WO2021042298A1

WO2021042298A1 - Vti measuring device and method

Info

Publication number: WO2021042298A1
Application number: PCT/CN2019/104416
Authority: WO
Inventors: 王彦; 王勃; 丛龙飞; 朱磊; 刘硕; 邵涛
Original assignee: 深圳迈瑞生物医疗电子股份有限公司
Priority date: 2019-09-04
Filing date: 2019-09-04
Publication date: 2021-03-11
Also published as: CN114025671A

Abstract

Disclosed are a VTI measuring device and a measuring method. The method comprising: controlling an ultrasonic probe (110) to emit ultrasonic waves at tissue (190) to be measured; receiving an ultrasonic echo returned from the tissue to be measured; finding, according to the ultrasonic echo, a target sampling position having the smallest hemodynamic information interference (305). A VTI at the target sampling position is then calculated. The calculated VTI is the least affected by the friction of the blood vessel wall and can best reflect the heart's pumping ability and cardiac output.

Description

A VTI measuring device and method

Technical field

The invention relates to a medical device, in particular to a measuring device and method for measuring the pumping distance of each heart beat by ultrasound.

Background technique

Cardiac output (CO) is one of the indicators for evaluating the pumping function of the heart, which corresponds to the amount of blood pumped by the heart in a period of time (for example, one minute). Although cardiac output is difficult to directly reflect the patient's condition, in the clinical scene of heart disease, cardiac output can usually be combined with information such as electrocardiogram and blood pressure to grasp the patient's condition. Doctors in the intensive care unit/coronary care unit also usually use CO to monitor the response of the heart after medication to determine the effect of the drug on the heart. Therefore, the accurate detection of the patient's cardiac output is clinically important.

At present, the commonly used formula for calculating cardiac output is:

Cardiac output (CO) = stroke volume (SV) × heart rate (HR)

The stroke volume (SV) is calculated using the following formula:

Stroke output (SV) = valve cross-sectional area (CSA) × pumping distance per stroke

The valve cross-sectional area CSA is calculated using the diameter of the aortic outflow tract. Some research conclusions show that the diameter of the aortic outflow tract of the subject is linearly related to his height. Therefore, the diameter of the aortic outflow tract of the subject is usually calculated based on the height of the subject. The pumping distance per stroke indicates the movement distance of red blood cells during a contraction period. When there is an error in the estimated aortic outflow tract diameter, the current algorithm will cause a significant error in the calculated value of cardiac output CO.

Summary of the invention

technical problem

The solution to the problem

Technical solutions

The present invention mainly provides a VTI measuring device and method for improving the accuracy of cardiac output assessment.

In an embodiment, a VTI measurement device is provided, including:

Ultrasound probe, used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit for outputting a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the ultrasonic echo of the first ultrasonic wave Signal, obtaining hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave, and obtaining a target sampling position according to the hemodynamic information, where the target sampling position refers to a position where hemodynamic information is least disturbed; the processor It is also used to control the ultrasonic probe to transmit a second ultrasonic wave to the tested tissue in a Doppler mode through the transmitting circuit, and to receive the echo of the second ultrasonic wave returned by the tested tissue through the receiving circuit to obtain the second ultrasonic wave. The ultrasonic signal generates the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave, and obtains the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and Calculate the blood flow velocity time integral VTI at the target sampling position according to the Doppler spectrum envelope;

The output device is used to output VTI.

In an embodiment, a VTI measurement device is provided, including:

The receiving circuit is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the measured tissue to obtain the ultrasonic echo signal;

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the tested tissue through the receiving circuit to obtain the ultrasonic wave of the first ultrasonic wave. The echo signal generates an ultrasound image based on the ultrasound echo signal of the first ultrasound, the ultrasound image includes a B image and/or a blood flow image, and a target sampling location is marked on the ultrasound image, and the target sampling location is an ultrasound image The position where the hemodynamic information is the least interfered; the processor is also used to control the ultrasound probe to transmit a second ultrasonic wave to the tested tissue according to the Doppler mode through the transmitting circuit, and to receive the second ultrasonic wave through the receiving circuit. The echo of the second ultrasonic wave returned by the tissue, the ultrasonic echo signal of the second ultrasonic wave is obtained, the Doppler spectrogram at the target sampling position is obtained according to the ultrasonic echo of the second ultrasonic wave, and the Doppler spectrogram is obtained according to the Doppler spectrogram The Doppler spectrum envelope of the Doppler spectrogram, and the velocity time integral VTI of the blood flow at the target sampling position is calculated according to the Doppler spectrum envelope;

The output device is used to output VTI.

In an embodiment, a VTI measurement device is provided, including:

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is used to control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the tested tissue through the receiving circuit, to obtain the ultrasonic echo of the first ultrasonic wave. Wave signal, obtain blood flow image data according to the ultrasound echo signal of the first ultrasound, obtain the target sampling position according to the blood flow image data, and obtain the multiplicity of the target sampling position according to the ultrasound echo signal of the first ultrasound. The Doppler spectrogram, the Doppler spectrum envelope of the Doppler spectrogram is obtained according to the Doppler spectrogram, and the velocity time integral VTI of the blood flow at the target sampling position is calculated according to the Doppler spectrum envelope. ；

The output device is used to output VTI.

In an embodiment, a VTI measurement device is provided, including:

The receiving circuit is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the measured tissue, and obtain the ultrasonic echo signal output by the ultrasonic probe;

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the ultrasonic echo of the first ultrasonic wave Signal, obtaining hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave, and obtaining a target sampling position according to the hemodynamic information, where the target sampling position refers to a position where hemodynamic information is least disturbed; the processor Obtain the Doppler spectrogram at the target sampling position, obtain the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and calculate the blood at the target sampling position according to the Doppler spectrum envelope. The velocity time integral VTI of the flow;

The output device is used to output VTI.

In an implementation, a VTI measurement device is provided, including:

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the tested tissue through the receiving circuit to obtain the ultrasonic wave of the first ultrasonic wave. The echo signal obtains hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave, and obtains a target sampling position according to the hemodynamic information, and the target sampling position means that the hemodynamic information is disturbed and satisfies a first preset condition The processor is also used to control the ultrasound probe to transmit a second ultrasonic wave to the measured tissue in a Doppler mode through the transmitting circuit, and to receive the second ultrasonic wave returned by the measured tissue through the receiving circuit Obtain the ultrasonic echo signal of the second ultrasonic wave, generate the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave, and obtain the Doppler spectrogram according to the Doppler spectrogram The Doppler spectrum envelope of the Le spectrogram, and calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

The output device is used to output VTI.

In an implementation, a VTI measurement device is provided, including:

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the tested tissue through the receiving circuit to obtain the ultrasonic wave of the first ultrasonic wave. An echo signal, an ultrasound image is generated according to the ultrasound echo signal of the first ultrasound, the ultrasound image includes a B image and/or a blood flow image, a target sampling position is marked on the ultrasound image, and the target sampling position is The position where the hemodynamic information in the ultrasound image is interfered with and meets the first preset condition; the processor is further configured to control the ultrasound probe to emit a second ultrasound to the tissue under test in a Doppler mode through the transmission circuit , And receive the echo of the second ultrasonic wave returned by the tested tissue through the receiving circuit, obtain the ultrasonic echo signal of the second ultrasonic wave, and obtain the Doppler at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave Spectrogram, obtain the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and calculate the velocity time of the blood flow at the target sampling position according to the Doppler spectrum envelope Points VTI;

The output device is used to output VTI.

In an implementation, a VTI measurement device is provided, including:

Beam synthesis module, used for beam synthesis of ultrasonic echo signals;

The processor is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the tested tissue through the receiving circuit to obtain the ultrasonic wave of the first ultrasonic wave. The echo signal obtains hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave, and obtains a target sampling position according to the hemodynamic information, and the target sampling position means that the hemodynamic information is disturbed and satisfies a first preset condition The processor also obtains the Doppler spectrogram at the target sampling position, obtains the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and according to the Doppler spectrogram Le spectrum envelope calculation of the velocity time integral VTI of the blood flow at the target sampling position;

The output device is used to output VTI.

In an embodiment, a VTI measurement method is provided, including:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Obtain hemodynamic information according to the ultrasound echo signal of the first ultrasound;

Obtain the target sampling position according to the hemodynamic information;

Controlling the ultrasound probe to transmit a second ultrasonic wave to the measured tissue according to the Doppler mode, and receive the echo of the second ultrasonic wave returned by the measured tissue, to obtain an ultrasonic echo signal of the second ultrasonic wave;

Obtain the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Obtaining the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram;

Calculate the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.

In an embodiment, a VTI measurement method is provided, including:

Generating an ultrasound image according to the echo of the first ultrasound, the ultrasound image including a B image and/or a blood flow image;

Marking a target sampling location on the ultrasound image, where the target sampling location is a location in the ultrasound image where hemodynamic information is least disturbed;

Obtain the Doppler spectrum envelope at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Calculate the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope calculation;

Output the VTI.

In an embodiment, a VTI measurement method is provided, including:

Obtain hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave. The ultrasonic echo signal of the first ultrasonic wave collects an ultrasonic wave transmitted from the ultrasonic probe to the measured tissue and receives the first ultrasonic wave returned by the measured tissue. The echo is obtained;

Obtain the target sampling position according to the hemodynamic information;

The velocity time integral VTI of the blood flow at the target sampling position is calculated based on the Doppler spectrum envelope.

In an embodiment, a VTI measurement method is provided, including:

Obtain the target sampling position according to the hemodynamic information;

Acquiring a Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the first ultrasonic wave;

Calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.

In an embodiment, a VTI measurement method is provided, including:

Calculating Doppler spectrograms at multiple positions in the scanning area of the first ultrasound according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Determine the target Doppler spectrogram from a plurality of Doppler spectrograms, where the target Doppler spectrogram has the maximum peak spectral velocity;

According to the target Doppler spectrogram, obtain the Doppler spectrum envelope of the target Doppler spectrogram;

Calculate the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Output VTI.

In an embodiment, a VTI measurement method is provided, including:

Calculating Doppler spectrograms at multiple locations in the scanning area of the first ultrasound according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Determining, from a plurality of Doppler spectrograms, a target Doppler spectrogram that meets the second preset condition;

Output VTI.

In an embodiment, a VTI measurement method is provided, which includes:

Calculating the Doppler spectrogram of each point in the scanning area of the first ultrasonic wave according to the ultrasonic echo signal of the ultrasonic wave, and obtaining the Doppler spectrogram of each point in the scanning area of the first ultrasonic wave;

Determine the target Doppler spectrogram from the Doppler spectrogram of each point in the scanning area of the first ultrasound, where the target Doppler spectrogram has the maximum peak spectral velocity;

Output VTI.

In an embodiment, a VTI measurement method is provided, including:

Generating a first ultrasound image based on the first ultrasound echo signal, and determining a region of interest of the first ultrasound image;

Calculating a Doppler spectrogram of each point in the region of interest of the first ultrasound image according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Output VTI.

In an embodiment, a VTI measurement method is provided, including:

Marking a target sampling position on the ultrasound image, where the target sampling position is a position in the ultrasound image where hemodynamic information is disturbed and satisfies the first preset condition;

Output the VTI.

In an embodiment, a computer-readable storage medium is provided, which includes a program, and the program can be executed by a processor to implement the above-mentioned method.

In one embodiment, a method for evaluating the pumping function of the heart is provided, and the pumping function of the heart is evaluated by using the above-mentioned device or the VTI obtained by the above-mentioned method.

The beneficial effects of the invention

Beneficial effect

In the above embodiment, because the calculated VTI is the VTI at the position where the hemodynamic information in the left ventricular outflow tract is the least disturbed, that is, the VTI is the least affected by the friction of the blood vessel wall and can best reflect the heart's pumping ability. It best reflects cardiac output.

Brief description of the drawings

Description of the drawings

Figure 1 is a schematic diagram of the structure of an ultrasonic diagnostic equipment;

Figure 2 is a flow chart of measuring VTI in the first embodiment;

Figure 3 is a schematic diagram of a B image in an embodiment;

Figure 4 is a Doppler spectrum diagram at a sampling position in an embodiment;

FIG. 5 is a flowchart of measuring VTI in various embodiments;

FIG. 6 is a flowchart of measuring VTI in various embodiments;

Fig. 7 is a flow chart of measuring VTI in an embodiment.

Invention embodiment

Embodiments of the present invention

Hereinafter, the present invention will be further described in detail through specific embodiments in conjunction with the accompanying drawings. Among them, similar elements in different embodiments use related similar element numbers. In the following embodiments, many detailed descriptions are used to make this application better understood. However, those skilled in the art can easily realize that some of the features can be omitted under different circumstances, or can be replaced by other elements, materials, and methods. In some cases, some operations related to this application are not shown or described in the specification. This is to avoid the core part of this application being overwhelmed by excessive descriptions. For those skilled in the art, these are described in detail. Related operations are not necessary, they can fully understand the related operations based on the description in the manual and the general technical knowledge in the field.

In addition, the features, operations, or features described in the specification can be combined in any appropriate manner to form various implementations. At the same time, the steps or actions in the method description can also be sequentially exchanged or adjusted in a manner obvious to those skilled in the art. Therefore, the various sequences in the specification and the drawings are only for the purpose of clearly describing a certain embodiment, and are not meant to be a necessary sequence, unless it is specified that a certain sequence must be followed.

The serial numbers assigned to the components herein, such as "first", "second", etc., are only used to distinguish the described objects and do not have any sequence or technical meaning. The "connection" and "connection" mentioned in this application include direct and indirect connection (connection) unless otherwise specified.

In the study and evaluation of the testee’s heart pumping function, the five chambers of the heart were scanned by ultrasound, and the cardiac output CO was obtained according to the valve cross-sectional area of the left ventricular outflow tract and the movement distance of red blood cells during a systolic period. The inventor realized that the aortic valve annulus is fibrous. For a subject, the left ventricular outflow tract is unlikely to change in a short period of time. The relative change in cardiac output CO is mainly affected by the pumping distance per stroke. Therefore, the relative change of cardiac output CO can be estimated by the relative change of the pumping distance per stroke, and the measurement of the pumping distance per stroke is less prone to errors. At present, the pumping distance per stroke is generally calculated by using a Doppler spectrum image at a certain position on the cross-sectional area of the left ventricular outflow tract valve, specifically the velocity time integral (VTI) of the Doppler spectrum envelope. Therefore, the present invention proposes to use the pumping distance per stroke to reflect the heart pumping function, and when the pumping distance per stroke is calculated, the visualized velocity time integral VTI is output to the user.

VTI can be calculated from the Doppler spectrum envelope of an ultrasonic receiving point in the measured tissue. If the most suitable sampling location can be found, and the VTI can be calculated based on the Doppler spectrum envelope at the sampling location, the result is VTI will be more accurate, which is more conducive to the accurate evaluation of the heart pumping function.

In the embodiment of the present invention, a number of examples are given to determine the appropriate sampling location (referred to as the "target sampling location" in this article) based on the hemodynamic information, and the person who interferes with the hemodynamic information at the sampling location If the first predetermined condition is satisfied (for example, the interference is minimal, the interference is less than a certain threshold, the interference is within a certain range, etc.), the VTI calculated by using the Doppler spectrum envelope of the sampling position will be more accurate. The hemodynamic information can be blood flow velocity information and/or energy information, or Doppler spectrum information, which can be obtained from blood flow image data. In the process of measuring VTI, only one mode can be used to transmit ultrasound to the measured tissue (such as the five chambers of the heart) to obtain hemodynamic information and Doppler spectrum data used to calculate VTI, or multiple modes can be used successively Transmit ultrasound to the tested tissue to obtain hemodynamic information and Doppler spectrum data used to calculate VTI. For example, first use the first mode to transmit ultrasound to the five chambers of the heart to obtain hemodynamic information. The information determines the most suitable sampling location, and then uses the second mode to transmit ultrasonic waves to the sampling location to obtain the Doppler spectrum data at that location.

Hereinafter, the various implementation manners will be described separately by taking the use of ultrasonic diagnostic equipment as an example.

Please refer to FIG. 1, in an embodiment shown in FIG. 1, an ultrasonic diagnostic equipment 100 is provided. The ultrasonic diagnostic equipment 100 includes an ultrasonic probe 110, a transmitting circuit 120, a receiving circuit 130, a beam combining module 140, and an IO solution. The adjustment module 150, the processor 160, the output device 170, and the memory 180.

The ultrasonic probe 110 includes a transducer (not shown in the figure) composed of a plurality of array elements arranged in an array. The plurality of array elements are arranged in a row to form a linear array, or arranged in a two-dimensional matrix to form a surface array. The array elements can also form a convex array. The array element is used to transmit an ultrasonic beam according to the excitation electrical signal, or to transform the received ultrasonic beam into an electrical signal. Therefore, each array element can be used to realize the mutual conversion of electric pulse signals and ultrasonic beams, so as to realize the transmission of ultrasonic waves to the target tissues to be detected (such as organs, tissues, blood vessels, fetuses, etc.) in the human body or animals. The echo of ultrasound reflected by the tissue. When performing ultrasonic testing, you can control which array elements are used to transmit ultrasonic beams and which array elements are used to receive ultrasonic beams through the transmitting circuit and receiving circuit, or control the array elements to be used for transmitting ultrasonic beams or receiving ultrasonic beams in time slots. wave. The array elements participating in the ultrasonic transmission can be excited by electrical signals at the same time, thereby simultaneously emitting ultrasonic waves; or the array elements participating in the ultrasonic transmission can also be excited by several electrical signals with a certain time interval, so as to continuously emit ultrasonic waves with a certain time interval.

The array element, for example, uses piezoelectric crystals to convert electrical signals into ultrasonic signals according to the transmission sequence transmitted by the transmitting circuit. According to the application, the ultrasonic signals may include one or more scan pulses, one or more reference pulses, and one or more push pulses. And/or one or more Doppler pulses.

Herein, the ultrasonic waves emitted by the ultrasonic probe may be focused waves, plane waves or divergent waves.

The user selects the appropriate position and angle by moving the ultrasound probe 110 to transmit ultrasound to the tested tissue 190 and receive the echo of the ultrasound returned by the tested tissue 190, and output the ultrasound echo signal. The ultrasound echo signal is based on the receiving array element. The channel analog electrical signal formed by the channel carries amplitude information, frequency information and time information.

The transmitting circuit 120 is used to generate a transmitting sequence according to the control of the processor. The transmitting sequence is used to control part or all of the multiple array elements to transmit ultrasonic waves to the target tissue. The parameters of the transmitting sequence include the position of the array element used for transmission, the number of array elements, and the ultrasonic wave. Beam emission parameters (e.g., amplitude, frequency, number of shots, interval of emission, angle of emission, waveform, focus position, etc.). In some cases, the transmitting circuit 120 is also used to phase delay the transmitted beams, so that different transmitting array elements emit ultrasonic waves at different times, so that each transmitted ultrasonic beam can be focused on a predetermined region of interest. Different working modes, such as B image mode, C image mode, and D image mode (Doppler mode), the transmission sequence parameters may be different. Ultrasound is sent in different working modes, and the echo signal is received by the receiving circuit 130 and followed by After processing by the modules and corresponding algorithms, the ultrasound data in each working mode can be obtained. According to the ultrasound data in each working mode, B images reflecting the anatomical structure of the tissues, C images reflecting the anatomical structure and blood flow information of the tissues, and Doppler images can be generated respectively. D image of Le spectrum image.

The receiving circuit 130 is used to receive ultrasonic echo signals from the ultrasonic probe and process the ultrasonic echo signals. The receiving circuit 130 may include one or more amplifiers, analog-to-digital converters (ADC), and the like. The amplifier is used to amplify the received echo signal after proper gain compensation. The amplifier is used to sample the analog echo signal at a predetermined time interval to convert it into a digitized signal. The digitized echo signal still retains its amplitude Information, frequency information and phase information. The data output by the receiving circuit 130 may be output to the beam combining module 140 for processing, or output to the memory 180 for storage.

The beam synthesis module 140 is signal-connected to the receiving circuit 130, and is used to perform beam synthesis processing such as corresponding delay and weighted summation on the echo signal. Because the distance between the ultrasonic receiving point in the measured tissue and the receiving array element is different, therefore, The channel data of the same receiving point output by different receiving array elements have delay differences, and delay processing is required to align the phase, and perform weighted summation of the different channel data of the same receiving point to obtain the ultrasound image data after beam synthesis. The ultrasound image data output by the beam synthesis module 140 is also referred to as radio frequency data (RF data). The beam combining module 140 outputs the radio frequency data to the IQ demodulation module 150. In some embodiments, the beam combining module 140 may also output the radio frequency data to the memory 180 for buffering or storage, or directly output the radio frequency data to the processor 160 for image processing.

The beam combining module 140 may perform the above functions in hardware, firmware, or software. For example, the beam combining module 140 may include a central controller circuit (CPU) capable of processing input data according to specific logic instructions, one or more micro-processing chips, or Any other electronic components, when the beam combining module 140 is implemented in software, it can execute instructions stored on a tangible and non-transitory computer readable medium (for example, the memory 180) to perform beam combining using any appropriate beam combining method Calculation.

The IQ demodulation module 150 removes the signal carrier through IQ demodulation, extracts the organizational structure information contained in the signal, and performs filtering to remove noise. The signal obtained at this time is called a baseband signal (IQ data pair). The IQ demodulation module 150 outputs the IQ data pair to the processor 160 for image processing.

In some embodiments, the IQ demodulation module 150 also buffers and saves the IQ data output to the memory 180, so that the processor can read the data from the memory 180 for subsequent image processing.

The IQ demodulation module 150 may also use hardware, firmware, or software to perform the above functions. In some embodiments, the IQ demodulation module 150 and the beam synthesis module 140 may also be integrated in a chip.

The processor 160 is used to configure a central controller circuit (CPU), one or more microprocessors, a graphics controller circuit (GPU) or any other electronic components capable of processing input data according to specific logic instructions, which can be configured according to the input data Commands or predetermined commands perform control of peripheral electronic components, or perform data reading and/or saving to the memory 180, and input data can also be processed by executing a program in the memory, for example, the collected data can be processed according to one or more working modes. The ultrasound data performs one or more processing operations, including but not limited to adjusting or limiting the form of ultrasound emitted by the ultrasound probe 110, generating various image frames for subsequent display by the display 171, or adjusting or limiting the display on the display 171 Or adjust one or more image display settings displayed on the display 171 (for example, ultrasound images, interface components, locating regions of interest).

When the echo signal is received, the collected ultrasound data can be processed by the processor 160 in real time during scanning or treatment, or can be temporarily stored in the memory 180, and processed in a quasi real-time manner in online or offline operation.

In this embodiment, the processor 160 may include a control module 161, a grayscale imaging module 163, a blood flow velocity calculation module 162, a blood flow image module 164, a Doppler spectral image module 165, and a VTI calculation module 166. In other embodiments, the processor 160 may further include other image processing modules, such as an elasticity detection module for detecting the elasticity of the tissue.

The control module 161 is electrically connected to the transmitting circuit 120 and the receiving circuit 130 to control the operation of the transmitting circuit 120 and the receiving circuit 130, for example, controlling the transmitting circuit 120 and the receiving circuit 130 to work alternately or simultaneously. The control module can also determine a suitable working mode according to the user's selection or the setting of the program, form a transmission sequence corresponding to the current working mode, and send the transmission sequence to the transmission circuit 120, so that the transmission circuit 120 uses a suitable transmission sequence to control the ultrasound The probe 110 emits ultrasonic waves. For example, in this embodiment, the control module 161 successively controls the ultrasonic probe to transmit ultrasonic waves in two working modes according to the setting of the program, first controls the ultrasonic probe to transmit the first ultrasonic wave used to obtain hemodynamic information of the measured tissue, and receives Measure the echo of the first ultrasonic wave returned by the tissue. After obtaining the sampling position according to the hemodynamic information, the control module 161 controls the ultrasound probe to transmit the second ultrasonic wave to the measured tissue according to the Doppler mode, and receive the echo of the second ultrasonic wave returned by the measured tissue.

The grayscale imaging module 163, the blood flow velocity calculation module 162, the blood flow image module 164, and the Doppler spectrum image module 165 constitute an image processing module. The grayscale imaging module 163 is used to process the ultrasound data to generate a grayscale image of signal strength changes in the scanning range. The grayscale image reflects the internal anatomical structure of the tissue and is called a B image. The grayscale imaging module 163 can output the B image to the output device 170, and the output device 170 outputs a visualized B image, for example, the output device 170 displays the B image or prints the B image. The grayscale imaging module 163 may also output the B image to the blood flow image module 164, and the B image and the blood flow information output by the blood flow velocity calculation module 162 together generate the blood flow image.

The blood flow velocity calculation module 162 is used to process the ultrasound data to generate the blood flow signal within the scanning range, for example, directly use the speckle method to process the IQ data pair or the grayscale image generated by the grayscale imaging module 163 to calculate each point Blood flow information. Alternatively, the blood flow velocity calculation module 162 can also process the IQ data pair or the grayscale image generated by the grayscale imaging module 163 using a wall filter algorithm to suppress the echo signals of stationary tissues or tissues with a slower speed, and extract blood flow Ultrasonic echo signal, using autocorrelation algorithm to calculate the blood flow force information at each point on the ultrasonic echo signal of blood flow. Hemodynamic information includes blood flow velocity information and energy information. The blood flow velocity calculation module 162 outputs blood flow information to the blood flow image module 164 and the Doppler spectrum image module 165 respectively.

The blood flow image module 164 is configured to superimpose the B image output by the grayscale imaging module 163 and the blood flow information output by the blood flow velocity calculation module 162 to generate a color blood flow image, which is also called a C image.

The Doppler spectrum image module 165 is used to obtain Doppler spectrum images of each point according to the received ultrasonic echo signal. The Doppler spectrum image module 165 can output the Doppler spectrum image to the output device 170 for display or printing.

The VTI calculation module 166 is used to obtain a Doppler envelope according to the Doppler spectrum image obtained by the Doppler spectrum image module 165, and calculate the blood flow velocity at a specific location according to the Doppler envelope. Time integral VTI. In this embodiment, the VTI calculation module 166 is used to automatically identify the Doppler spectrogram at the position where the bleeding flow force information is least disturbed, and obtain the Doppler spectrum envelope based on the identified Doppler spectrogram. The Puller spectrum envelope calculates the velocity time integral of the blood flow at the position where the hemodynamic information is least disturbed.

The memory 180 is used to store data or programs. For example, the memory 180 may be used to store collected ultrasound data or image frames generated by the processor that are not displayed immediately. The image frames may be 2D or 3D images, or the memory 180 may Stores the graphical user interface, one or more default image display settings, and programming instructions for the processor, beamforming module or IQ decoding module. The memory 180 may be a tangible and non-transitory computer-readable medium, such as flash memory, RAM, ROM, EEPROM, and so on.

The output device 170 is used to output various detection or diagnosis results, and the results can be visually presented to the doctor or the subject in the form of graphics, images, text, numbers, or charts. In this embodiment, the output device 170 includes a display 171 and/or a printer 172.

In some embodiments, the ultrasonic diagnostic equipment 100 may also include an input device (not shown in the figure). The input device may be, for example, a keyboard, operation buttons, a mouse, a trackball, etc., or a touch screen integrated with a display. Control screen. When the input module is a keyboard or operation button, the user can directly input operation information or operation instructions through the input module; when the input module is a mouse, trackball or touch screen, the user can connect the input module to the soft keys, Operation icons, menu options, etc. cooperate to complete the input of operation information or operation instructions.

Please refer to FIG. 2. Based on the ultrasonic diagnostic device 100 shown in FIG. 1, the process of measuring VTI is shown in FIG. 2, and includes the following steps:

Step 10: The processor controls the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue through the transmitting circuit, and receives the echo of the first ultrasonic wave returned by the tested tissue. In this embodiment, the measured tissue includes five chambers of the heart, and the first ultrasonic wave can be a focused wave, a plane wave, or a diverging wave. In order to prevent the most suitable sampling position from being missed, in this embodiment, the first ultrasound adopts a full-screen multi-beam focused wave or plane wave to cover the tissue parts of the five chambers of the heart as much as possible. For example, the user can position the ultrasound probe, align the transmitting array element of the ultrasound probe with the long axis of the tip of the heart to launch, scan the cut surface of the heart, and set the transmission parameters according to the B mode. Various tissue interfaces on the cut surface reflect or scatter at least part of the first ultrasonic wave to form a reflected echo. The ultrasonic probe receives the echo of the first ultrasonic wave and converts it into a corresponding electrical signal for output. The ultrasound acquisition settings of the ultrasound probe can be set or selected by the user using the input device. For example, the user can define the gain, power, time gain compensation (TGC), resolution, etc. of the ultrasound probe by selecting one or more interface components of the GUI (Graphical User Interface) displayed on the display.

Step 11: Process the echo of the first ultrasonic wave. The echo of the first ultrasonic wave is sensed by the ultrasonic probe 110, and after the receiving circuit 130, the beam synthesis module 140, the IQ demodulation module 150 and each image processing module, the ultrasonic echo signal of the blood flow is extracted from the ultrasonic data, and the ultrasonic echo signal is calculated Hemodynamic information, which is used to subsequently determine the sampling location. In order to provide users with intuitive visual perception, in this step, data frames of B image or C image are also generated according to the echo of the first ultrasound. Each data frame includes multiple data sets, and each data set includes position coordinates. The pixel value, the position coordinate and the pixel in the display area of the B image or C image on the display screen form a one-to-one mapping relationship, and the pixel value represents the brightness and/or color of the pixel at the position. When the image is a grayscale image (such as a B image), the pixel value can be a brightness value; when the image is a color image (such as a C image), the pixel value can be a brightness value and a color value. For displays that use the three primary colors of red, green and blue , The color value includes the value of the three colors of red, green and blue or the proportional relationship of the three. After the data frame is generated, the data frame is output to the display for display, thereby displaying a visualized B image or C image on the display screen. As shown in FIG. 3, a B image 300 generated based on the echo of the first ultrasonic wave. In the embodiment of the present invention, the tissue anatomy structure 301 of the five chambers of the heart is displayed on the B image 300.

Step 12. Determine the region of interest. According to the tissue anatomy 301 of the five chambers of the heart displayed on the B image 300, the marking frame 302 of interest can be manually marked at the position of the left ventricular outflow tract. According to the echo of the first ultrasound, the processor can form various chambers of the heart based on the change in pixel intensity. For example, a low-intensity pixel cluster represents the chamber 303, and the relatively high-intensity pixel cluster surrounding these low-intensity pixel clusters represents the diaphragm 304 Therefore, through the B image, the user (such as a doctor) can identify each chamber according to the characteristics of each chamber. For example, the left ventricle is the larger of the chambers relative to the other chambers, so that the identification frame of interest 302 can be marked at the position of the left ventricular outflow tract, and the area enclosed by the identification frame 302 of interest is called the region of interest. In some embodiments, the processor can automatically identify the left ventricle based on the echo data of the first ultrasound, for example, using a machine learning method for automatic identification, and automatically locate the region of interest based on the identified position of the left ventricular outflow tract , And then automatically mark the interest identification frame 302 on at least a part of the left ventricular outflow tract image, as shown in FIG. 3. Optionally, the position and size of the interest identification frame 302 can be adjusted by the user operating an input device (such as a mouse or a touch screen), so that the size and position of the region of interest can also be adjusted.

Step 13. Determine the target sampling location. The blood is pumped from the left ventricle through the contraction of the heart, and the blood will be rubbed by the blood vessel wall during the flow, which will reduce the flow rate. The blood closer to the blood vessel wall is more affected by the friction of the blood vessel wall, and the blood in the middle position is less affected by the blood vessel wall. Therefore, the present invention hopes to collect the blood in the middle part of the blood vessel wall as a sample for calculating the VTI. In this embodiment, the processor extracts the bleeding flow force information according to the ultrasonic echo signal of the first ultrasound, and uses the position where the hemodynamic information is disturbed and satisfies the first preset condition as the target sampling position. The hemodynamic information includes position information, as well as blood flow velocity information and/or energy information. For example, wall filtering and autocorrelation processing are performed on the echo data of the first ultrasound to obtain the hemodynamic information. The phase of the hemodynamic information is It is the blood flow velocity and the model of the hemodynamic information is the energy information. The first preset condition may be that the interference is minimal, or that the interference is less than a certain threshold, or that the interference is within a certain range, and so on.

In a specific embodiment, the target sampling location can be determined according to the blood flow velocity information. The solution is to find the hemodynamic information with the highest blood flow velocity in the obtained hemodynamic information, and further obtain the blood flow. The position information of the hemodynamic information with the highest speed, and the position with the highest blood flow speed as the target sampling position. In a specific embodiment, the target sampling location can be determined according to the blood flow velocity information, and the solution is to find the hemodynamic information with the largest average blood flow velocity in a certain period of time in the obtained hemodynamic information Further, the position information of the hemodynamic information with the maximum average blood flow velocity can be obtained, and the position with the maximum average blood flow velocity is taken as the target sampling position. In a specific embodiment, the target sampling location can be determined according to the blood flow velocity information. The solution is to find the blood flow velocity information with the maximum peak value within a certain period of time in the obtained hemodynamic information, and further obtain The position information of the dynamic information with the maximum peak blood flow velocity, and the position of the blood flow velocity with the maximum peak as the target sampling position. In an embodiment, the target sampling location can be determined according to the blood flow velocity information. The solution is to find the blood flow velocity or the average blood flow velocity or the peak value of the blood flow velocity in the obtained hemodynamic information. Threshold conditions can meet clinical needs, for example, blood flow velocity is greater than 60% of maximum blood flow velocity, or average blood flow velocity is not less than 40cm/s, or the peak blood flow velocity is 30cm/s-40cm/s and so on.

In another specific embodiment, the target sampling position can be determined according to the energy information. The solution is to find the hemodynamic information with the largest energy information in the obtained hemodynamic information, and further obtain the hemodynamic information with the largest energy information. For the position information of the hemodynamic information, the position with the largest energy information is used as the target sampling position. In a specific embodiment, the target sampling location can be determined according to the energy information. The solution is to find the hemodynamic information with the largest average energy information in a certain period of time in the obtained hemodynamic information, and further The position information of the hemodynamic information with the largest average energy information is obtained, and the position with the largest average energy information is taken as the target sampling position. In a specific embodiment, the target sampling location can be determined according to the energy information. The solution is to find the energy information with the largest peak value within a certain period of time in the obtained hemodynamic information, and further obtain the largest peak energy information. For the position information of the dynamic information, the energy information position with the maximum peak value is used as the target sampling position. In one embodiment, the target sampling location can be determined according to the energy information. The solution is to find the energy or average energy or the peak value of the energy information in the obtained hemodynamic information to meet a certain threshold condition to meet the clinical requirements. Demand, for example, the energy information is greater than 70% of the maximum energy information, and so on.

In another specific embodiment, the target sampling position can be determined based on the combination of blood flow velocity information and energy information. The solution is to first identify the blood flow information points whose energy information exceeds a set threshold, and combine these points Find the hemodynamic information with the maximum blood flow velocity or the blood flow velocity meeting certain conditions, and use the position with the maximum blood flow velocity or meeting certain conditions as the target sampling position. The Doppler spectrum at the target sampling position will be collected later, so the target sampling position is also referred to as a Doppler sampling gate.

In an embodiment, to facilitate the user to view, the position of the sampling gate 305 is marked on the B image 300. Under normal circumstances, because the VTI is calculated using a Doppler spectrum image at a certain position on the cross-sectional area of the left ventricular outflow tract valve, the position of the sampling gate 305 should be located inside the marking frame 302 of interest. In order to reduce the amount of data processing, in a preferred embodiment, the processor extracts the bleeding flow force information according to the echo of the first ultrasound, and finds out the area of interest according to the area enclosed by the interest identification frame 302 Therefore, in a preferred embodiment, only the hemodynamic information of each point in the selected area in the identification box of interest is compared, and the hemodynamic information is selected. The position with the least interference is used as the target sampling position.

In some embodiments, step 12 can be omitted, that is, the interest identification box is not marked. In this case, the hemodynamic information of each point in the full-screen area will be compared, and the hemodynamic information will be selected. The largest position is used as the target sampling position.

After the target sampling location is determined, the target sampling location 305 can be marked on the B image or the C image as shown in FIG. 3 to provide the doctor or the subject with a more direct visual perception, or it may not be marked.

Step 14. Transmit the second ultrasonic wave and receive the echo. After obtaining the target sampling position, the processor controls the transmitter circuit to switch to the Doppler mode, and controls the ultrasound probe to transmit the second ultrasonic wave to the measured tissue according to the Doppler mode. The transmission parameters of the second ultrasonic wave are set according to the Doppler mode. It can be pulse Doppler or continuous Doppler. The second ultrasonic wave can be a focused wave, a plane wave or a diverging wave. The scanning range of the second ultrasonic wave includes at least the target sampling position. In a preferred embodiment, the second ultrasonic wave may be emitted only to the target sampling position, and the Doppler data at the target sampling position can be obtained through processing. In some embodiments, the second ultrasonic wave may also be emitted for the full screen or a larger range (for example, a region of interest) including the target sampling position.

Step 15: Obtain the Doppler spectrogram at the target sampling position. The echo of the second ultrasonic wave returned by the tested tissue is an echo signal of a duration. The echo of the second ultrasonic wave is passed through the receiving circuit 130, the beam synthesizing module 140, the IQ demodulation module 150, and the velocity calculation module 162 After processing, the ultrasound echo signal of the blood flow is extracted from the ultrasound data, the Doppler spectrum imaging module 165 obtains the Doppler data according to the ultrasound echo signal of the blood flow, and the Doppler spectrogram 401 is obtained according to the Doppler data. As shown in Figure 4. When only the second ultrasonic wave is transmitted to the target sampling position, the Doppler spectrum imaging module 165 can directly obtain the Doppler spectrogram 401 at the target sampling position. When transmitting the second ultrasonic wave for the full screen or a larger range including the sampling position, the Doppler spectrum imaging module 165 selects the blood flow ultrasonic echo at the target sampling position from the blood flow ultrasonic echo signals at many positions Signal, and then the Doppler spectrogram 401 at the target sampling position is obtained. Or, first obtain the Doppler spectrum images of many positions, and then select the Doppler spectrum images at the target sampling position from them.

Step 16. Obtain the Doppler spectrum envelope at the target sampling position. The envelope 403 of the Doppler spectrum image is automatically traced according to the Doppler spectrum image at the target sampling position. In order to provide the doctor or the subject with a more direct visual perception, the Doppler spectrogram 306 at the target sampling position can be displayed on or beside the B image or the C image, as shown in FIG. 3.

Step 17. Calculate the velocity time integral (ie VTI). As shown in the Doppler spectrum diagram 401 shown in FIG. 4, VTI represents the area 405 under the curve of the Doppler spectrum envelope 403, and the area 405 under the curve can be obtained by integrating the curve. When calculating VTI, a certain Doppler spectrum envelope 403 curve can be integrated to calculate the area under the Doppler spectrum envelope 403 curve to obtain the velocity time integral of the blood flow at the target sampling position VTI; VTI can also be calculated based on the Doppler spectrum envelope at the target sampling position in multiple cardiac cycles. As shown in Figure 4, the distance 407 between two adjacent envelopes represents a cardiac cycle. The areas under multiple envelopes are then averaged to obtain the average VTI for multiple cardiac cycles.

Step 18: Output the velocity time integral VTI for the convenience of doctors to check. The output mode may be displayed on the display interface, as shown in FIG. 3, the VTI value 307 is displayed next to the ultrasound image 301, as shown in the figure, VTI=17.2crn. In other embodiments, it can also be printed out by a printer.

In the above embodiment, it is calculated that the VTI uses two ultrasonic transmissions, that is, the first ultrasonic wave is transmitted in the B mode or the C mode, the target sampling position is detected, and then the second ultrasonic wave is transmitted in the Doppler mode. , Obtain the Doppler spectrogram of the target sampling position, obtain the Doppler spectrum envelope of the target sampling position according to the Doppler spectrogram, and calculate the blood flow velocity time of the target sampling position according to the Doppler spectrum envelope of the target sampling position Points VTI. In another embodiment, the Doppler spectrogram of the target sampling position can be obtained by one ultrasonic emission, and the VTI can be further calculated. The processing flow is shown in Fig. 5 and includes the following steps:

Step 20: Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue, and control the receiving circuit to receive the echo of the first ultrasonic wave returned from the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave. The first ultrasonic wave can be a focused wave, a plane wave or a diverging wave. In order to prevent the most suitable sampling position from being missed, in this embodiment, the first ultrasound adopts a full-screen multi-beam focused wave or plane wave to cover the tissue parts of the five chambers of the heart as much as possible. The first ultrasonic wave is reflected or scattered by the interface of the five chambers of the heart to form a reflected echo, and the echo signal of the first ultrasonic wave is obtained.

Step 21: Obtain blood flow image data according to the echo signal of the first ultrasound. The echo of the first ultrasonic wave is sensed by the ultrasonic probe 110, and the blood flow image data is obtained through the receiving circuit 130, the beam synthesis module 140, the IQ demodulation module 150, and the velocity calculation module 162.

Step 22: Obtain a Doppler spectrogram of the target sampling position according to the blood flow image data. In a specific embodiment, the processor calculates the hemodynamic information of each point in the blood flow image according to the blood flow image data, and uses the point with the largest value of the hemodynamic information as the target sampling position, according to the echo signal of the first ultrasound. Obtain the Doppler spectrogram at the target sampling position.

Step 23: Obtain the Doppler spectrum envelope of the target sampling position according to the Doppler spectrum diagram.

Step 24: Calculate the velocity time integral VTI of the target sampling position according to the Doppler spectrogram. The calculation method is the same as step 17.

Step 25, output VTI. The output mode can be displayed on the display interface or printed out by a printer.

In an embodiment, hemodynamic information may also be obtained according to the echo of the first ultrasonic wave, and the target sampling position may be obtained subsequently according to the hemodynamic information. For example, as shown in Figure 6, the following steps are included.

Step 30: Control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue, and receive the echo of the first ultrasonic wave returned by the measured tissue.

Step 31: Obtain hemodynamic information according to the echo signal of the first ultrasonic wave. The echo of the first ultrasonic wave is sensed by the ultrasonic probe 110, and hemodynamic information is obtained through the receiving circuit 130, the beam synthesis module 140, the IQ demodulation module 150, and the velocity calculation module 162.

Step 32: Obtain a Doppler spectrogram of the target sampling position according to the hemodynamic information. In a specific embodiment, the processor searches for the position where the hemodynamic information is least disturbed, and uses the position where the hemodynamic information is least disturbed as the target sampling position. In one embodiment, the Doppler spectrogram at the target sampling position can be obtained according to the echo signal of the first ultrasound; in one embodiment, the second ultrasound can be transmitted to the target sampling position according to the Doppler mode to obtain the second ultrasound. According to the ultrasonic echo signal of the second ultrasonic wave, the Doppler spectrogram at the target sampling position is obtained.

Step 33: Obtain the Doppler spectrum envelope at the target sampling position according to the Doppler spectrum map.

Step 34: Calculate the velocity time integral VTI at the target sampling position according to the Doppler spectrum envelope.

Step 35, output VTI.

In one embodiment, the ultrasonic wave may be transmitted first to obtain the Doppler spectrogram in the preset area, the target Doppler spectrogram is determined according to the Doppler spectrogram, and the target Doppler spectrogram package is obtained according to the target Doppler spectrogram. Network to calculate VTI. For example, as shown in Figure 7, it includes the following steps:

Step 40: Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue;

Step 41: Calculate multiple Doppler spectrograms at different positions in the preset area of the first ultrasound according to the ultrasound echo signal of the first ultrasound; the preset area may be the entire scan area, which may be an ROI selected automatically or manually area. Among them, Doppler spectrograms of multiple locations or points in the preset area can be acquired at multiple locations, and Doppler spectrograms of all locations or points in the preset area can also be acquired. It should be understood that the “dot” mentioned here refers to a pixel point in the scanning area or a small area including several pixels, rather than a pure point in a mathematical sense.

Step 42: Determine the target Doppler spectrogram based on the multiple Doppler spectrograms; the target Doppler spectrogram may be determined from the multiple Doppler spectrograms based on satisfying the second preset condition. For example, the target Doppler spectrogram may be selected to have The Doppler spectrogram of the maximum peak spectral velocity is used as the target Doppler spectrogram, or a Doppler spectrogram that meets other conditions can also be selected as the target Doppler spectrogram;

Step 43: Obtain the Doppler spectrum envelope of the target Doppler spectrogram according to the target Doppler spectrogram;

Step 44: Calculate the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Step 45, output VTI.

In the embodiment of the present invention, when evaluating the heart pumping function of the testee, the cardiac output CO is not directly calculated, but the VTI is directly calculated, and the VTI is displayed to the doctor. In this method of evaluating cardiac output CO, since there is no need to estimate the diameter of the subject’s aortic outflow tract, the evaluation is more accurate.

In the embodiment of the present invention, the ultrasonic probe is controlled to transmit ultrasonic waves to the tested tissue and receive the echo of the ultrasonic waves returned by the tested tissue. According to the ultrasonic echo, find the target sampling position with the least interference of hemodynamic information, and then calculate The VTI at the target sampling location. When calculating the VTI, the position where the hemodynamic information of the left ventricular outflow tract is least disturbed is detected by ultrasound, and the VTI of the Doppler spectrum envelope at this position is calculated, so the calculated VTI is subjected to the vascular wall friction It has the least impact and best reflects the heart's pumping ability, and thus best reflects the cardiac output.

This document is described with reference to various exemplary embodiments. However, those skilled in the art will recognize that changes and modifications can be made to the exemplary embodiments without departing from the scope of this document. For example, various operation steps and components used to perform the operation steps can be implemented in different ways according to a specific application or considering any number of cost functions associated with the operation of the system (for example, one or more steps can be deleted, Modify or incorporate into other steps).

In addition, as understood by those skilled in the art, the principles herein can be reflected in a computer program product on a computer-readable storage medium, which is pre-installed with computer-readable program code. Any tangible, non-transitory computer-readable storage medium can be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-ROM, DVD, Blu Ray disks, etc.), flash memory and/or the like . These computer program instructions can be loaded on a general-purpose computer, a special-purpose computer, or other programmable data processing equipment to form a machine, so that these instructions executed on the computer or other programmable data processing device can generate a device that realizes the specified function. These computer program instructions can also be stored in a computer-readable memory, which can instruct a computer or other programmable data processing equipment to operate in a specific manner, so that the instructions stored in the computer-readable memory can form a piece of Manufactured products, including realizing devices that realize designated functions. Computer program instructions can also be loaded on a computer or other programmable data processing equipment, thereby executing a series of operation steps on the computer or other programmable equipment to produce a computer-implemented process, so that the execution of the computer or other programmable equipment Instructions can provide steps for implementing specified functions.

Although the principles herein have been shown in various embodiments, many modifications to the structure, arrangement, proportions, elements, materials, and components that are particularly suitable for specific environments and operating requirements can be made without departing from the principles and scope of this disclosure. use. The above modifications and other changes or amendments will be included in the scope of this article.

The foregoing detailed description has been described with reference to various embodiments. However, those skilled in the art will recognize that various modifications and changes can be made without departing from the scope of this disclosure. Therefore, the consideration of this disclosure will be in an illustrative rather than restrictive sense, and all these modifications will be included in its scope. Likewise, the advantages, other advantages, and solutions to problems of the various embodiments have been described above. However, benefits, advantages, solutions to problems, and any solutions that can produce these or make them more specific should not be construed as critical, necessary, or necessary. The term "including" and any other variants thereof used in this article are non-exclusive inclusions. Such a process, method, article or device that includes a list of elements not only includes these elements, but also includes those that are not explicitly listed or are not part of the process. , Methods, systems, articles or other elements of equipment. In addition, the term "coupled" and any other variations thereof used herein refer to physical connection, electrical connection, magnetic connection, optical connection, communication connection, functional connection and/or any other connection.

Those skilled in the art will recognize that many changes can be made to the details of the above-described embodiments without departing from the basic principles of the present invention. Therefore, the scope of the present invention should be determined according to the following claims.

Claims

A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave, the hemodynamic information is obtained according to the ultrasonic echo signal of the first ultrasonic wave, and the target sampling position is obtained according to the hemodynamic information, and the target sampling position refers to the position where the hemodynamic information is least disturbed The processor is also used to control the ultrasound probe to transmit a second ultrasonic wave to the measured tissue in a Doppler mode through the transmitting circuit, and to receive the second ultrasonic wave returned by the measured tissue through the receiving circuit Wave, obtain the ultrasonic echo signal of the second ultrasonic wave, generate the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave, and obtain the Doppler spectrum according to the Doppler spectrogram The Doppler spectrum envelope of the graph, and calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

The output device (170) is used to output VTI.
The apparatus according to claim 1, wherein the processor is further configured to generate a visualized ultrasound image according to an ultrasound echo signal of the first ultrasound, the ultrasound image including a B image and/or a blood flow image .
The device according to claim 2, wherein the processor is further configured to mark a visualized target sampling position on the ultrasound image.
The device according to claim 2, wherein the processor is further configured to mark a visualized region of interest on the ultrasound image, and mark the visualized target sampling position in the region of interest.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave generates an ultrasonic image based on the ultrasonic echo signal of the first ultrasonic wave, the ultrasonic image includes a B image and/or a blood flow image, the target sampling position is marked on the ultrasonic image, and the target The sampling position is the position where the hemodynamic information in the ultrasound image is least disturbed; the processor is also used to control the ultrasound probe through the transmitting circuit to transmit a second ultrasonic wave to the measured tissue in a Doppler mode, and Receive the echo of the second ultrasonic wave returned by the tested tissue through the receiving circuit, obtain the ultrasonic echo signal of the second ultrasonic wave, and obtain the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave , Obtaining the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and calculating the velocity-time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope ；

The output device (170) is used to output VTI.
5. The device according to claim 5, wherein the output device comprises a display for displaying images and data, the data includes VTI, and the images include ultrasound images and Doppler sampling gates.
The device according to any one of claims 1 to 6, wherein the blood flow force information includes blood flow velocity information and/or energy information.
The device according to claim 7, wherein the processor calculates the blood flow velocity information and/or energy information of each receiving point of the measured tissue according to the ultrasonic echo signal of the first ultrasonic wave, and sets the maximum velocity information The position with the largest position or energy information is used as the target sampling position.
8. The device of any one of claims 1-8, wherein the first ultrasonic wave is a focused wave, a plane wave, or a diverging wave.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave, the blood flow image data is obtained according to the ultrasonic echo signal of the first ultrasonic wave, the target sampling position is obtained according to the blood flow image data, and the ultrasonic echo signal of the first ultrasonic wave is obtained. The Doppler spectrogram at the target sampling position, the Doppler spectrum envelope of the Doppler spectrogram is obtained according to the Doppler spectrogram, and the target sample is calculated according to the Doppler spectrum envelope The velocity time integral VTI of the blood flow at the position; the output device (170) is used to output the VTI.
The device according to claim 10, wherein the processor calculates the hemodynamic information of each point in the blood flow image according to the blood flow image data, and uses the point with the largest value of the hemodynamic information as the target sampling position.
The device according to claim 11, wherein the blood flow force information includes blood flow velocity information and/or energy information.
The device according to claim 12, wherein the processor calculates the blood flow velocity information and/or energy information of each receiving point of the measured tissue according to the ultrasonic echo signal of the first ultrasonic wave, and sets the maximum velocity information The position with the largest position or energy information is used as the target sampling position.
The device according to any one of claims 10-13, wherein the first ultrasonic wave is a focused wave, a plane wave, or a diverging wave.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave, the hemodynamic information is obtained according to the ultrasonic echo signal of the first ultrasonic wave, and the target sampling position is obtained according to the hemodynamic information, and the target sampling position refers to the position where the hemodynamic information is least disturbed The processor also obtains the Doppler spectrogram at the target sampling position, obtains the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and according to the Doppler spectrum Envelope calculation of the velocity time integral VTI of the blood flow at the target sampling position;

The output device (170) is used to output VTI.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave, the hemodynamic information is obtained according to the ultrasonic echo signal of the first ultrasonic wave, and the target sampling position is obtained according to the hemodynamic information. The target sampling position means that the hemodynamic information is disturbed and satisfies the first The position of the preset condition; the processor is also used to control the ultrasound probe to transmit a second ultrasonic wave to the tested tissue in a Doppler mode through the transmitting circuit, and to receive the return from the tested tissue through the receiving circuit The echo of the second ultrasonic wave, the ultrasonic echo signal of the second ultrasonic wave is obtained, the Doppler spectrogram at the target sampling position is generated according to the ultrasonic echo signal of the second ultrasonic wave, and the result is obtained according to the Doppler spectrogram The Doppler spectrum envelope of the Doppler spectrogram, and calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

The output device (170) is used to output VTI.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave generates an ultrasonic image according to the ultrasonic echo signal of the first ultrasonic wave, the ultrasonic image includes a B image and/or a blood flow image, the target sampling position is marked on the ultrasonic image, and the target The sampling position is the position where the hemodynamic information in the ultrasound image is interfered and satisfies the first preset condition; the processor is also used to control the ultrasound probe to transmit to the tissue under test in a Doppler mode through the transmitting circuit The second ultrasonic wave and the echo of the second ultrasonic wave returned from the tested tissue are received through the receiving circuit to obtain the ultrasonic echo signal of the second ultrasonic wave. According to the ultrasonic echo signal of the second ultrasonic wave, the target sampling position is obtained Doppler spectrogram, obtain the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and calculate the blood flow at the target sampling position according to the Doppler spectrum envelope The speed time integral VTI;

The output device (170) is used to output VTI.
A VTI measuring device, which is characterized by comprising:

The ultrasonic probe (110) is used to transmit ultrasonic waves to the measured tissue and receive the echo of the ultrasonic waves returned by the measured tissue;

A transmitting circuit (120), configured to output a corresponding transmitting sequence to the ultrasonic probe according to a set mode, so as to control the ultrasonic probe to transmit corresponding ultrasonic waves;

The receiving circuit (130) is used to control the ultrasonic probe to receive the echo of the ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal;

The beam synthesis module (140) is used to perform beam synthesis on the ultrasonic echo signal;

The processor (160) is configured to control the ultrasonic probe to transmit the first ultrasonic wave to the measured tissue through the transmitting circuit, and to receive the echo of the first ultrasonic wave returned by the measured tissue through the receiving circuit to obtain the first ultrasonic wave. The ultrasonic echo signal of the ultrasonic wave, the hemodynamic information is obtained according to the ultrasonic echo signal of the first ultrasonic wave, and the target sampling position is obtained according to the hemodynamic information. The target sampling position means that the hemodynamic information is disturbed and satisfies the first The position of the preset condition; the processor also obtains the Doppler spectrogram at the target sampling position, obtains the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram, and according to the Calculating the Doppler spectrum envelope to calculate the velocity time integral VTI of the blood flow at the target sampling position;

The output device (170) is used to output VTI.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Obtain hemodynamic information according to the ultrasound echo signal of the first ultrasound;

Obtaining the target sampling position according to the hemodynamic information;

Controlling the ultrasound probe to transmit a second ultrasonic wave to the measured tissue according to the Doppler mode, and receive the echo of the second ultrasonic wave returned by the measured tissue, to obtain an ultrasonic echo signal of the second ultrasonic wave;

Obtain the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Obtaining the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.
The method according to claim 16, further comprising: generating and displaying a visualized ultrasound image according to the ultrasound echo signal of the first ultrasound, the ultrasound image including a B image and/or a blood flow image.
The method according to claim 17, further comprising: marking the visualized target sampling position on the ultrasound image.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Generating an ultrasound image according to the echo of the first ultrasound, the ultrasound image including a B image and/or a blood flow image;

Marking a target sampling location on the ultrasound image, where the target sampling location is a location in the ultrasound image where hemodynamic information is least disturbed;

Controlling the ultrasound probe to transmit a second ultrasonic wave to the measured tissue according to the Doppler mode, and receive the echo of the second ultrasonic wave returned by the measured tissue, to obtain an ultrasonic echo signal of the second ultrasonic wave;

Obtain the Doppler spectrum envelope at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.
A VTI measurement method, which is characterized in that it includes:

Obtain hemodynamic information according to the ultrasonic echo signal of the first ultrasonic wave. The ultrasonic echo signal of the first ultrasonic wave transmits the first ultrasonic wave to the tested tissue by the ultrasonic probe and receives the first ultrasonic wave returned by the tested tissue. Echo

Obtaining the target sampling position according to the hemodynamic information;

Obtain the Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Obtaining the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram;

The velocity time integral VTI of the blood flow at the target sampling position is calculated according to the Doppler spectrum envelope.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Obtain hemodynamic information according to the ultrasound echo signal of the first ultrasound;

Obtaining the target sampling position according to the hemodynamic information;

Acquiring a Doppler spectrogram at the target sampling position according to the ultrasonic echo signal of the first ultrasonic wave;

Obtaining the Doppler spectrum envelope of the Doppler spectrogram according to the Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.
The method according to any one of claims 16 to 21, wherein the blood flow force information includes blood flow velocity information and/or energy information.
The method according to claim 22, wherein the target sampling position is a position with the greatest speed or a position with the greatest energy information.
The method according to any one of claims 16 to 23, wherein the first ultrasonic wave is a focused wave, a plane wave, or a diverging wave.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Calculating Doppler spectrograms at multiple positions in the scanning area of the first ultrasound according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Determining a target Doppler spectrogram from the multiple Doppler spectrograms, where the target Doppler spectrogram has a maximum peak spectral velocity;

Obtaining the Doppler spectrum envelope of the target Doppler spectrogram according to the target Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Output the VTI.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Calculating Doppler spectrograms at multiple positions in the scanning area of the first ultrasound according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Determining, from the multiple Doppler spectrograms, a target Doppler spectrogram that meets the second preset condition;

Obtaining the Doppler spectrum envelope of the target Doppler spectrogram according to the target Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Output the VTI.
The method according to any one of claims 25-26, wherein the first ultrasonic wave is a plane wave or a diverging wave.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Calculating the Doppler spectrogram of each point in the scanning area of the first ultrasonic wave according to the ultrasonic echo signal of the first ultrasonic wave, and obtaining the Doppler spectrogram of each point in the scanning area of the first ultrasonic wave;

Determining a target Doppler spectrogram from the Doppler spectrogram of each point in the scanning area of the first ultrasound, where the target Doppler spectrogram has a maximum peak spectral velocity;

Obtaining the Doppler spectrum envelope of the target Doppler spectrogram according to the target Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Output the VTI.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Generating a first ultrasound image based on the first ultrasound echo signal, and determining a region of interest of the first ultrasound image;

Calculating a Doppler spectrogram of each point in the region of interest of the first ultrasound image according to the ultrasound echo signal of the first ultrasound to obtain multiple Doppler spectrograms;

Determining a target Doppler spectrogram from the multiple Doppler spectrograms, where the target Doppler spectrogram has a maximum peak spectral velocity;

Obtaining the Doppler spectrum envelope of the target Doppler spectrogram according to the target Doppler spectrogram;

Calculating the velocity time integral VTI of the blood flow at the position of the target Doppler spectrogram according to the Doppler spectrum envelope;

Output the VTI.
A VTI measurement method, which is characterized in that it includes:

Control the ultrasonic probe to transmit the first ultrasonic wave to the tested tissue and receive the echo of the first ultrasonic wave returned by the tested tissue to obtain the ultrasonic echo signal of the first ultrasonic wave;

Generating an ultrasound image according to the echo of the first ultrasound, the ultrasound image including a B image and/or a blood flow image;

Marking a target sampling position on the ultrasound image, where the target sampling position is a position in the ultrasound image where hemodynamic information is disturbed and satisfies the first preset condition;

Controlling the ultrasound probe to transmit a second ultrasonic wave to the measured tissue according to the Doppler mode, and receive the echo of the second ultrasonic wave returned by the measured tissue, to obtain an ultrasonic echo signal of the second ultrasonic wave;

Obtain the Doppler spectrum envelope at the target sampling position according to the ultrasonic echo signal of the second ultrasonic wave;

Calculating the velocity time integral VTI of the blood flow at the target sampling position according to the Doppler spectrum envelope;

Output the VTI.
A computer-readable storage medium, characterized by comprising a program, which can be executed by a processor to implement the method according to any one of claims 16-29.
A method for evaluating the pumping function of the heart, characterized in that the VTI obtained by using the device according to any one of claims 1-15 or the method according to any one of claims 16-29 has an effect on the pumping function of the heart. Make an evaluation.