A tachycardia diagnosis and treatment device

Abstract

The present application discloses a tachycardia diagnosis and treatment device, which includes an ultrasonic transducer module, a control module, a strain rate module, a three-dimensional imaging module, a spiral wave endpoint positioning module, and a diagnosis module. The ultrasonic transducer module emits ultrasonic waves and receives echo signals. The control module generates three-dimensional displacement field data through the echo signals. After calculating the strain rate by the strain rate module, it is stored by the three-dimensional imaging module and mapped into three-dimensional data. The spiral wave endpoint positioning module obtains an effective endpoint set through sub-image detection and clustering screening. The diagnosis module determines tachycardia based on a preset threshold, triggers the phased array module to generate a treatment instruction containing sound intensity, phase, and position information, and finally the ultrasonic transducer module realizes precise focusing treatment. Through non-invasive ultrasonic technology, multi-module collaborative processing, and real-time data feedback, non-invasive diagnosis of tachycardia is achieved, with both precision and safety.

Description

Technical Field

[0001] The present application relates to the technical field of ultrasonic diagnosis and treatment, and particularly relates to a tachycardia diagnosis and treatment device. Background Art

[0002] Spiral wave electrical signals are the main generation mechanism of tachycardia. Clinically, if the spiral wave electrical signals in the target area can be detected and eliminated in time, tachycardia can be effectively treated.

[0003] Currently, implantable cardioverter defibrillators (ICDs) are generally used to treat tachycardia. The ICD effectively eliminates spiral waves and turbulence by stimulating with a large voltage, causing all myocardial cells to depolarize rapidly simultaneously, achieving the effect of treating tachycardia.

[0004] However, the ICD needs to be implanted into the patient's body, which is likely to cause rejection in the patient's body, has a high cost, and has relatively large potential safety hazards to the body due to the electric shock stimulation.

[0005] Therefore, how to ensure the accuracy and safety of treatment is an urgent problem to be solved. Summary of the Invention

[0006] In view of this, a tachycardia diagnosis and treatment device provided by an embodiment of the present application can reduce the treatment cost and ensure the safety of treatment. The tachycardia diagnosis and treatment device provided by an embodiment of the present application is implemented as follows:

[0007] A tachycardia diagnosis and treatment device provided by an embodiment of the present application includes an ultrasonic transducer module, a control module, a strain rate module, a three-dimensional imaging module, a spiral wave endpoint positioning module, and a diagnosis module that are connected in sequence. The diagnosis module is also connected to the control module, wherein:

[0008] The ultrasonic transducer module is configured to emit ultrasonic waves after receiving the emission signal sent by the control module, and receive the echo signal after the ultrasonic waves are reflected by the target area, and send the echo signal to the control module;

[0009] The control module is configured to send the emission signal to the ultrasonic transducer module and receive the echo signal, generate three-dimensional displacement field data corresponding to the target area according to the echo signal, and send the three-dimensional displacement field data to the strain rate module;

[0010] The strain rate module is configured to perform deformation tensor calculation on the received three-dimensional displacement field data to obtain a strain rate, and send the strain rate to the three-dimensional imaging module;

[0011] The three-dimensional imaging module is configured to obtain a strain rate data set based on the received strain rate, perform three-dimensional mapping on the strain rate data set to obtain three-dimensional imaging data, and send the three-dimensional imaging data to the spiral wave endpoint localization module;

[0012] The spiral wave endpoint localization module is configured to generate a plurality of sub-images based on the received three-dimensional imaging data, perform spiral wave endpoint detection on the plurality of sub-images to obtain the spiral wave endpoints of the plurality of sub-images, perform clustering and screening on the spiral wave endpoints of the plurality of sub-images to obtain a filtered set of spiral wave endpoints, and send the filtered set of spiral wave endpoints to the diagnostic module;

[0013] The diagnostic module is configured to determine whether tachycardia exists in the target region based on a preset frequency threshold and the received filtered set of spiral wave endpoints; when tachycardia exists in the target region, the diagnostic module sends a treatment instruction and the filtered set of spiral wave endpoints to the control module;

[0014] The control module is further configured to generate control information based on the received filtered set of spiral wave endpoints after receiving the treatment instruction from the control module, and send the control information to the ultrasonic transducer module, where the control information includes the sound intensity, phase of the ultrasonic wave, and the position of the spiral wave endpoint;

[0015] The ultrasonic transducer module is further configured to adjust the sound intensity and phase of the ultrasonic wave according to the received control information and then emit the ultrasonic wave towards the target region to perform ultrasonic focusing on the position of the spiral wave endpoint.

[0016] In some embodiments, the strain rate module includes a first receiving unit, a first calculating unit, a conversion unit, and a first sending unit that are connected in sequence. The strain rate module and the three-dimensional imaging module are as follows;

[0017] The first receiving unit is configured to receive the three-dimensional displacement field data from the control module;

[0018] The first calculating unit is configured to perform deformation tensor calculation on the three-dimensional displacement field data to obtain a gradient deformation tensor and a Green-Lagrange strain tensor; perform eigenvalue decomposition and invariant combination operations on the gradient deformation tensor and the Green-Lagrange strain tensor respectively to obtain the tensor invariants of the target region;

[0019] The conversion unit is configured to perform strain rate conversion on the tensor invariants to obtain the strain rate of the target region;

[0020] The first sending unit is configured to send the strain rate of the target region to the three-dimensional imaging module.

[0021] In some embodiments, the spiral wave endpoint positioning module includes a second receiving unit, a building unit, a cutting unit, a second calculation unit, a screening unit, and a second sending unit diagnostic module that are connected in sequence, where;

[0022] The second receiving unit is configured to receive the three-dimensional imaging data of the three-dimensional imaging module;

[0023] The building unit is configured to establish a three-dimensional rectangular coordinate system based on the three-dimensional imaging data;

[0024] The cutting unit is configured to cut the three-dimensional imaging data perpendicular to the coordinate axes along the x, y, and z axes of the three-dimensional rectangular coordinate system to generate a plurality of sub-images;

[0025] The second calculation unit is configured to use the Moore neighborhood tracking algorithm for each of the plurality of sub-images to obtain the intersection line between the foreground and the background in each sub-image, where the foreground is the area in the sub-image containing the spiral wave, and the background is the area in the sub-image without the spiral wave; when the intersection line meets a preset curvature threshold, the spiral wave endpoints of the sub-image corresponding to the intersection line are obtained by fitting the curvature circle algorithm;

[0026] The screening unit is configured to perform clustering screening on the spiral wave endpoints of the plurality of sub-images to obtain a screened set of spiral wave endpoints;

[0027] The second sending unit is configured to send the screened set of spiral wave endpoints to the diagnostic module.

[0028] In some embodiments, the screening unit includes an obtaining element and a screening-out element that are connected in sequence, where;

[0029] The obtaining element is configured to obtain the corresponding plurality of spiral wave endpoints in the plurality of sub-images to obtain an initial set of spiral wave endpoints;

[0030] The screening-out element is configured to perform a screening process on the spiral wave endpoints in the initial set of spiral wave endpoints whose standard deviation of the spatial distribution exceeds a preset distance threshold to obtain a screened set of spiral wave endpoints.

[0031] In some embodiments, the preset distance threshold is 0.5 mm.

[0032] In some embodiments, the ultrasonic transducer module includes at least two groups of ultrasonic transducers.

[0033] In some embodiments, the operating frequency range of the ultrasonic transducer is 1 MHz to 10 MHz.

[0034] In some embodiments, the time of ultrasonic focusing is 20 ms.

[0035] In some embodiments, the preset frequency threshold is the occurrence frequency of the endpoints of spiral waves at 85%.

[0036] In some embodiments, the imaging interval time of the three-dimensional mapping is 10 ms.

[0037] A tachycardia diagnosis and treatment device provided by an embodiment of the present application includes an ultrasonic transducer module, a control module, a strain rate module, a three-dimensional imaging module, a spiral wave endpoint positioning module, and a diagnosis module. The ultrasonic transducer module emits ultrasonic waves and receives echo signals. The control module generates three-dimensional displacement field data through the echo signals. After calculating the strain rate by the strain rate module, the three-dimensional imaging module stores and maps it into three-dimensional data. The spiral wave endpoint positioning module obtains a set of effective endpoints through sub-image detection and clustering screening. The diagnosis module determines tachycardia based on a preset threshold, triggers the phased array module to generate a treatment instruction including sound intensity, phase, and position information, and finally the ultrasonic transducer module realizes precise focused treatment. Through non-invasive ultrasonic technology, multi-module collaborative processing, and real-time data feedback, non-invasive diagnosis of tachycardia is achieved, with both accuracy and safety. The technical problems proposed in the background art are solved. Description of the Drawings

[0038] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following will briefly introduce the drawings required for the description of the embodiments of the present application or the prior art. Obviously, the drawings in the following description are some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0039] Figure 1 It is a device structure diagram of a tachycardia diagnosis and treatment device provided by an embodiment of the present application;

[0040] Figure 2 It is a device structure diagram of another tachycardia diagnosis and treatment device provided by an embodiment of the present application;

[0041] Figure 3 It is a device structure diagram of another tachycardia diagnosis and treatment device provided by an embodiment of the present application;

[0042] Figure 4 It is a device structure diagram of another tachycardia diagnosis and treatment device provided by an embodiment of the present application. Detailed Embodiments

[0043] To make the objectives, technical solutions, and advantages of the embodiments of the present application clearer, the following will further describe the specific technical solutions of the present application in detail with reference to the drawings in the embodiments of the present application. The following embodiments are used to illustrate the present application but are not used to limit the scope of the present application.

[0044] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terms used herein are for the purpose of describing embodiments of this application only and are not intended to limit this application.

[0045] In the following description, reference is made to "some embodiments", which describe a subset of all possible embodiments. However, it can be understood that "some embodiments" can be the same subset or different subsets of all possible embodiments and can be combined with each other without conflict.

[0046] It should be noted that the terms "first / second / third" involved in the embodiments of this application are used to distinguish similar or different objects and do not represent a specific order for the objects. It can be understood that "first / second / third" can be interchanged in a specific order or sequence when permitted, so that the embodiments of this application described here can be implemented in an order other than that illustrated or described here.

[0047] In view of this, the embodiments of this application provide a device structure diagram of a tachycardia diagnosis and treatment device, as Figure 1 shown, including an ultrasonic transducer module 101, a control module 102, a strain rate module 103, a three-dimensional imaging module 104, a spiral wave endpoint localization module 105, and a diagnosis module 106 connected in sequence. The diagnosis module 106 is also connected to the control module 102, where:

[0048] The ultrasonic transducer module 101 is configured to emit ultrasonic waves after receiving the transmission signal sent by the control module, and receive the echo signal after the ultrasonic waves are reflected by the target area, and send the echo signal to the control module.

[0049] In the embodiments of this application, the ultrasonic transducer module 101 can be a transducer array composed of multiple piezoelectric ceramic elements. Each element can convert an electrical signal into an ultrasonic signal and emit it, receive the echo signal after the ultrasonic signal is reflected by the target area, and can also convert the received ultrasonic wave into an electrical signal. The control module 102 generates a transmission signal, and this signal determines key parameters such as the frequency, amplitude, and phase of the ultrasonic wave emission. In this application, the operating frequency range of the ultrasonic transducer can be set to 1 MHz to 10 MHz. For example, the transmission frequency is set to 5 MHz. This frequency can not only ensure the effective penetration of ultrasonic waves into human tissues but also obtain a relatively clear image of the target area; the amplitude is set to an appropriate value, such as 10 Vpp, after calibration according to the patient's physical condition and imaging depth requirements, to ensure that the emitted ultrasonic waves have sufficient energy to reach the target area. In this application, there are at least two groups of ultrasonic transducers.

[0050] The control module 102 is connected to the ultrasonic transducer module 101 through a high-speed data line, and accurately transmits the transmission signal to the ultrasonic transducer module 101. The drive circuit in the ultrasonic transducer module 101 amplifies the received transmission signal in power to ensure that the signal can effectively drive the piezoelectric ceramic elements. Then, according to the timing control information in the transmission signal, the drive circuit sequentially triggers each piezoelectric ceramic element in the transducer array. For example, for imaging of the target area, a linear scanning mode can be adopted, that is, the piezoelectric ceramic elements arranged linearly are sequentially triggered in order, so that the ultrasonic waves generated by them are superimposed to form a beam with a specific directivity, and the beam is focused on a specific area of the target area to ensure the accuracy and clarity of imaging.

[0051] The control module 102 is used to send a transmission signal to the ultrasonic transducer module 101 and receive an echo signal, generate three-dimensional displacement field data of the target area according to the echo signal, and send the three-dimensional displacement field data to the strain rate module 103.

[0052] In the embodiment of the present application, the control module 102 determines the parameters of the transmission signal according to the requirements of tachycardia diagnosis and treatment and a preset scanning scheme, so as to balance the penetration depth and imaging resolution of ultrasonic waves.

[0053] Through digital beamforming technology, the control module 102 precisely controls the transmission signal of each array element. By calculating the delay time and phase of different array elements, the transmitted ultrasonic waves are focused on a specific area of the target area in space. For example, using a phased array algorithm, according to the approximate position and depth of the target area, the transmission time of each array element is adjusted so that the ultrasonic waves form a focal point at the target position, improving the clarity of imaging.

[0054] Through a high-speed data transmission interface, the control module 102 sends the generated transmission signal to the ultrasonic transducer module 101. After receiving the echo signal reflected from the target area, the control module 102 preprocesses the echo signal and then performs acquisition.

[0055] The control module 102 analyzes the preprocessed echo signal and reconstructs a three-dimensional image of the target area using ultrasonic imaging algorithms (such as synthetic aperture imaging algorithm, coherent plane wave imaging algorithm, etc.). In this process, by comparing the phase and amplitude changes of the echo signals at different times, the displacement information of the target area tissue is determined.

[0056] According to the displacement information obtained by analyzing the echo signal, the control module 102 calculates the displacement field of the target area in three-dimensional space. The cross-correlation algorithm or phase difference algorithm can be used to calculate the displacement of the tissue. For example, by calculating the cross-correlation coefficient of the corresponding points in two adjacent frames of images, the maximum correlation point is found, thereby determining the displacement of the tissue. Integrating the displacement information at different positions, the three-dimensional displacement field data of the target area is obtained.

[0057] The control module 102 sends the generated three-dimensional displacement field data of the target area to the strain rate module 103 through the data transmission interface.

[0058] The strain rate module 103 is used to calculate the deformation tensor for the received three-dimensional displacement field data to obtain the strain rate, and send the strain rate to the three-dimensional imaging module 104.

[0059] In the embodiment of the present application, the strain rate module 103 receives the three-dimensional displacement field data through the data transmission interface with the control module 102.

[0060] In order to make the three-dimensional displacement field data more continuous in space and facilitate subsequent calculations, interpolation processing can also be performed on the three-dimensional displacement field data in the present application. Common interpolation methods include linear interpolation, cubic spline interpolation, etc. Through interpolation processing, reasonable displacement values can be estimated between data points, improving the resolution of the data.

[0061] The strain rate module 103 calculates the deformation tensor of the target area using the deformation tensor calculation formula according to the relevant theories in continuum mechanics. For an object in three-dimensional space, the deformation tensor is a second-order tensor, usually represented by a 3×3 matrix. Its calculation is based on the spatial derivatives of the displacement field data. For example, the partial derivatives of the displacement field in the x, y, and z directions constitute the elements of the deformation tensor.

[0062] In actual calculations, since the displacement field data is discrete, numerical difference methods need to be used to approximately calculate the derivatives of the displacement field. For example, the central difference method is used to calculate the first-order partial derivatives, and the derivative values are estimated through the displacement differences between adjacent data points.

[0063] According to the relationship between the deformation tensor and the strain rate, the strain rate module 103 calculates the strain rate of the target area. The strain rate describes the deformation speed of an object per unit time, and it is related to the time derivative of the deformation tensor. In actual calculations, the strain rate can be obtained by performing difference calculations on the deformation tensors at different times.

[0064] The strain rate usually includes multiple components, such as longitudinal strain rate, transverse strain rate, and shear strain rate, etc. The strain rate module 103 calculates these components respectively to comprehensively describe the deformation of the target area. For example, the longitudinal strain rate reflects the stretching or compression speed of the target area tissue in the long axis direction, the transverse strain rate reflects the deformation speed in the short axis direction, and the shear strain rate reflects the degree of shear deformation of the tissue.

[0065] The strain rate module 103 sends the calculated strain rate data of the target area to the three-dimensional imaging module 104 through the data transmission interface.

[0066] A three-dimensional imaging module 104 is configured to obtain a strain rate data set based on the received strain rate, perform three-dimensional mapping on the strain rate data set to obtain three-dimensional imaging data, and send the three-dimensional imaging data to a spiral wave endpoint localization module 105.

[0067] In an embodiment of the present application, the three-dimensional imaging module 104 may receive strain rate data of a target area at different times from the strain rate module 103 according to a preset time interval. Specifically, the preset time interval in the present application is 10 ms. It may also be to obtain all the strain rate data, and the present application does not make a limitation here. The three-dimensional imaging module 104 is connected to the strain rate module 103 through a high-speed and stable data transmission interface.

[0068] The three-dimensional imaging module 104 may set up a dedicated database to store the collected strain rate data. The database adopts an efficient data structure, such as a relational database (such as MySQL) or a non-relational database (such as MongoDB), to optimize the storage and query efficiency of the data.

[0069] Organize the data according to time sequence and spatial position, and each strain rate data point will be associated with its corresponding timestamp and three-dimensional spatial coordinates.

[0070] Divide the three-dimensional space where the target area is located into regular grids, such as cubic grids. Each grid cell has a unique coordinate identifier, corresponding to a specific area within the target area.

[0071] For each grid cell, calculate the strain rate value of the grid cell according to the existing strain rate data points around it using an interpolation algorithm (such as trilinear interpolation). In this way, the discrete strain rate data points are extended to a continuous three-dimensional strain rate distribution.

[0072] Map the calculated strain rate value of each grid cell to the corresponding position in the three-dimensional space to form three-dimensional imaging data of the strain rate data set. This three-dimensional imaging data can intuitively display the strain rate distribution of the target area at different times.

[0073] After completing the three-dimensional mapping, the three-dimensional imaging module 104 will send the generated three-dimensional imaging data to the spiral wave endpoint localization module 105.

[0074] A spiral wave endpoint localization module 105 is configured to generate multiple sub-images based on the received three-dimensional imaging data, perform spiral wave endpoint detection on the multiple sub-images to obtain spiral wave endpoints of the multiple sub-images, perform clustering and screening on the spiral wave endpoints of the multiple sub-images to obtain a screened set of spiral wave endpoints, and send the screened set of spiral wave endpoints to a diagnosis module 106.

[0075] In the embodiments of the present application, the spiral wave endpoint localization module 105 is connected to the three-dimensional imaging module 104 through a high-speed and stable data interface to receive three-dimensional imaging data.

[0076] According to the anatomical structure and imaging characteristics of the target area, the three-dimensional imaging data is segmented according to certain rules. For example, it can be divided into cube sub-blocks of the same size according to spatial position, and each sub-block corresponds to a sub-image. It can also be segmented according to the functional characteristics of different regions of the target area, such as the atrium, ventricle, etc.

[0077] Reasonably set the size and overlap rate of the sub-images. If the sub-image is too large, it may lead to inaccurate detection of spiral wave endpoints; if it is too small, the computational complexity will increase. Generally, the size of the sub-image can be set to a side length of 10 - 20 voxels, and the overlap rate can be set to 10% - 30% to ensure the continuity of information between adjacent sub-images.

[0078] Extract features related to spiral wave endpoints, such as phase gradient, curvature, etc. for each sub-image. For example, by calculating the phase values of each point in the image, the phase gradient can be obtained, and there are usually obvious changes in the phase gradient at the spiral wave endpoints.

[0079] Adopt a special detection algorithm to identify spiral wave endpoints, such as an algorithm based on phase singularity detection. This algorithm analyzes the continuity of the phase in the sub-image and finds the points where the phase undergoes a 2π jump, and these points are the possible spiral wave endpoints.

[0080] Use a clustering algorithm (such as a density-based clustering algorithm) to cluster the spiral wave endpoints detected in all sub-images. The density-based clustering algorithm can divide them into different clusters according to the distance and density between the endpoints.

[0081] Set screening criteria to remove noise points and misdetected points. For example, for clusters with too few points, they can be considered as clusters composed of noise points and be removed; at the same time, remove the endpoints located at the image edge or in positions that do not conform to physiological characteristics.

[0082] Send the set of screened spiral wave endpoints to the diagnostic module in a specific data format.

[0083] The diagnostic module 106 is used to determine whether tachycardia exists in the target area according to a preset frequency threshold and the received set of screened spiral wave endpoints; when tachycardia exists in the target area, the diagnostic module sends a treatment instruction and the set of screened spiral wave endpoints to the control module.

[0084] In the embodiments of the present application, the diagnostic module is connected to the spiral wave endpoint localization module 105 through a reliable data transmission channel to receive the set of screened spiral wave endpoints.

[0085] Preset a period for counting the occurrence frequency of spiral wave endpoints, for example, set it to 1 second. This period duration can effectively capture the dynamic changes of spiral wave endpoints, reflect the immediate electrophysiological state of the target area, and will not cause misjudgment due to being too long or too short.

[0086] During the preset period, the diagnostic module monitors and counts the received set of spiral wave endpoints in real time. Whenever a new spiral wave endpoint data point enters the set, the corresponding counter is incremented by 1. As time progresses, based on the accumulated value of the counter and the preset period duration, according to the formula "frequency = number of endpoint occurrences ÷ preset period", the occurrence frequency of spiral wave endpoints is accurately calculated.

[0087] Compare the calculated occurrence frequency of spiral wave endpoints with the preset frequency threshold. In this application, if the occurrence frequency of spiral wave endpoints is greater than 85% in three consecutive heartbeat cycles, it means that the electrical activity disorder in the target area is relatively frequent, and it is sufficient to determine that tachycardia exists in the target area; conversely, if it is less than or equal to the threshold, it is determined that tachycardia does not exist in the target area and it is in a relatively normal rhythm state, and there is no need to send a treatment instruction and the filtered set of spiral wave endpoints to the control module 102.

[0088] Once the judgment is completed, the diagnostic module immediately outputs the judgment result in a standardized data format (such as a boolean value, "true" indicates the existence of tachycardia, "false" indicates the non-existence). This result can be directly called by other modules (such as the control module 102) in the subsequent diagnosis and treatment process to quickly initiate corresponding treatment or monitoring strategies.

[0089] After the diagnostic module determines that tachycardia exists in the target area, it will perform an internal verification of the judgment result again to ensure the accuracy of the judgment. At the same time, organize and screen the data of the set of spiral wave endpoints, check the integrity and accuracy of the data, and perform necessary format conversion and encoding on the data so that it can be stably transmitted between modules.

[0090] The diagnostic module generates a treatment instruction according to the preset treatment plan and the specific situation of the current tachycardia. The treatment instruction contains various key information, such as the start time of treatment, duration, approximate energy intensity range of ultrasonic waves, etc. For example, for mild tachycardia, the treatment duration may be set to 10 seconds and the ultrasonic energy intensity is at a medium level; for a more serious situation, the treatment duration may be extended to 20 seconds and the energy intensity is correspondingly increased.

[0091] Package the generated treatment instruction and the filtered set of spiral wave endpoints to form a complete data packet. Send the data packet to the control module 102 through a stable and reliable data transmission channel.

[0092] The control module 102 is further configured to generate control information according to the received filtered set of spiral wave endpoints after receiving a treatment instruction from the control module, and send the control information to the ultrasonic transducer module 101. The control information includes the sound intensity, phase of the ultrasonic wave, and the position of the spiral wave endpoints.

[0093] In the embodiment of the present application, the control module 102 receives a data packet from the diagnostic module through an internal high-speed data bus. The data packet contains a treatment instruction and a filtered set of spiral wave endpoints.

[0094] The control module 102 matches the most suitable treatment plan from a preset treatment plan database according to the parameters in the received treatment instruction (such as treatment start time, duration, approximate energy intensity range). For example, if the treatment instruction indicates mild tachycardia, and the set treatment duration is 10 seconds and the energy intensity is at a medium level, the module will select the corresponding detailed treatment parameter combination.

[0095] Based on the positions of the endpoints in the filtered set of spiral wave endpoints and the severity of the tachycardia, combined with the matched treatment plan, accurately calculate the ultrasonic sound intensity required for each ultrasonic transducer element. For endpoints close to key parts of the target area or in areas with more severe tachycardia, the sound intensity can be appropriately increased.

[0096] In order to enable the ultrasonic wave to accurately focus on the spiral wave endpoint position, the control module 102 uses the phased array principle to calculate the phase of the ultrasonic wave emitted by each element according to the three-dimensional spatial position of the endpoint and the layout of the ultrasonic transducer elements. By precisely adjusting the phase, the ultrasonic waves emitted by each element are in-phase superimposed at the spiral wave endpoint to enhance the focusing effect.

[0097] Associate the calculated sound intensity, phase with the specific position information of the spiral wave endpoints to form a complete set of treatment control information. Each spiral wave endpoint corresponds to a specific set of sound intensity, phase, and position parameters.

[0098] Organize and encapsulate the generated treatment control information in a format recognizable by the ultrasonic transducer module 101. Then send the data packet to the ultrasonic transducer module 101 through a high-speed data interface.

[0099] The ultrasonic transducer module 101 is configured to adjust the sound intensity and phase of the ultrasonic wave according to the received control information and then emit the ultrasonic wave towards the target area to perform ultrasonic focusing on the position of the spiral wave endpoints. In the present application, the ultrasonic focusing time can be set to 20 ms.

[0100] In the embodiment of the present application, the ultrasonic transducer module 101 receives the treatment control information data packet sent by the control module 102 through a high-speed data interface and parses the treatment control information data packet.

[0101] The power adjustment circuit inside the ultrasonic transducer module 101 precisely adjusts the amplitude of the driving signal for each ultrasonic transducer element according to the parsed sound intensity information. For example, by changing the gain of the power amplifier, the sound intensity of the ultrasonic waves emitted by each element meets the requirements of the treatment control information. Meanwhile, a real-time monitoring and feedback mechanism is adopted to ensure the stability and accuracy of the sound intensity.

[0102] Using the phase control circuit, according to the parsed phase information, the phase of the driving signal for each ultrasonic transducer element is adjusted. By controlling the delay time of the signal, precise phase adjustment is achieved to ensure that the ultrasonic waves emitted by each element are in-phase superimposed at the spiral wave endpoint position.

[0103] The ultrasonic transducer module 101, based on the position information of the spiral wave endpoint, adopts a phased array focusing algorithm to coordinate the emission time and parameters of each ultrasonic transducer element. So that the ultrasonic waves emitted by all elements are focused in space to the specified spiral wave endpoint position, forming a high-intensity ultrasonic beam.

[0104] During the process of emitting ultrasonic waves, the ultrasonic transducer module 101 monitors the emission state in real time, including parameters such as sound intensity, phase, emission frequency, etc. If it is found that the parameters deviate from the preset values, adjustments are made in a timely manner to ensure the ultrasonic focusing effect on the spiral wave endpoint. At the same time, according to the parameters such as the treatment start time and duration specified in the treatment instruction, the emission duration of the ultrasonic waves is precisely controlled.

[0105] The embodiment of this application realizes non-invasive diagnosis and treatment through the full-process ultrasonic technology, avoiding the risks of invasive methods. Through three-dimensional displacement field, strain rate analysis, and spiral wave endpoint clustering screening, the target area is accurately located and the tachycardia is quantitatively diagnosed. Multi-module collaborative processing and real-time data feedback are used to achieve non-invasive diagnosis of tachycardia, with both accuracy and safety.

[0106] In the above Figure 1 shown situation, the embodiment of this application also provides a device structure diagram of a tachycardia diagnosis and treatment device. As Figure 2 shown, the strain rate module 103 includes a first receiving unit 1031, a first calculation unit 1032, a conversion unit 1033, and a first sending unit 1034 connected in sequence, where:

[0107] The first receiving unit 1031 is used to receive the three-dimensional displacement field data sent by the control module 102.

[0108] In the embodiment of this application, the first receiving unit 1031 receives the three-dimensional displacement field data through the high-speed data interface with the control module 102.

[0109] The first calculation unit 1032 is configured to calculate the deformation tensor for the three-dimensional displacement field data to obtain the gradient deformation tensor and the Green-Lagrange strain tensor; perform eigenvalue decomposition and invariant combination operations on the gradient deformation tensor and the Green-Lagrange strain tensor respectively to obtain the tensor invariants of the target region.

[0110] In the embodiment of the present application, the first calculation unit 1032 performs spatial derivative calculation on the three-dimensional displacement field data to obtain the gradient deformation tensor. In actual calculation, since the displacement field data is discrete, numerical difference methods are usually used to approximately calculate the derivative. For example, the central difference method is used to calculate the first-order partial derivatives of the displacement field in each direction, and these partial derivatives constitute the elements of the gradient deformation tensor. For a three-dimensional space, the gradient deformation tensor is a 3×3 matrix, and its elements reflect the change rate of the displacement field in different directions.

[0111] According to the gradient deformation tensor, the calculation is performed using the calculation formula of the Green-Lagrange strain tensor. The Green-Lagrange strain tensor is a symmetric second-order tensor that describes the strain state of an object during the deformation process and takes into account the geometric relationship before and after the object's deformation. The calculation formula involves the product and summation operations of the gradient deformation tensor, and by performing specific combinations and operations on the elements of the gradient deformation tensor, each element of the Green-Lagrange strain tensor is obtained.

[0112] The first calculation unit 1032 performs eigenvalue decomposition on the calculated gradient deformation tensor and Green-Lagrange strain tensor respectively. The process of decomposing the tensor into eigenvalues and eigenvectors, where the eigenvalues reflect the stretching or deformation degree of the tensor in different directions, and the eigenvectors represent these directions. Through eigenvalue decomposition, the principal strains and principal strain directions of the tensor can be obtained, providing important information for subsequent analysis.

[0113] According to the results obtained from the eigenvalue decomposition, invariant combination operations are performed. The invariants of a tensor refer to the quantities that remain unchanged under coordinate system transformation and reflect the inherent characteristics of the tensor. For a second-order tensor, there are three basic invariants, and by performing specific combination operations (such as summation, multiplication, etc.) on the eigenvalues, the invariants can be obtained. These invariants can comprehensively reflect the deformation characteristics of the target region tissue and provide a basis for subsequent strain rate calculation.

[0114] The conversion unit 1033 is configured to perform strain rate conversion on the tensor invariants to obtain the strain rate of the target region.

[0115] In the embodiments of the present application, the conversion unit 1033 performs strain rate conversion according to the obtained tensor invariants by using a pre-established strain rate conversion model or formula. For example, the generalized Maxwell model or the Kelvin-Voigt model can be adopted to relate stress, strain, and strain rate, and the strain rate is solved through the known tensor invariants.

[0116] Taking the generalized Maxwell model as an example, this model is composed of multiple Maxwell units connected in series, and each Maxwell unit contains a spring and a damper. Through mechanical analysis of the model, the relational expression of stress-strain-strain rate can be obtained. Given the material parameters of the tissue in the target area and the tensor invariants calculated through the previous steps, substituting them into the constitutive equation, the strain rate can be obtained.

[0117] The first sending unit 1034 is configured to send the strain rate of the target area to the three-dimensional imaging module 104.

[0118] In the embodiments of the present application, the first sending unit 1034 formats the calculated strain rate data of the target area to meet the receiving requirements of the three-dimensional imaging module 104. Then, the strain rate data is sent to the three-dimensional imaging module 104 through the data transmission interface.

[0119] In the embodiments of the present application, through the calculation of the deformation tensor, the deformation of the tissue in the target area is accurately described, providing an accurate quantitative basis for diagnosis and treatment. The eigenvalue decomposition and invariant combination operation yield tensor invariants, mining the deep essential features of the deformation in the target area, stably and reliably assisting in diagnosis, and being unaffected by measurement conditions.

[0120] In the above Figure 2 shown case, the embodiments of the present application further provide a tachycardia diagnosis and treatment device diagram. As Figure 3 shown, the spiral wave endpoint positioning module 105 includes a second receiving unit 1051, an establishing unit 1052, a cutting unit 1053, a second calculating unit 1054, a screening unit 1055, and a second sending unit 1056 that are connected in sequence, where:

[0121] The second receiving unit 1051 is configured to receive the three-dimensional imaging data sent by the three-dimensional imaging module 104.

[0122] In the embodiments of the present application, the second receiving unit 1051 is connected to the three-dimensional imaging module 104 through a high-speed and stable data transmission interface to receive the three-dimensional imaging data sent by it.

[0123] The establishing unit 1052 is configured to establish a three-dimensional rectangular coordinate system according to the three-dimensional imaging data.

[0124] In an embodiment of the present application, the establishment unit 1052 establishes a three-dimensional rectangular coordinate system inside the module according to the characteristics of the three-dimensional imaging data and the general anatomical structure of the target area. Taking a fixed point in the target area (such as the center of the target area or a specific anatomical landmark point) as the origin of the coordinate system, the directions of the x, y, and z axes are determined. For example, the long axis direction of the target area is set as the x axis, the short axis direction is set as the y axis, and the direction perpendicular to the plane of the target area is set as the z axis.

[0125] The cutting unit 1053 is configured to cut the three-dimensional imaging data perpendicular to the coordinate axes along the x, y, and z axes of the three-dimensional rectangular coordinate system, generating a plurality of sub-images.

[0126] In an embodiment of the present application, the cutting unit 1053 cuts the three-dimensional imaging data perpendicular to the coordinate axes along the x, y, and z axes of the established three-dimensional rectangular coordinate system. When cutting, a suitable cutting interval is set according to the actual requirements and the limitation of computing resources. For example, cutting is performed every 5 voxels (or adjusted according to the imaging resolution and data volume), so as to divide the three-dimensional imaging data into a plurality of sub-images with the same or similar sizes. Each sub-image contains the imaging information of a part of the target area, which is convenient for subsequent detailed detection of the spiral wave endpoints.

[0127] The second calculation unit 1054 is configured to use the Moore neighborhood tracking algorithm for each of the plurality of sub-images to obtain the intersection line between the foreground and the background in each sub-image, where the foreground is the area in the sub-image containing the spiral wave, and the background is the area in the sub-image without the spiral wave; when the intersection line meets a preset curvature threshold, the spiral wave endpoints of the sub-image corresponding to the intersection line are obtained through the fitting curvature circle algorithm.

[0128] In an embodiment of the present application, for each generated sub-image, the second calculation unit 1054 applies the Moore neighborhood tracking algorithm to determine the intersection line between the foreground (the area containing the spiral wave) and the background (the area without the spiral wave) therein. Specifically, first, a starting point is selected in the sub-image, usually an edge point or a point with obvious features is selected as the starting point. Then, according to the rules of Moore neighborhood tracking, the neighboring points around the starting point (such as 8-neighborhood or 4-neighborhood) are sequentially checked, and it is determined whether the neighboring point belongs to the foreground or the background according to a preset gray value or other feature thresholds. The boundary between the foreground and the background is traced point by point until the starting point is returned, thereby obtaining the complete intersection line.

[0129] After the second calculation unit 1054 obtains the intersection lines between the foreground and the background in each sub-image, it calculates the curvature of each point on the intersection lines. By setting a preset curvature threshold, the points on the intersection lines whose curvatures satisfy the threshold are screened out. For these qualified points, the fitting curvature circle algorithm is used, that is, with this point as the center, by fitting the points within a certain range around it, an approximate curvature circle is obtained. The center of this curvature circle is the corresponding spiral wave endpoint. In this way, the spiral wave endpoints can be accurately extracted from the intersection lines.

[0130] The screening unit 1055 is used to cluster and screen the spiral wave endpoints of multiple sub-images to obtain a set of screened spiral wave endpoints.

[0131] In the embodiment of the present application, the screening unit 1055 performs clustering and screening on all the spiral wave endpoints obtained from multiple sub-images. Using a clustering algorithm, according to the spatial distance and density distribution between the spiral wave endpoints, they are divided into different clusters. Appropriate clustering parameters (such as the neighborhood radius and the minimum number of points) are set to remove noise points and isolated points (that is, those points that do not belong to any obvious cluster), and the representative spiral wave endpoints are retained, so as to obtain a set of screened spiral wave endpoints.

[0132] The second sending unit 1056 is used to send the set of screened spiral wave endpoints to the diagnosis module.

[0133] In the embodiment of the present application, the second sending unit 1056 formats the set of screened spiral wave endpoints so that it conforms to the data format that the diagnosis module can receive and process. Then, this set is sent to the diagnosis module through the data transmission interface.

[0134] In the embodiment of the present application, by segmenting sub-images and combining specific algorithms, the data complexity and interference are reduced, and the detection accuracy of spiral wave endpoints is improved. With the help of the three-dimensional coordinate system and the cutting operation, the spatial positions of the endpoints are clarified for accurate positioning of the treatment. Clustering and screening remove noise and misdetected endpoints, ensuring the quality of the endpoint set and reducing interference.

[0135] In the above Figure 3 shown situation, the embodiment of the present application also provides a tachycardia diagnosis and treatment device diagram. As Figure 4 shown, the screening unit 1055 includes an acquisition element and a screening element 10552 connected in sequence, where:

[0136] The acquisition element 10551 is used to acquire the corresponding multiple spiral wave endpoints in multiple sub-images to obtain an initial set of spiral wave endpoints.

[0137] In an embodiment of the present application, after the component 10551 completes the detection of the spiral wave endpoints of multiple sub-images, the detected spiral wave endpoints in each sub-image are summarized. Each spiral wave endpoint has corresponding coordinate values (x, y, z) in a three-dimensional rectangular coordinate system, and these coordinate values define its position in the three-dimensional space of the target area. By integrating the coordinate information of the spiral wave endpoints of all sub-images, an initial set of spiral wave endpoints is obtained.

[0138] The screening component 10552 is used to screen out the spiral wave endpoints in the initial set of spiral wave endpoints whose standard deviation of spatial distribution exceeds a preset distance threshold, and a screened set of spiral wave endpoints is obtained.

[0139] In an embodiment of the present application, for all endpoints in the initial set of spiral wave endpoints, the screening component 10552 needs to calculate their standard deviation of spatial distribution. The specific steps are as follows:

[0140] Calculate the average value of the coordinate values of all endpoints on the x, y, and z axes respectively to obtain the spatial mean point . The calculation formula is: (1).

[0141] Where n is the number of endpoints in the initial set of spiral wave endpoints, is the coordinate of the i-th endpoint.

[0142] For each endpoint , calculate the sum of the squares of its distances to the mean point , and then calculate the average value to obtain the variance .

[0143] The calculation formula is: (2).

[0144] Take the square root of the variance to obtain the standard deviation of spatial distribution .

[0145] The preset distance threshold is a preset value. In the present application, the preset distance threshold is 0.5 mm. This threshold is used to determine whether the spatial distribution of the spiral wave endpoints is too scattered. If the standard deviation of the spatial distribution of the endpoints exceeds this threshold, it indicates that there may be some abnormal endpoints that are far from the main distribution area, and these endpoints are likely to be caused by noise, misdetection, etc.

[0146] Compare the calculated standard deviation of spatial distribution with the preset distance threshold. For each endpoint in the initial set of spiral wave endpoints, calculate its distance to the mean point .

[0147] (3).

[0148] If the standard deviation of the spatial distribution of the entire set exceeds the preset distance threshold for the distance corresponding to a certain endpoint, then that endpoint is screened out from the initial set of spiral wave endpoints. Repeat this process until the standard deviation of the spatial distribution of the remaining set of endpoints does not exceed the preset distance threshold. At this time, the obtained set is the screened set of spiral wave endpoints.

[0149] The screened set of spiral wave endpoints contains the spiral wave endpoints that are retained after screening, with relatively concentrated spatial distribution and representativeness. Output this set in a suitable data format (such as a list form, where each element is the three-dimensional coordinates of an endpoint), and it can be sent to the diagnostic module later for further tachycardia diagnosis and treatment plan formulation.

[0150] In the embodiments of the present application, by screening out abnormal endpoints, removing noise and false detection interference, the data quality of the set of spiral wave endpoints is improved, and the actual distribution of the spiral wave is accurately presented. The abnormal area is accurately located, making the treatment plan more targeted and personalized, and improving the treatment effect.

[0151] It should be noted that in each embodiment of the present application, each functional unit can be integrated in one processing unit, can also exist physically alone, or two or more units can be integrated in one unit.

[0152] It should be understood that throughout the specification, the mention of "one embodiment" or "an embodiment" or "some embodiments" means that specific features, structures, or characteristics related to the embodiment are included in at least one embodiment of the present application. Therefore, the appearances of "in one embodiment" or "in an embodiment" or "in some embodiments" throughout the specification do not necessarily refer to the same embodiment. In addition, these specific features, structures, or characteristics can be combined in one or more embodiments in any suitable manner. It should be understood that in various embodiments of the present application, the magnitudes of the serial numbers of the above processes do not mean the order of execution is prior or subsequent. The order of execution of each process should be determined by its function and internal logic, and should not constitute any limitation to the implementation process of the embodiments of the present application. The serial numbers of the embodiments of the present application above are only for description and do not represent the advantages or disadvantages of the embodiments. The above descriptions of the various embodiments tend to emphasize the differences between the various embodiments, and their similarities or similarities can be referred to each other. For the sake of brevity, they will not be repeated herein.

[0153] The term "and / or" in this article is merely a description of the association relationship of the associated objects, indicating that there can be three relationships. For example, object A and / or object B can represent: object A exists alone, object A and object B exist simultaneously, and object B exists alone.

[0154] It should be noted that in this text, the terms "include", "comprise" or any other variants thereof are intended to cover non-exclusive inclusion, such that a process, method, article or device comprising a series of elements not only includes those elements but also includes other elements not expressly listed, or further includes elements inherent to such process, method, article or device. Without further limitation, an element defined by the phrase "comprising a..." does not exclude the presence of additional identical elements in the process, method, article or device comprising such element.

[0155] In several embodiments provided in this application, it should be understood that the disclosed devices and methods can be implemented in other ways. The above-described embodiments are merely illustrative. For example, the division of the modules is only a logical function division, and there can be other division methods in actual implementation. For example, multiple modules or components can be combined, or can be integrated into another system, or some features can be ignored or not executed. In addition, the coupling, direct coupling, or communication connection between the various components shown or discussed can be through some interfaces, and the indirect coupling or communication connection of devices or modules can be electrical, mechanical or other forms.

[0156] The modules described above as separate components may or may not be physically separated, and the components shown as modules may or may not be physical modules; they can be located in one place or distributed to multiple network units; some or all of the modules can be selected according to actual needs to achieve the purpose of the solution of this embodiment.

[0157] In addition, in each embodiment of this application, the various functional modules can all be integrated in a processing unit, or each module can be separately used as a unit, or two or more modules can be integrated in a unit; the above-mentioned integrated modules can be implemented in the form of hardware, or in the form of hardware plus software functional units.

[0158] Those of ordinary skill in the art can understand that all or part of the steps of implementing the above method embodiments can be completed by hardware related to program instructions. The foregoing program can be stored in a computer-readable storage medium. When the program is executed, it performs the steps including the above method embodiments; and the foregoing storage medium includes: various media such as removable storage devices, read-only memory (ROM), magnetic disks or optical discs that can store program codes.

[0159] Alternatively, if the above integrated units of the present application are implemented in the form of software function modules and sold or used as independent products, they can also be stored in a computer-readable storage medium. Based on such an understanding, the technical solution of the embodiments of the present application, in essence or the part that contributes to the related art, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes several instructions for causing an electronic device to execute all or part of the methods described in the various embodiments of the present application. The aforementioned storage medium includes: various media that can store program codes such as removable storage devices, ROMs, magnetic disks, or optical discs.

[0160] The features disclosed in the several method or device embodiments provided by the present application can be combined arbitrarily without conflict to obtain new method embodiments or device embodiments.

[0161] The above is only the implementation manner of the present application, but the protection scope of the present application is not limited thereto. Any person skilled in the art within the technical scope disclosed by the present application can easily think of changes or substitutions, which should all be covered by the protection scope of the present application. Therefore, the protection scope of the present application should be subject to the protection scope of the claims.

Claims

1. A tachycardia diagnosis and treatment device, characterized in that It includes an ultrasonic transducer module, a control module, a strain rate module, a three-dimensional imaging module, a spiral wave endpoint localization module, and a diagnosis module connected in sequence. The diagnosis module is also connected to the control module, where: The ultrasonic transducer module is configured to emit ultrasonic waves after receiving the emission signal sent by the control module, and receive the echo signal after the ultrasonic waves are reflected by the target area, and send the echo signal to the control module; The control module is configured to send the emission signal to the ultrasonic transducer module and receive the echo signal, generate three-dimensional displacement field data corresponding to the target area according to the echo signal, and send the three-dimensional displacement field data to the strain rate module; The strain rate module is configured to perform deformation tensor calculation on the received three-dimensional displacement field data to obtain the strain rate, and send the strain rate to the three-dimensional imaging module; The three-dimensional imaging module is configured to obtain a strain rate data set according to the received strain rate, perform three-dimensional mapping on the strain rate data set to obtain three-dimensional imaging data, and send the three-dimensional imaging data to the spiral wave endpoint localization module; The spiral wave endpoint localization module is configured to generate a plurality of sub-images according to the received three-dimensional imaging data, perform spiral wave endpoint detection on the plurality of sub-images to obtain the spiral wave endpoints of the plurality of sub-images, perform clustering and screening on the spiral wave endpoints of the plurality of sub-images to obtain a filtered set of spiral wave endpoints, and send the filtered set of spiral wave endpoints to the diagnosis module; The diagnosis module is configured to determine whether tachycardia exists in the target area according to a preset frequency threshold and the received filtered set of spiral wave endpoints; when tachycardia exists in the target area, the diagnosis module sends a treatment instruction and the filtered set of spiral wave endpoints to the control module; The control module is further configured to generate control information according to the received filtered set of spiral wave endpoints after receiving the treatment instruction sent by the control module, and send the control information to the ultrasonic transducer module. The control information includes the sound intensity, phase of the ultrasonic wave, and the position of the spiral wave endpoint; The ultrasonic transducer module is further configured to adjust the sound intensity and phase of the ultrasonic wave according to the received control information and then emit the ultrasonic wave to the target area to perform ultrasonic focusing on the position of the spiral wave endpoint; The spiral wave endpoint localization module includes a second receiving unit, a building unit, a cutting unit, a second calculation unit, a screening unit, and a second sending unit connected in sequence, where; The second receiving unit is configured to receive the three-dimensional imaging data of the three-dimensional imaging module; The building unit is configured to establish a three-dimensional rectangular coordinate system according to the three-dimensional imaging data; The cutting unit is configured to cut the three-dimensional imaging data perpendicular to the coordinate axes along the x, y, and z axes of the three-dimensional rectangular coordinate system to generate a plurality of sub-images; The second calculation unit is configured to use the Moore neighborhood tracking algorithm for each of the multiple sub-images to obtain the intersection line between the foreground and the background in each sub-image, where the foreground is the region in the sub-image that contains the spiral wave, and the background is the region in the sub-image without the spiral wave; when the intersection line meets a preset curvature threshold, the spiral wave endpoints of the sub-image corresponding to the intersection line are obtained by fitting the curvature circle algorithm; The screening unit is configured to perform clustering screening on the spiral wave endpoints of the multiple sub-images to obtain a set of screened spiral wave endpoints; The second sending unit is configured to send the set of screened spiral wave endpoints to the diagnosis module.

2. The tachycardia diagnosis and treatment device according to claim 1, characterized in that, The strain rate module includes a first receiving unit, a first calculation unit, a conversion unit, and a first sending unit that are connected in sequence, where; The first receiving unit is configured to receive the three-dimensional displacement field data of the control module; The first calculation unit is configured to perform deformation tensor calculation on the three-dimensional displacement field data to obtain a gradient deformation tensor and a Green-Lagrange strain tensor; perform eigenvalue decomposition and invariant combination operations on the gradient deformation tensor and the Green-Lagrange strain tensor respectively to obtain the tensor invariants of the target region; The conversion unit is configured to perform strain rate conversion on the tensor invariants to obtain the strain rate of the target region; The first sending unit is configured to send the strain rate of the target region to the three-dimensional imaging module.

3. The tachycardia diagnosis and treatment device according to claim 1, characterized in that, The screening unit includes an acquisition element and a screening element that are connected in sequence, where; The acquisition element is configured to acquire the corresponding multiple spiral wave endpoints in the multiple sub-images to obtain an initial set of spiral wave endpoints; The screening element is configured to perform screening processing on the spiral wave endpoints in the initial set of spiral wave endpoints whose standard deviation of spatial distribution exceeds a preset distance threshold to obtain a set of screened spiral wave endpoints.

4. A tachycardia diagnosis and treatment device according to claim 3, characterized in that, The preset distance threshold is 0.5 mm.

5. A tachycardia diagnosis and treatment device according to claim 1, characterized in that, The ultrasonic transducer module includes at least two groups of ultrasonic transducers.

6. The tachycardia diagnosis and treatment device according to claim 5, characterized in that, The operating frequency range of the ultrasonic transducer is 1 MHz to 10 MHz.

7. The tachycardia diagnosis and treatment device according to claim 1, characterized in that, The time of ultrasonic focusing is 20 ms.

8. A tachycardia diagnosis and treatment device according to claim 1, characterized in that, The preset frequency threshold is the occurrence frequency of 85% of the spiral wave endpoints.

9. A tachycardia diagnosis and treatment device according to claim 5, characterized in that, The imaging interval time of the three-dimensional mapping is 10 ms.

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