Processing methods of multiple dynamic parameters of the body and their application in ejection fraction

Abstract

The method for processing multiple dynamic parameters of the body and its application in ejection fraction, through the equipment with simultaneous acquisition of electromyographic signal, sound signal and M-ultrasound image, collects electromyographic, sound and M-ultrasound signals, and comprehensively analyzes these signals to obtain accurate human body movement state. In particular, by simultaneously monitoring the electrocardiogram signal, cardiac ultrasound image and heartbeat sound, and performing time alignment on the electrocardiogram signal, cardiac ultrasound image and heartbeat sound signal processing, the minimum spacing and maximum spacing between the front and rear walls of the left ventricle of the heart can be more accurately found in the cardiac ultrasound image, and the minimum volume of the contraction of the left ventricle of the heart and the maximum volume of the left ventricle of the heart when it is expanded can be obtained by calculation to calculate the ejection fraction of the heart.

Description

Technical Field

[0001] The invention relates to a medical device and a signal processing method and application thereof. Background Art

[0002] When the human body (including other animal bodies) moves, it will generate muscle electricity under the command of the brain, hereinafter referred to as electromyography. Electromyography drives the human body to move. Electrocardiography is also a kind of electromyography, which makes the heart beat.

[0003] Existing technology can effectively monitor the generation of myoelectricity and the amount of electricity. The intensity of the myoelectric signal is recorded. For example, an electrocardiogram can tell the waveform of the electrocardiogram.

[0004] At the same time, through ultrasound images, we can also know the shape and position of human muscles. When the body moves, it also produces sounds, such as the sound of bones touching each other, the sound of heart beating, etc. And when the human body moves, the above-mentioned myoelectricity generation, muscle shape changes, and sound generation are all produced in coordination and in response. For example, when the heart beats, electrocardiograms are generated first, which drives the heart to beat, and then the heart collides to produce sound (heartbeat sound).

[0005] Existing medical equipment can monitor electromyography, morphological images, and sounds separately, but there is currently no technology to monitor all three at the same time. For example, existing equipment can use morphological images to assist in the analysis of ejection fraction.

[0006] Ejection fraction refers to the percentage of the ventricular end-diastolic volume (i.e. cardiac preload), with a normal value of 50-70%. It can be checked by cardiac ultrasound and is one of the important indicators for determining the type of heart failure. Ventricular ejection fraction refers to the percentage of the ventricular end-diastolic volume (i.e. cardiac preload), with a normal value of 50-70%. It can be checked by cardiac ultrasound and is one of the important indicators for determining the type of heart failure.

[0007] Ejection fraction is a volume ratio indicator that reflects the ventricular ejection function from a volume perspective.

[0008] However, since only image information is provided to medical personnel, the above-mentioned ejection fraction analysis requires medical personnel to obtain the ejection fraction through image information, then measure by marking their own hand movements on the image, and then calculate, which is not convenient for quickly providing medical solutions.

[0009] Therefore, in order to quickly obtain relevant information about the human body's status, to better assist medical personnel, and to ensure the accuracy of medical equipment's monitoring of the human body, it is necessary for us to make full use of the electromyography, morphological images, and sound information generated and monitored during human movement. Summary of the invention

[0010] In order to solve the above problems, the present invention provides a method for collecting and processing multiple dynamic parameters of a body and an application of the method in analyzing cardiac ejection fraction.

[0011] Among them, a method for collecting multiple dynamic parameters of an organism is provided:

[0012] A collection device having at least two of the three collection functions of ultrasonic signal collection, electromyographic signal collection and audio signal collection is used to collect at least two of the ultrasonic signals, electromyographic signals and audio signals from the same body, and the collected signals are synchronously displayed on a display device; the synchronization is that each signal is projected onto the display device in real time, and the time difference between each signal projected onto the display device is equal to the collection time difference of each signal.

[0013] The synchronous display described herein is specifically performed as follows:

[0014] S1: First obtain the time required for processing the ultrasonic signal, the electromyographic signal, and the audio signal respectively; obtain the maximum time among them, and then compare the processing time of the remaining signals with the maximum time to obtain the comparison time; the processing time required is the time required from the acquisition time to the signal acquisition time until the signal is displayed on the display device.

[0015] S2: After the signal processing time required is the maximum time, it is immediately displayed;

[0016] The remaining signals will be displayed immediately after processing is completed and the comparison time has passed.

[0017] The method for collecting and processing multiple dynamic parameters of a body as described above is further described as follows: the ultrasonic 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.

[0018] The method for collecting and processing multiple dynamic parameters of the body as described above is further described as follows: the ECG QRS wave signal has a maximum duration; the duration required for processing the ECG QRS wave signal and the comparison duration between the durations of processing other signals are specifically: 0.125S.

[0019] A method for obtaining cardiac ejection fraction using multi-dynamic parameter processing is provided:

[0020] The ECG QRS waves collected continuously from the same body in the same time period, as well as the M ultrasound images of the heart morphological changes that occur synchronously with the ECG, are distributed on the same time axis and aligned to the same starting time point;

[0021] 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 electrocardiogram QRS wave is generated, a first longitudinal pixel column of the M ultrasound image is obtained, and a minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the first longitudinal pixel column;

[0022] 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 electrocardiogram QRS wave is generated, a second longitudinal pixel column of the M ultrasound image is obtained, and the maximum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the second longitudinal pixel column;

[0023] The cardiac ejection fraction is calculated using the minimum and maximum values.

[0024] The method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing as described above is further described as follows: the alignment to the same starting time point is specifically, using the method described in any one of claims 1 to 4 above, to synchronously display the collected ultrasound signal and electromyographic signal on a display device; making the display time difference of the ultrasound signal and electromyographic signal projected on the display device in real time equal to the acquisition time difference of the collected signal.

[0025] The method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing as described above is further described as follows: the electrocardiogram QRS wave and the M ultrasound image are collected by a device having the function of collecting both the electrocardiogram QRS wave and the M ultrasound image;

[0026] A duration axis and a real-time status axis are provided on the display device.

[0027] The method for obtaining the cardiac ejection fraction by using the multi-dynamic parameter processing as described above is further described as follows: the calculation method of the first specific time length and the second specific time length is: analyzing a plurality of binarized M ultrasound images, marking the time when the minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium appears, and calculating 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 minimum value appears, to obtain the first specific time length;

[0028] The time difference between the time when one of the Q wave, R wave, and S wave appears and the time when the maximum value appears is calculated to obtain the second specific time length.

[0029] The method for obtaining the cardiac ejection fraction by using the multi-dynamic parameter processing as described above is further described as follows: after obtaining the minimum and maximum values ​​of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium, the cardiac ejection fraction is calculated by the following calculation formula EF=(EDV-ES)*100%, wherein EF is the cardiac ejection fraction, EDV is the maximum volume of the left ventricle when the distance between the anterior and posterior wall endocardium of the left ventricle is the maximum, and ES is the minimum volume of the left ventricle when the distance between the anterior and posterior wall endocardium of the left ventricle is the minimum;

[0030] Among them, the maximum volume of the left ventricle of the heart is calculated by the minimum distance between the anterior and posterior endocardium of the left ventricle of the heart; the maximum volume of the left ventricle of the heart is calculated by the maximum distance between the anterior and posterior endocardium of the left ventricle of the heart.

[0031] The method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing as described above 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.

[0032] Beneficial effects of the present invention:

[0033] The present invention can accurately obtain the maximum distance and the minimum distance between the front and rear walls of the left ventricle during the heart beating process, thereby automatically obtaining the ejection fraction of the heart.

[0034] By continuously obtaining the maximum distance between the front and rear walls of the left ventricle, the average value and current value of the heart's ejection fraction as well as the maximum and minimum values ​​of the heart's ejection fraction can be dynamically known. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 This is the structural diagram of the multifunctional acquisition device in Example 1, which realizes the same device to respectively collect ultrasound image information, heartbeat sound, and electrocardiogram.

[0036] Figure 2 This is the schematic diagram of the control principle of the multifunctional acquisition device introduced in Example 1 and Example 2.

[0037] Figure 3 This is the structural diagram of the multifunctional acquisition device in Example 2, which realizes the same device to respectively collect ultrasound image information, heartbeat sound, and electrocardiogram information.

[0038] Figure 4 This is a schematic diagram of the control principle of the acquisition device for acquiring and processing ultrasonic image information in Example 3.

[0039] Figure 5 This is a structural diagram of the acquisition device for acquiring and processing ultrasonic image information in Example 3.

[0040] Figure 6 It is a schematic diagram of a specific method for synchronous display of the present invention. DETAILED DESCRIPTION

[0041] The device and method of the present invention are mainly used for human body, and the organism of the present invention mainly refers to human body. Of course, it can also be applied to other animals besides human body. The "human body" mentioned below is a reference according to the usage habits.

[0042] The present invention is preferably implemented in the form of software code, and the steps of the present invention are edited into software code and installed in a computer with computing functions, for example, in the form of software code, installed in a smart phone or tablet computer, which has the function of recognizing and reading M-mode ultrasound cardiac images.

[0043] Those skilled in the art will appreciate that the exemplary algorithm steps described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or in a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of the present invention.

[0044] The implementation of the present invention is completed by installing a corresponding computer program in a computer with relevant hardware. The computer program can be stored in a computer-readable storage medium. When the computer program is executed by a processor, it can implement various required steps. Among them, the computer program includes computer program code, and the computer program code can be in source code form, object code form, executable file or some intermediate form. The computer-readable medium may include: any entity or device capable of carrying the computer program code, recording medium, USB flash drive, mobile hard disk, disk, optical disk, computer memory, read-only memory (ROM, Read-Only Memory), random access memory (RAM, Random Access Memory), electric carrier signal, telecommunication signal and software distribution medium. It should be noted that the content contained in the computer-readable medium can 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, computer-readable media do not include electric carrier signals and telecommunication signals.

[0045] 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 device, power supply, chassis and related software. The related software refers to the software that can project the M-mode echocardiography (M-echo) image onto the display screen. Of course, the M-mode echocardiography can also be displayed in the form of images, but the computer background can process and calculate the image by itself, and finally only the calculation result is presented on the display.

[0046] Example 1:

[0047] The body information of the human body is collected by a multifunctional collection device provided with a probe for transmitting and collecting ultrasonic signals, a sound collection head, and electromyographic collection electrodes. Ultrasonic image information, sound information, and electromyographic information are collected respectively. Specifically, the heart beat information of the human body is collected by a multifunctional collection device provided with a probe for transmitting and collecting ultrasonic signals, a sound collection head, and electrocardiographic collection electrodes, and the heart ultrasonic image information, heartbeat sound, and electrocardiographic information are collected respectively.

[0048] With reference to the following device, the same device can collect ultrasound image information, heartbeat sound, and electrocardiogram.

[0049] refer to Figure 1 This embodiment provides a multifunctional stethoscope, including a device body 5, on which a single-element ultrasound probe 2 is provided, on which an electrocardiogram sensor is provided, and a charging interface is provided at the lower end of the device body 5; the device body 5 is provided with a control circuit board for controlling the operation of the device body 5 and interacting with a mobile client terminal to transmit data, and a power module for supplying power to the entire stethoscope body, and the charging interfaces are respectively connected to the power modules, and the power modules include rechargeable batteries.

[0050] The single-element ultrasound probe 2 and the electrocardiogram sensor are integrated into a device body 5, so that the probe can realize the functions of ultrasound and electrocardiogram.

[0051] A microphone 4 is provided on the device body 5, and the ECG sensor is a three-lead ECG electrode, which is composed of three ECG electrodes 3 evenly arranged on the front end surface of the device body 5. The single-element ultrasonic probe 2 is located in the middle of the front end surface of the device body 5, and the microphone 4 is located on one side of the front end surface of the device body 5.

[0052] The detection functions of heart sounds, fetal heart monitoring, breathing sounds and bowel sounds can be realized by the pickup 4. In actual operation, the sound output of the stethoscope can be through the speaker of the mobile client terminal, or through the Bluetooth headset connected to the stethoscope, and the waveform is displayed on the display of the mobile client terminal.

[0053] The device body 5 includes an upper shell 6, a main shell 7 and a lower shell connected in sequence from top to bottom. The control circuit board is located inside the main shell 7. A protective cover 1 covering the upper end of the device body 5 is provided. A latching tooth 601 capable of clamping the inner side of the protective cover 1 is provided on the surface of the upper shell 6. A hollow cover 401 is screwed on the upper shell 6. A diaphragm sheet 402 located above the pickup 4 is provided on the inner side of the hollow cover 401.

[0054] The structure of the device control circuit board, the ECG sensor, the single-element ultrasound probe 2, and the microphone 4 is shown in FIG. Figure 2 .

[0055] The outer shell 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. The protective cover 1 at the upper end of the device body 5 covers the upper shell 6, which can prevent the pickup 4, ECG electrode 3 and diaphragm 402 from being contaminated by foreign objects when not in use.

[0056] The control circuit board is provided with a main control chip, which is used to process the detection data of the single-element ultrasonic probe 2, the electrocardiogram sensor and the microphone 4, and convert it into readable numerical values ​​and curve data; the data transmission module 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 to the main control chip.

[0057] The single-element ultrasonic probe 2 is connected to the main control chip through the ultrasonic channel, the microphone 4 and the electrocardiogram sensor are connected to the main control chip through the composite channel, and the client terminal mobile client terminal is connected to the main control chip through the data transmission module.

[0058] In this embodiment, the multifunctional stethoscope can simultaneously use a single-element ultrasonic probe to collect ultrasonic image information, a microphone 4 to collect heartbeat sound, and an electrocardiogram sensor to collect electrocardiogram information. At the same time, the three collection heads collect the above information at the same time and at substantially the same position (e.g., at the heart of the left chest of the human body), so the collected information is real-time and is for the same body.

[0059] Example 2:

[0060] With reference to the device of the following Chinese patent CN209695222U, the same device can collect ultrasound image information, heartbeat sound, and electrocardiogram.

[0061] Its structure includes reference Figure 2 , Figure 3 :

[0062] 1. Single-element ultrasound probe, used to detect the heart's ejection fraction LVEF. Cardiopulmonary function probe, including an ECG sensor for detecting heart rate ECG. The ECG sensor is a three-lead ECG electrode, and the respiratory rate sensor is a capacitive respiratory sensor. A respiratory rate sensor for detecting respiratory rate RR. The single-element ultrasound probe is connected to the main control chip through an ultrasonic channel. The ECG sensor and respiratory rate sensor on the cardiopulmonary function probe are connected to the main control chip through a composite channel. The client terminal mobile client terminal is connected to the main control chip through a data transmission module. The single-element ultrasound probe and the cardiopulmonary function probe are both located on the front end of the stethoscope body, and the ECG sensor and respiratory rate sensor are fixed side by side as a whole. The single-element ultrasound probe includes:

[0063] (1) Ultrasonic transducer, a single-element ultrasonic probe includes a circuit 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 for receiving echo signals from the ultrasonic transducer; (4) an interface circuit for connecting to the main control chip in the stethoscope body through an ultrasonic channel; (5) a controller for controlling the operation of the transmitting circuit, detecting whether there is an echo signal in the receiving circuit, and storing the echo signal. The controller includes a transmitting control module, a data storage module, a receiving control module, and an interface control module. The transmitting control module is connected to the transmitting circuit through a transmitting control bus, the data storage module is connected to the receiving circuit, the receiving circuit is connected to the receiving control module through a receiving control bus, and the interface control module is connected to the interface circuit. (6) And a transmitting control bus, a receiving switch circuit, and a receiving control bus.

[0064] 2. Main control chip, reference Figure 2 , used to process the detection data of single-element ultrasound probe, ECG sensor and respiratory rate sensor, and convert them into readable numerical values ​​and curve data.

[0065] 3. Data transmission module, used to transmit the data generated by the main control chip to the mobile client terminal.

[0066] 4. Power module, used to supply power to the entire stethoscope body.

[0067] 5. Power switch, used to turn on or off the power supply of the power module.

[0068] 6. A flash memory chip FLASH is used to store all the data generated by the main control chip. The flash memory chip FLASH is connected to the main control chip.

[0069] 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.

[0070] During the implementation process, the front end of the stethoscope body is pressed against the patient's lung and heart parts that need to be auscultated, so that the single-element ultrasonic probe, electrocardiogram sensor and respiratory rate sensor on the front end of the stethoscope body are in contact with the surface of the auscultation part, and the main control chip sends electrical signals for detection to the single-element probe, electrocardiogram sensor and respiratory rate sensor respectively, and the single-element probe, electrocardiogram sensor and respiratory rate sensor detect the body parts and send back the detection data to the main control chip, and the main control chip processes the detection data sent back by the single-element probe, electrocardiogram 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 convert the continuously obtained specific values ​​into curves. 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, and the doctor can view the specific values ​​of respiratory rate RR, heart rate ECG and heart ejection fraction LVEF in real time on the mobile client. 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, which can prevent the stethoscope body from losing detection data when the power module is accidentally powered off.

[0071] When using the device of CN209695222U, the respiratory rate sensor needs to be changed to the microphone 4 in Example 1 to realize the heartbeat sound collection function required by the present invention.

[0072] In this embodiment, the multifunctional stethoscope can simultaneously use a single-element ultrasonic probe to collect ultrasonic image information, a microphone to collect heartbeat sounds, and an electrocardiogram sensor to collect electrocardiogram information. At the same time, the three collection heads collect the above information at the same time and at basically the same position (for example, at the heart of the left chest of the human body). Therefore, the collected information is real-time and is for the same body.

[0073] Example 3:

[0074] In the above examples 1 and 2, both need to process and collect ultrasonic image information. You can refer to the device of the following Chinese patent CN209751086U, which can collect and process ultrasonic image information. Figure 4 , Figure 5 .

[0075] This embodiment includes an ultrasonic transducer for emitting a scanning beam, a digital control processing chip for controlling the ultrasonic transducer to emit a scanning beam and collect echo signals, a portable control terminal for issuing control instructions to the digital control processing chip and viewing scanned images, as well as a transmit-receive multiplexing circuit, a transmit-receive switching circuit, a transmitting circuit, a receiving circuit, a USB interface circuit, a low power module and an ultrasonic instrument housing.

[0076] The transmitting-receiving switching circuit, the transmitting-receiving multiplexing circuit and the ultrasonic transducer are connected in series in sequence, the transmitting circuit and the receiving circuit are respectively connected to the transmitting-receiving switching circuit, the ultrasonic transducer, the digital control processing chip, the transmitting-receiving multiplexing circuit, the transmitting-receiving switching circuit, the transmitting circuit, the receiving circuit and the USB interface circuit are all encapsulated in an ultrasonic instrument housing, the ultrasonic transducer is located at the front end of the ultrasonic instrument housing, the front end surface of the ultrasonic instrument housing is a coupling plane, and the USB interface circuit is located at the rear end of the ultrasonic instrument housing.

[0077] The low power module is provided with:

[0078] 1. A digital power supply is used to provide adaptive electric energy 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 for protecting its voltage stability. The digital control processing chip, the transmitting and receiving switching circuit, the transmitting circuit and the transmitting and receiving multiplexing circuit are respectively connected to the digital power supply;

[0079] 2. An analog power supply, which is used to provide adaptive electric energy for the transmitting and receiving multiplexing circuit and the receiving circuit. The analog power supply is provided with a linear voltage regulator for protecting its voltage stability. The transmitting and receiving multiplexing circuit and the receiving circuit are respectively connected to the analog power supply;

[0080] 3. An adjustable high-voltage DC converter, used to provide an adaptive high voltage for the transmitting circuit, the transmitting circuit is connected to the adjustable high-voltage DC converter;

[0081] 4. An 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 are respectively connected to the USB interface circuit through the overcurrent protector.

[0082] The front end of the ultrasonic instrument housing is a coupling plane, and the digital control processing chip is provided with:

[0083] 1. A transmitting beam control module is used to control the transmitting and receiving switching circuit to open the transmitting circuit channel and close the receiving circuit channel, and to control the ultrasonic transducer to emit a scanning beam. The transmitting beam control module is connected to the transmitting circuit through a transmitting control bus.

[0084] 2. A receiving control module is used to detect whether there is an echo signal in the transmit-receive multiplexing circuit, and to control the transmit-receive switching circuit to open the receiving circuit channel and close the transmitting circuit channel. The transmit-receive switching circuit and the transmit-receive multiplexing circuit are respectively connected to the receiving control module through a receiving control bus.

[0085] 3. A data processing module, used for receiving and collecting echo signals, the data processing module is connected to the receiving circuit;

[0086] 4. An interface control module is used to control the alternating operation of the transmitting beam control module and the receiving control module, and to send the echo signal collected by the data processing module to the portable control terminal. The transmitting beam control module and the receiving control module are respectively connected to the interface control module, and the interface control module is connected to the portable control terminal through a USB interface circuit.

[0087] The digital control processing chip is an FPGA programmable digital gate array processing chip. The portable control terminal is a mobile phone terminal.

[0088] During the implementation process, the portable control terminal powers the ultrasound instrument through the USB interface circuit, the digital power supply can provide adaptive power for the digital control processing chip, the transmit-receive switching circuit, the transmit circuit and the transmit-receive multiplexing circuit, the analog power supply can provide adaptive power for the transmit-receive multiplexing circuit and the receive circuit, the adjustable high-voltage DC converter provides an adaptive high voltage for the transmit circuit, and both the digital power supply and the analog power supply are provided with a linear voltage regulator for protecting their voltage stability.

[0089] The portable control terminal sends a command to the ultrasound instrument to perform scanning. The digital control processing chip controls the transmitting and receiving switching circuit to open the transmitting circuit channel and close the receiving circuit channel through the transmitting circuit, thereby controlling the ultrasonic transducer to emit a scanning beam, and the ultrasonic transducer sends the acquired echo signal to the transmitting and receiving 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. The echo signal is sent to the digital control processing chip through the transmitting and receiving switching circuit and the receiving circuit in turn. The digital control processing chip collects the echo signal, and the collected echo signal is sent to the portable control terminal through the USB interface circuit in turn. The portable control terminal processes the collected echo signal to obtain an ultrasonic image and displays it.

[0090] The voltage of the portable control terminal for powering 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 low power module to no more than 500mA. The digital power supply can output two types of adaptive power supplies: 3.3V, 300mA and 1.2V, 460mA. The analog power supply can output an adaptive power supply of 3.3V, 400mA.

[0091] As can be seen from the foregoing, ultrasound apparatuses are all powered by portable control terminals. The low power module in the ultrasound apparatus can convert the electrical energy input by the portable control terminal into compatible electrical energy, thus meeting the miniaturization requirements of the ultrasound apparatus.

[0092] According to the needs of scanning, a command for scanning is sent to the ultrasound instrument 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 emit a scanning beam, and the ultrasonic transducer sends the acquired echo signal to the transmitting and receiving multiplexing 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. The echo signal is sent to the data processing module in turn through the transmitting and receiving switching circuit and the receiving circuit. The data processing module collects the echo signal, and the collected echo signal is sent to the portable control terminal in turn through the interface control module and the USB interface circuit. The portable control terminal processes the collected echo signal to obtain an ultrasonic image and displays it.

[0093] After the portable control terminal sends a scanning instruction to the ultrasound instrument, the transmitting beam control module controls the ultrasonic transducer to send a scanning beam, and the interface control module controls the transmitting beam control module and the receiving control module to operate alternately, so that the ultrasound instrument can realize the ultrasonic scanning function.

[0094] Example 4:

[0095] The method of obtaining cardiac ejection fraction using multi-dynamic parameter processing is as follows:

[0096] 1. Use the acquisition device provided in Examples 1, 2, and 3, which has both ultrasonic signal acquisition function and electromyographic signal acquisition function, to acquire ultrasonic signals and electromyographic signals from the same body, and synchronously display the acquired signals on a display device.

[0097] The same organism here refers to the human body or the human heart. Ultrasonic signal information is M-wave echocardiogram, and electromyographic information is electrocardiographic signal, which is shown in electrocardiographic QRS wave electrocardiogram. Since the beating of the heart is the contraction movement of the heart stimulated by electrocardiogram, therefore, one electrocardiographic information corresponds to one heart cycle beating, and therefore, the electrocardiographic signal and the heart cycle beating are synchronized. The corresponding synchronization here does not mean to be carried out at the same time, but to follow accordingly.

[0098] 2. The synchronous display described in step 1 above is as follows: the collected ECG QRS wave and the M ultrasound image of the heart morphological changes that occur synchronously with the ECG are distributed on the same time axis and aligned to the same starting time point. The collected ultrasound signal and electromyographic signal are synchronously displayed on the display device; the display time difference of the ultrasound signal and electromyographic signal projected on the display device in real time is equal to the acquisition time difference of the collected signal.

[0099] The details are as follows: Since the acquisition device is a collection device with both ultrasonic signal acquisition function and electromyographic signal acquisition function on the same body, and is displayed on the same display device (display), the acquisition part of the acquisition device (reference Figure 1 For example, a single-element ultrasonic probe 2, a microphone 4, and an ECG sensor / ECG electrode 3) obtain the above-mentioned signal. Since the human heartbeat is stimulated by the ECG, within a heartbeat cycle (from the early stage of cardiac contraction to the end of cardiac diastole), an ECG signal is generated first, and then the heart morphology changes. Therefore, there is a time difference between the ECG signal collected by the collection part of the collection device and the heart morphology change (because there is ECG first, and then there is heartbeat / heart morphology change). This time difference must be accurately reflected on the display device. Therefore, this time difference must be calculated by a method and reflected accordingly, so that the display time difference of the ultrasonic signal and the electromyographic signal projected on the display device in real time is equal to the collection time difference of the collected signal.

[0100] 3. In the M ultrasound image, at a time point after a first specific time after one of the Q wave, R wave, and S wave in the electrocardiogram QRS wave is generated, the first longitudinal pixel column of the M ultrasound image is obtained, and the minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the first longitudinal pixel column. In the M ultrasound image, at a time point after a second specific time after one of the Q wave, R wave, and S wave in the electrocardiogram QRS wave is generated, the first longitudinal pixel column of the M ultrasound image is obtained, and the maximum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the second longitudinal pixel column.

[0101] The calculation method of the first specific duration and the second specific duration is as follows: analyze a number of binarized M ultrasound images, mark the time when the minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium 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, and obtain the first specific duration; 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 maximum value appears, and obtain the second specific duration. Here, it should be taken into account that different organisms may have different ECG cycles, and that each wavelength is slightly different within a cycle. ECG has a QRS wave group, which is composed of Q wave, R wave, and S wave. For example, the heart condition of a certain organism is as follows: when the ECG R wave occurs, after the first specific duration of 0.40s, the heart enters the end of the systolic period and reaches the minimum volume, which is the rapid ejection period; after the R wave occurs and after the second specific duration of 0.80s, the heart enters the end of the diastolic period and reaches the maximum volume. Here, the time of occurrence 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 is the largest and is the easiest to identify. Of course, other Q waves, S waves, T waves, and P waves can also be used as the starting point of time. These peaks are all in one heartbeat cycle, and each heartbeat cycle has these waves. Therefore, it does not matter which peak is used as the starting point. When the R wave is used as the starting point: after the first specific time of 0.40s, the heart enters the end of the systolic period and reaches the minimum volume; and after the second specific time of 0.80s, the heart enters the end of the diastolic period and reaches the maximum volume; when the Q wave is used as the starting point: after the Q wave occurs, after the first specific time of 0.36s, the heart enters the end of the systolic period and reaches the minimum volume; and after the second specific time of 0.76s, the heart enters the end of the diastolic period and reaches the maximum volume. The images of the minimum volume and the maximum volume will be captured by ultrasound to produce an M-type echocardiogram.

[0102] Through the minimum and maximum values, the following calculation formula is used:

[0103] EF=(EDV-ES)*100%Calculate the cardiac ejection fraction, where EF is the cardiac ejection fraction, EDV is the maximum volume of the left ventricle when the distance between the anterior and posterior endocardium of the left ventricle is the maximum; ES is the minimum volume of the left ventricle when the distance between the anterior and posterior endocardium of the left ventricle is the minimum;

[0104] Among them, the maximum volume of the left ventricle of the heart is calculated by the minimum distance between the anterior and posterior endocardium of the left ventricle of the heart; the maximum volume of the left ventricle of the heart is calculated by the maximum distance between the anterior and posterior endocardium of the left ventricle of the heart.

[0105] The M ultrasonic image of the present invention: The M ultrasonic 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. The first vertical pixel column and the first vertical pixel column are both one of many vertical pixel columns.

[0106] On this basis, in order to find the minimum and maximum values ​​of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium in a frame of M ultrasound image, we can use the relationship between the ECG QRS complex time and the end of the heart's systole and the end of the heart's diastole.

[0107] When using this relationship, it is satisfied that: each signal is projected onto the display device in real time, and the time difference between each signal projected onto the display device is equal to the acquisition time difference of each signal; specifically, the ECG wave group corresponds to one frame M of ultrasound image, and the time difference between the ECG and ultrasound images projected onto the display device is equal to the acquisition time difference between the ECG signal and the ultrasound signal transmitted to the acquisition head. For example: the ECG R wave signal is generated from the body and is collected by the electromyography acquisition electrode in Example 1 at the 0th second, and when the R wave signal is generated from the body, the heart enters the end of the systolic period after the first specific time length of 0.40 seconds, that is, the single-element ultrasound probe collects the image of the heart entering the end of the systolic period in 0.40 seconds, so there is a 0.40s acquisition time difference between the time when the ultrasound image and the time when the R wave signal are collected, that is, the acquisition time difference is 0.40 seconds. It takes 0.5 seconds from the time the electromyography electrode collects the R wave signal to the time it is projected on the display, and it only takes 0.37 seconds from the time the single-element ultrasound probe collects the heart image to the time the image is projected on the display. If the ECG R wave signal and the ultrasound image signal are directly projected, the heart will enter the end of the systolic period 0.37 seconds after the R wave signal seen on the display is generated. 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 display to avoid calculation errors.

[0108] After processing the acquisition time difference and display time difference, we can strictly correspond the ECG QRS wave to the ultrasound image to find the heart entering the end of diastole (maximum volume, or maximum value). For example, after the R wave occurs for the first specific duration of 0.40, the corresponding column of pixels on the M ultrasound image (the first vertical pixel column) is the end of the heart's contraction period, reaching the minimum volume and minimum value. After the R wave occurs for the first specific duration of 0.80s, the corresponding column of pixels on the M ultrasound image (the second vertical pixel column) is the end of the heart's diastole, that is, the maximum volume and maximum value.

[0109] Example 5:

[0110] As mentioned in Example 4: reflect the actual time difference between the ECG and the image on the body on the display to avoid calculation errors. The method is as follows:

[0111] By using the acquisition device provided in Examples 1, 2, and 3, which has at least two of the three acquisition functions of ultrasound signal acquisition, electromyography signal acquisition, and audio signal acquisition, at least two of the ultrasound signal, electromyography signal, and audio signal are acquired from the same body, and the acquired signals are synchronously displayed on a display device.

[0112] The display device is provided with a duration axis and a real-time state axis. The time axis referred to in the present invention is a horizontal axis projected onto the display device; the real-time state axis can also be called a change state axis, which is a vertical axis projected onto the display device. The time axis and the change state axis are reflected on the display device, and the relationship between the change state of the signal and time can be seen.

[0113] The synchronization display here means that each signal is projected onto the display device in real time, and the time difference between each signal projected onto the display device is equal to the acquisition time difference of each signal.

[0114] Since at least one of the collected ultrasonic signals, electromyographic signals, and audio signals is affected by the processing circuit, causing the display time to lag behind the other signals; therefore, the time when the signal affected by the processing circuit is put on the display device lags behind the other signals. Specifically, the circuit reasons of various electronic components and the reasons why the software processes the collected information cause a time difference between signal collection and signal presentation, and different information sources have different time differences. For example, the sound of the heartbeat can be processed very quickly through the circuit and software, and the ultrasonic image can also be faster, but the electrocardiogram signal is relatively slow from collection to presentation, about 0.125S slower. Therefore, in order to make the presented information consistent, the presented information needs to be adjusted. This is the so-called "synchronization".

[0115] The delay time caused 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. It is better to test the software and circuit in practice to get the time required for the software and circuit to process the signal. We record this time. The ultrasonic signal, heartbeat sound signal and ECG signal have the same processing steps and different processing times. We record the processing time required for the ultrasonic signal, heartbeat sound, signal and ECG signal, and get the longest time required for ECG signal processing. Therefore, when we present the three signals, after the processing of the heartbeat sound ultrasound signal is completed, we do not present it immediately, but wait for the ECG signal to be processed. 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 ultrasound image signal are processed, wait for the above delay difference, and then the sound signal and ultrasound signal can be presented; at the same time, the ECG signal is also processed and presented immediately; so that the presented ultrasound signal, ECG signal and sound signal are synchronized and aligned in time (i.e., acquisition state).

[0116] The specific method of synchronous display is as follows: Figure 6 :

[0117] S1: First obtain the time required for processing the ultrasonic signal, the electromyographic signal, and the audio signal, for example: the processing time of the ultrasonic signal is 0.5s, the electromyographic signal is 0.625s, and the audio signal is 0.5s; the maximum time is 0.625s for the electromyographic signal, and then the processing time of the remaining signals is compared with the maximum time, and the audio signal (or ultrasonic) 0.5s is subtracted from the maximum time 0.625 to obtain a comparison time of 0.125s; the time required for processing is the time required from the acquisition time of the signal to the time the signal is displayed on the display device, for example: the ECG R wave signal is generated from the body, is collected by the electromyographic acquisition electrode in Example 1 at the 0th second, and it takes 0.625s to be projected on the display.

[0118] S2: After the signal that takes the maximum processing time is processed, it is displayed immediately; after the processing of the remaining signals is completed and the comparison time has passed, they are displayed immediately. That is to say, after the ECG signal is processed, it is immediately displayed on the display, and the delay to the display is 0.625s. After the processing of the remaining signals is completed and the comparison time has passed 0.125s, they are immediately displayed, and the delay to the display is 0.625s. Therefore, the time difference (delay) to the display is equal. The time difference between the ECG and the image seen on the display is completed to be the real time difference.

[0119] The ultrasonic 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.

[0120] Example 6:

[0121] The method for calculating the minimum volume and the maximum volume of the heart through image pixels required in Example 4 can be referred to the following example.

[0122] When analyzing cardiac ejection fraction, it is necessary to know the minimum volume of the heart when the heart contracts and the maximum volume of the heart when the heart expands.

[0123] When using the device software for automatic recognition, since the device software cannot accurately identify the maximum and minimum volumes of the heart through ultrasound images, we inject the heartbeat sound and ECG waveform into the device software. After the device software obtains the ECG waveform (and heartbeat sound), it matches the continuously changing ECG waveform to the corresponding continuously changing ultrasound image to find the most appropriate cross-sectional shape of the distance between the front and back walls of the heart. For example:

[0124] At 0.04 seconds after the R wave of the electrocardiogram, it can correspond 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. That is, it can be clearly seen from the electrocardiogram that the minimum distance between the anterior and posterior walls of the heart must be in this section. Since this section has demarcated a very small range area, it is very easy to find the distance between the anterior and posterior walls in this very small range area through image recognition. There are many methods for image recognition: for example, the color block recognition method and device provided by CN201310125145.X disclosed in Chinese patent, by edge detection of the image to be recognized, extracting the contour of the color block in the image to be recognized to determine the shape of the color block, calculating the centroid coordinates of the color block according to the extracted contour of the color block to obtain the position of the color block, and selecting the color of a point in the color block to determine the color of the color block. Therefore, it can simultaneously recognize the shape, position and color of the color block, so that the information of the color block can be extracted more comprehensively. There are many methods for image recognition: for example, grayscale recognition.

[0125] There are many methods for image recognition, for example, some methods in a lung ultrasound image recognition method and system disclosed in Chinese patent CN202010409334.X can be adopted.

[0126] The normalized grayscale image is obtained by graying and normalizing the effective area image.

[0127] The following formula is used to grayscale the effective area image:

[0128] Gray=R*0.299+G*0.587+B*0.114, where R, G, and B are red, green, and blue components respectively.

[0129] The normalized grayscale images are scaled to a uniform size and form images to be recognized.

[0130] The normalized grayscale image is scaled to a uniform size, such as a 256*256 image to be tested. Preferably, bilinear interpolation, cubic spline interpolation, Lanczos interpolation or other methods are used for scaling.

[0131] By using the method of graphic recognition to find the minimum distance between the anterior and posterior walls of the left ventricle, we can get the volume of the heart when the heart contracts to the minimum. By using the same method to find the maximum distance between the anterior and posterior walls of the left ventricle, we can get the volume of the heart when the heart expands to the maximum. By substituting it into the ejection fraction analysis formula, we can get the ejection fraction.

[0132] Example 7:

[0133] The calculation method for calculating the minimum volume and the maximum volume of the heart through image pixels required in Examples 4 and 6 can refer to the following example.

[0134] 1. To calculate the minimum and maximum volumes of the heart, it is necessary to determine the border of the left ventricular septum and the border of the left ventricular posterior wall on echocardiography.

[0135] S1: Set the virtual centerline from the echocardiogram, which is approximately at the same distance from the upper border to the lower border;

[0136] From the virtual centerline, the echocardiograms were divided into: the upper echocardiogram with the image of the mitral valve and the endocardium of the left ventricular septum; and the lower echocardiogram with the endocardial border of the left ventricular posterior wall;

[0137] S2: The upper echocardiogram is processed to obtain the left ventricular septal border. The lower echocardiogram is processed to obtain the left ventricular posterior wall intima border.

[0138] 2. Among them, the method of processing the echocardiogram image to obtain the left ventricular septum boundary is:

[0139] S01: On an echocardiogram with images of the mitral valve and the left ventricular septum endothelium, determine the approximate extent of the adjacent areas of the left ventricular septum endothelium and the mitral valve by:

[0140] (1): On the echocardiogram, the continuous edge close to the mitral valve is used as 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 calculation starting line:

[0141] (2): At the calculation starting point line, go downward and count the percentage of black pixels in each pixel row parallel to the calculation starting point line;

[0142] (3): The first pixel row with at least 35% black pixels is the upper boundary of the approximate range;

[0143] (4): Obtain the lower edge of the approximate range as follows: (I) Continue to count the percentage of black pixels in each pixel row along the upper edge of the range of the mitral lobe pixel block domain downward. When the proportion of black pixels in the pixel row is the largest, the corresponding pixel row is the lower edge of the approximate range; (II) When multiple pixel rows are obtained that satisfy the above condition (I), the first pixel row that satisfies the above condition (I) and is closest to the upper edge of the range is the lower edge of the approximate range.

[0144] S02: Find the pixel block domain of the adjacent area of ​​the left ventricular septum endothelium and the mitral valve within the approximate range, by searching row by row from the upper range line to the lower range line within the approximate range, and satisfying at least the following search conditions: (I) In the same column of pixels, the pixel grayscale value increases from the upper range line to the lower range line for at least ten pixels; (II) The first range found with the above (I) feature is the pixel block domain of the adjacent area of ​​the left ventricular septum endothelium and the mitral valve. When the search conditions are met, within the found pixel block domain of the adjacent area of ​​the left ventricular septum endothelium and the mitral valve, only one of the following situations is allowed, and this situation is regarded as a noise point: (I) The grayscale value of no more than 2 pixels stops increasing compared with the previous pixel; (II) The grayscale value of 1 pixel decreases compared with the previous pixel.

[0145] S03: setting the grayscale value of the pixel block domain in the adjacent area to 0;

[0146] S04: Binarizing the echocardiogram including the adjacent region whose grayscale value of the pixel block domain is set to 0, to obtain a binary echocardiogram in which the adjacent region and the mitral valve region are excluded from the left ventricular septum endocardium.

[0147] S05: Delineate a region of interest on the binary echocardiogram, the region of interest includes the entire left ventricular septum endocardial boundary image; calculation method of the region of interest: on the echocardiogram, the continuous edge close to the mitral valve 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 in the following manner: (I) Continue to count the percentage of black pixels in each pixel row downward from the first boundary of the region of interest, 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 multiple pixel rows are obtained that meet the above condition (I), the first pixel row that meets the above condition (I) closest to the first boundary of the region of interest is the second boundary of the region of interest.

[0148] The area between the first boundary of the region of interest and the second boundary of the region of interest is the region of interest.

[0149] 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 septum endocardial boundary;

[0150] S07: Perform a closing operation on the obtained left ventricular septum endocardium boundary, and make the obtained left ventricular septum endocardium boundary a connected domain, that is, the final left ventricular septum endocardium boundary.

[0151] 3. Among them, the method of processing the echocardiogram below to obtain the left ventricular posterior wall intimal border is:

[0152] 1: Binarized ultrasound image; the continuous edge close to the mitral valve is calibrated as the upper boundary of the echocardiogram; the continuous edge on the opposite side of the upper boundary is the lower boundary of the echocardiogram;

[0153] On the echocardiogram, the distance between the upper boundary and the lower boundary is the virtual midline. Starting from the virtual midline and moving toward the lower boundary, the row position where the first white pixel appears in each column is counted in units of pixel columns.

[0154] 2: In the statistical data, if the row where the white pixel appears for the first time is more than 45 pixels away from the upper boundary, the column where it is located is the data error column;

[0155] 3: Use the following method to correct the data errors in the column:

[0156] (1) Merge adjacent columns with erroneous data into an error interval; (2) Set the row where the first white pixel point appears in the correct data column adjacent to the left side of the error interval as the first reference point, and set the row where the first white pixel point appears in the correct data column adjacent to the right side of the error interval as the second reference point; connect the first reference point and the second reference point with a straight line, and the straight line is the left ventricular posterior wall endocardial boundary of the error interval.

[0157] 4: Perform morphological opening operation to make the binarized echocardiogram smoother; then perform edge detection to obtain the intimal boundary of the left ventricular posterior wall.

[0158] 5: Perform a closing operation on the obtained left ventricular posterior wall intima boundary, and make the obtained left ventricular posterior wall intima boundary a connected domain, that is, the left ventricular posterior wall intima boundary.

[0159] After obtaining the minimum and maximum values ​​of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium, the cardiac ejection fraction is calculated by the following calculation 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 wall endocardium of the left ventricle is the maximum; ES is the minimum volume of the left ventricle when the distance between the anterior and posterior wall endocardium of the left ventricle is the minimum;

[0160] Among them, the maximum volume of the left ventricle of the heart is calculated by the minimum distance between the anterior and posterior endocardium of the left ventricle of the heart; the maximum volume of the left ventricle of the heart is calculated by the maximum distance between the anterior and posterior endocardium of the left ventricle of the heart.

[0161] The above are various embodiments for implementing the present invention. In the above embodiments, the description of each embodiment has its own emphasis. For the part that is not described or recorded in detail in a certain embodiment, please refer to the relevant description of other embodiments.

[0162] The embodiments described above are only used to illustrate the technical solutions of the present invention, rather than to limit the same. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that the technical solutions described in the aforementioned embodiments may still be modified, or some of the technical features may be replaced by equivalents. Such modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included in the protection scope of the present invention.

[0163] The above are only specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto. Any technician familiar with the technical field can easily think of various equivalent modifications or replacements within the technical scope disclosed by the present invention, and these modifications or replacements should be included in the protection scope of the present invention. Therefore, the protection scope of the present invention shall be based on the protection scope of the claims.

Claims

1. A method for collecting and processing multiple dynamic parameters of an organism, characterized in that: A collection device having at least two of the three collection functions of ultrasonic signal collection, electromyographic signal collection, and audio signal collection is used to collect at least two of the ultrasonic signal, electromyographic signal, and audio signal from the same body, and the collected signals are synchronously displayed on a display device; the synchronization is that each signal is projected onto the display device in real time, and the time difference between each signal projected onto the display device is equal to the collection time difference of each signal, and the specific method is: S1: first obtain the time required for processing the ultrasonic signal, the electromyographic signal, and the audio signal respectively; obtain the maximum time among them, and then compare the processing time of the remaining signals with the maximum time to obtain the comparison time; the processing time required is the time required from the acquisition time to the signal acquisition time until the signal is displayed on the display device; S2: After the signal processing time required is the maximum time, it is immediately displayed; The remaining signals will be displayed immediately after processing is completed and the comparison time has passed.

2. A method for collecting and processing multiple dynamic parameters of an organism as claimed in claim 1, characterized in that: The ultrasonic 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.

3. A method for collecting and processing multiple dynamic parameters of an organism as claimed in claim 2, characterized in that: The ECG QRS wave signal has a maximum duration; the duration required for processing the ECG QRS wave signal and the duration of processing other signals are specifically compared to: 0.125S.

4. A method for obtaining cardiac ejection fraction using multi-dynamic parameter processing, characterized in that: The ECG QRS waves collected continuously from the same body in the same time period, as well as the M ultrasound images of the heart morphological changes that occur synchronously with the ECG, are distributed on the same time axis and aligned 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 electrocardiogram QRS wave is generated, a first longitudinal pixel column of the M ultrasound image is obtained, and a minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the first 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 electrocardiogram QRS wave is generated, a second longitudinal pixel column of the M ultrasound image is obtained, and the maximum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium is found in the second longitudinal pixel column; The cardiac ejection fraction is calculated using the minimum and maximum values.

5. The method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing as claimed in claim 4, characterized in that: The alignment to the same starting time point is specifically, using the method described in any one of claims 1 to 3 above to synchronously display the collected ultrasonic signals and electromyographic signals on a display device; making the display time difference of the ultrasonic signals and electromyographic signals projected on the display device in real time equal to the collection time difference of the collected signals.

6. The method for obtaining cardiac ejection fraction by using multiple dynamic parameter processing according to claim 4, characterized in that: The electrocardiogram QRS wave and M ultrasound image are collected by a device having the function of collecting both the electrocardiogram QRS wave and M ultrasound image; A duration axis and a real-time status axis are provided on the display device.

7. The method for obtaining cardiac ejection fraction by using multiple dynamic parameter processing according to claim 4, characterized in that: The first specific time length and the second specific time length are calculated by: analyzing a plurality of binarized M ultrasound images, marking the time when the minimum value of the distance between the left ventricular anterior wall endocardium and the left ventricular posterior wall endocardium appears, and calculating 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 minimum value appears, to obtain the first specific time length; The time difference between the time when one of the Q wave, R wave, and S wave appears and the time when the maximum value appears is calculated to obtain the second specific time length.

8. The method for obtaining cardiac ejection fraction by using multi-dynamic parameter processing as claimed in claim 4, characterized in that: M ultrasound images are composed of horizontal pixel rows parallel to the time axis and vertical pixel rows perpendicular to the time axis.

Images