundary of echocardiography; the continuous edge on the opposite side of the upper boundary is the lower boundary of echocardiography;

From the echocardiogram, the same distance from the upper boundary to the lower boundary is the virtual midline, starting at the virtual midline, and going down the boundary direction, in units of pixel columns, and counting the row position of the first white pixel in each column;

2: In the statistical data, if the row where the white pixel is located for the first time, and the distance from the upper boundary is more than 45 pixels, the column is the data error column;

3: Use the following methods to correct the data error in the column:

(1) Merge adjacent columns with wrong data into one error interval; (2) Set the row where the white pixel point first appears where the adjacent correct data column on the left side of the error interval is located as the first reference point, Set the row of the first white pixel point where the correct data column adjacent to the right side of the error interval is located is set as the second reference point; a straight line connects the first reference point and the second reference point, and the straight line is the left ventricular posterior of the error interval. Intima border.

4: Perform morphological opening operation to make the binarized echocardiogram smoother; then perform edge detection to obtain the intimal boundary of the posterior wall of the left ventricle.

5: Perform a closed operation on the obtained posterior intima boundary of the left ventricle, and make the obtained posterior intima boundary of the left ventricle a connected domain. This is the intimal border of the posterior wall of the left ventricle.

After obtaining the minimum and maximum values of the distance between the intima of the anterior wall of the left ventricle and the intima of the posterior wall of the left ventricle, the cardiac ejection fraction is calculated by the following formula: EF=(EDV-ES)*100%, where EF is the cardiac ejection fraction, EDV is the maximum volume of the left ventricle when the distance between the anterior and posterior intima of the left ventricle is the largest; ES is the smallest volume of the left ventricle when the distance between the anterior and posterior intima of the left ventricle is the smallest;

Among them, the maximum volume of the left ventricle of the heart is calculated through the minimum distance between the anterior and posterior intima of the left ventricle of the heart;

The above are the various embodiments enumerated for implementing the present invention. In the foregoing embodiments, the description of each embodiment has its own emphasis. For parts that are not described or described in detail in a certain embodiment, reference may be made to the relevant descriptions of other embodiments.

The above-mentioned embodiments are only used to illustrate the technical solutions of the present invention, but not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that: it can still be used for the foregoing implementations. The technical solutions described in the examples are modified, or some technical features thereof are equivalently replaced; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the spirit and scope of the technical solutions of the embodiments of the present invention, and should be included in the within the protection scope of the present invention.

The above are only specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto. Any person skilled in the art can easily think of various equivalent modifications or changes within the technical scope disclosed by the present invention. Replacement, these modifications or replacements should all be covered within the protection scope of the present invention. Therefore, the protection scope of the present invention should be subject to the protection scope of the claims.

Claims (10)

1. A method for collecting multi-dynamic parameter processing of an organism is characterized in that an acquisition device which has at least two acquisition functions of an ultrasonic signal acquisition function, an electromyographic signal acquisition function and an audio signal acquisition function at the same time is adopted to acquire at least two signals of the ultrasonic signal, the electromyographic signal and the audio signal from the same organism and synchronously display the acquired signals on a display device; the synchronization is that all the signals are projected on the display device in real time, and the time difference between all the signals projected on the display device is equal to the acquisition time difference of all the signals.

2. The method for processing the collected multiple dynamic parameters of the machine body according to claim 1, wherein the synchronous display specifically comprises:

s1, acquiring the time length required by the respective processing of the ultrasonic signal, the electromyographic signal and the audio signal; obtaining the maximum duration, and then comparing the duration of the rest signal processing with the maximum duration to obtain the comparison duration; the time length required by the processing is the time required from the acquisition of the signals to the display of the signals on the display device.

S2, immediately displaying the signal with the time length required by processing as the maximum time length after the signal processing is finished;

and (4) finishing processing the rest signals, and immediately displaying after the contrast time.

3. The method for collecting processing of multiple dynamic parameters of human body according to claim 1, wherein said ultrasound signal is heart M ultrasound image signal; the electromyographic signal is an electrocardio QRS wave signal, and the audio signal is a heart sound.

4. The method of claim 3, wherein said ECG QRS wave signal has a maximum duration; the comparison duration between the duration required by processing the electrocardio QRS wave signals and the duration of the rest signal processing is specifically as follows: 0.125S.

5. A method for obtaining the cardiac ejection fraction by utilizing multi-dynamic parameter processing is characterized in that,

the method comprises the steps that electrocardio QRS waves which are continuously collected from the same organism in the same time period and M ultrasonic images of heart form changes which synchronously occur with electrocardio are distributed on the same time axis and aligned to the same initial time point;

in the M ultrasonic image, obtaining a first longitudinal pixel array of the M ultrasonic image at a time point after a first specific time length after one of Q wave, R wave and S wave in the electrocardio QRS wave is generated, and finding out the minimum value of the distance between the inner membrane of the front wall of the left ventricle and the inner membrane of the rear wall of the left ventricle in the first longitudinal pixel array;

in the M ultrasonic image, obtaining a second longitudinal pixel array of the M ultrasonic image at a time point after a second specific time length after one of Q wave, R wave and S wave in the electrocardio QRS wave is generated, and finding out the maximum value of the distance between the inner membrane of the front wall of the left ventricle and the inner membrane of the rear wall of the left ventricle in the second longitudinal pixel array;

and calculating the cardiac ejection fraction according to the minimum value and the maximum value.

6. The method for obtaining cardiac ejection fraction by multi-dynamic parameter processing according to claim 5, wherein the alignment is performed to the same starting time point, specifically, the method according to any one of claims 1 to 4 is used to synchronously display the collected ultrasonic signals and myoelectric signals on a display device; the display time difference of the ultrasonic signals and the myoelectric signals projected to the display device is equal to the acquisition time difference of the acquired signals.

7. The method of claim 5, wherein the cardiac QRS wave and the M-ultrasonic image are acquired by a device having both functions of acquiring cardiac QRS wave and M-ultrasonic image;

the display device is provided with a continuous time axis and a real-time state axis.

8. The method of claim 5, wherein the first specific duration and the second specific duration are calculated by: analyzing a plurality of M ultrasonic images subjected to binarization processing, marking the time of the minimum value of the interval between the inner membrane of the front wall of the left ventricle and the inner membrane of the rear wall of the left ventricle, and calculating the time difference between the time of the occurrence of one of Q wave, R wave and S wave and the time of the occurrence of the minimum value to obtain a first specific time length;

and calculating the time difference between the time of occurrence of one of the Q wave, the R wave and the S wave and the time of occurrence of the maximum value to obtain a second specific time length.

9. The method of claim 5, wherein after obtaining the minimum and maximum values of the distance between the anterior intima and the posterior intima of the left ventricle, the cardiac ejection fraction is calculated by the following calculation formula EF ═ EDV-ES (100%), where EF is the cardiac ejection fraction, and EDV is the maximum volume of the left ventricle of the heart at the maximum distance between the anterior and posterior intima of the left ventricle; minimum volume of the left ventricle of the heart at minimum distance of the anterior-posterior intima of the left ventricle of the ES heart;

wherein, the maximum volume of the left ventricle of the heart is calculated by the minimum distance between the front wall and the back wall of the left ventricle of the heart; and calculating the maximum volume of the left ventricle of the heart according to the maximum distance between the front wall and the back wall of the inner membrane of the left ventricle of the heart.

10. The method of obtaining cardiac ejection fraction using multi-dynamic parameter processing as claimed in claim 5, wherein the M ultrasound image is formed by: the horizontal pixel rows parallel to the time axis and the vertical pixel rows perpendicular to the time axis.

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