Heart magnetic field simulation device based on current dipole and control method thereof

Abstract

The invention provides a heart magnetic field simulation device based on a current dipole and a control method thereof. The device comprises a trunk simulation container; a support; the heart simulation shell is supported in the internal space of the trunk simulation container by a supporting piece, and a plurality of through holes are distributed in the surface of the heart simulation shell; the conductive solution is located in the trunk simulation container; the current dipole simulator is located in the conductive solution and fixed to any through hole in the surface of the heart simulation shell, and the positive electrode and the negative electrode of the current dipole simulator are connected to the electrocardiosignal generator; the electrocardiosignal generator is configured to generate a simulation electrocardiosignal, the electrocardiosignal generator, the positive electrode of the current dipole simulator, the conductive solution and the negative electrode of the current dipole simulator form a conductive path, and the conductive path generates a heart simulation magnetic field; when the current dipole simulator is fixed at different through hole positions of the heart simulation shell, the conductive path has different magnetic field expressions. According to the technical scheme, the cost of magnetocardiography simulation is reduced.

Description

[Technical field]

[0001] The present application relates to the field of medical device technology, and in particular to a cardiac magnetic field simulation device based on current dipole and a control method thereof. [Background technology]

[0002] The electrical activity of the heart generates weak magnetic fields outside the body. Magnetocardiography (MCG) devices that integrate extremely weak magnetic field measurement technology (such as optically pumped magnetometers) can detect these magnetic signals non-invasively, providing important information for early diagnosis and risk assessment of heart disease.

[0003] At present, the simulation of cardiac magnetic field is mainly based on mathematical methods. These mathematical methods are based on the theoretical model of bioelectromagnetism, using the current distribution characteristics of cardiac electrical activity to generate magnetic field distribution maps through complex differential equations. However, these mathematical methods usually require high computing power and long calculation time, and there are certain calculation errors when processing complex models. The overall cost is high and it is difficult to adapt to the rapid verification, experimental teaching or equipment inspection involved in cardiac magnetic field simulation.

[0004] Therefore, how to efficiently simulate the main characteristics of the cardiac magnetic field while reducing the simulation cost of the cardiac magnetic field has become a technical problem that needs to be solved urgently. [Summary of the invention]

[0005] The embodiment of the present application provides a cardiac magnetic field simulation device based on current dipole and a control method thereof, aiming to solve the technical problem of high cost of cardiac magnetic field simulation using mathematical methods in related technologies.

[0006] In a first aspect, an embodiment of the present application provides a cardiac magnetic field simulation device based on current dipole, comprising:

[0007] torso simulation container;

[0008] A support member is located in the trunk simulation container, and a first end of the support member is fixedly connected to an inner wall of the trunk simulation container;

[0009] A heart simulation shell connected to the second end of the support member and supported by the support member in the inner space of the trunk simulation container, wherein a plurality of through holes are distributed on the surface of the heart simulation shell;

[0010] A conductive solution is located in the trunk simulation container, and the highest point of the heart simulation shell is located below the highest point of the liquid surface of the conductive solution;

[0011] A current dipole simulator is in the conductive solution and fixed at any through-hole position on the surface of the heart simulation shell, wherein the positive electrode and the negative electrode of the current dipole simulator are respectively connected to an electrocardiogram signal generator;

[0012] The ECG signal generator is configured to generate a simulated ECG signal, wherein:

[0013] The ECG signal generator, the positive electrode of the current dipole simulator, the conductive solution and the negative electrode of the current dipole simulator form a conductive path, and the conductive path generates a heart simulation magnetic field in response to the simulated ECG signal from the ECG signal generator. When the current dipole simulator is fixed at different through-hole positions of the heart simulation shell, the conductive path has different magnetic field performances.

[0014] In one embodiment of the present application, optionally, the shape of the heart simulation shell is spherical, and the multiple through holes are evenly distributed on the surface of the heart simulation shell.

[0015] In one embodiment of the present application, optionally, the thickness of the heart simulation shell is greater than or equal to 2 mm and less than or equal to 4 mm, the diameter of the heart simulation shell is 100 mm, the aperture of each through hole is greater than or equal to 6 mm and less than or equal to 10 mm, and the distance between adjacent through holes is greater than 6 mm.

[0016] In one embodiment of the present application, optionally, the shape of the heart simulation shell is a shape of a biological heart, and the multiple through holes are distributed at designated cardiac magnetometry detection positions on the surface of the heart simulation shell.

[0017] In one embodiment of the present application, optionally, the conductive solution is a 0.9% sodium chloride solution, and the height difference between the highest point of the liquid surface of the conductive solution and the highest point of the heart simulation shell is greater than or equal to 50 mm.

[0018] In one embodiment of the present application, optionally, the current dipole simulator includes:

[0019] A fixing piece, which can be plugged and fixed in any through hole;

[0020] A positive electrode carrier, located on the surface of the fixing member and arranged at a first position outside the through hole;

[0021] a negative electrode carrier, located on the surface of the fixing member, and arranged at a second position outside the through hole, the first position and the second position are non-adjacent positions, the positive electrode carrier and the negative electrode carrier are in a non-contact state, and the conductive path has different magnetic field performances when the positive electrode carrier and the negative electrode carrier are located at different relative positions outside the same through hole;

[0022] A twisted pair, comprising a first wire and a second wire, wherein the first wire and the second wire pass through the through hole, and the positive electrode carrier and the negative electrode carrier are connected to the electrocardiographic signal generator through the first wire and the second wire respectively;

[0023] The fixing member fixes a first line segment of the first wire adjacent to the connection end with the positive electrode carrier and a second line segment of the second wire adjacent to the connection end with the negative electrode carrier in the through hole, respectively, so that the positive electrode carrier and the negative electrode carrier are fixed at the first position and the second position, respectively.

[0024] In one embodiment of the present application, optionally, the fixing member includes:

[0025] A fixing body, wherein the fixing body has a fixing hole, and the first wire and the second wire pass through the fixing hole to be connected to the electrocardiographic signal generator;

[0026] A T-shaped fixing plug is pluggable and fixed in the fixing hole, and the first line segment and the second line segment are respectively pressed and fixed on the inner wall of the fixing hole;

[0027] The fixing teeth are located on the outer surface of the fixing member body and match with the inner edge of the through hole so that the fixing member can be plugged in and fixed in the through hole.

[0028] In one embodiment of the present application, optionally, the positive electrode carrier and the negative electrode carrier are copper balls; or the positive electrode carrier and the negative electrode carrier are coaxial cables.

[0029] In a second aspect, an embodiment of the present application provides a control method for a cardiac magnetic field simulation device based on a current dipole, which is used in the cardiac magnetic field simulation device based on a current dipole as described in any one of the first aspects above, comprising:

[0030] Outputting a first simulated ECG signal through the ECG signal generator of the cardiac magnetic field simulation device;

[0031] determining a simulated magnetic signal generated by a conductive path of the cardiac magnetic field simulation device in response to the first simulated ECG signal;

[0032] Determining a detection magnetic signal obtained by a magnetocardiographic imaging device detecting a simulated magnetic signal of the cardiac magnetic field simulation device;

[0033] determining a device consistency parameter of the magnetocardiography device based on a difference between a contrast magnetic signal obtained by detecting the analog magnetic signal using a contrast device of the magnetocardiography device and the detection magnetic signal corresponding to the magnetocardiography device; or

[0034] Based on the differences between the plurality of detected magnetic signals of the magnetocardiograph device, a device consistency parameter of the magnetocardiograph device is determined.

[0035] In a third aspect, an embodiment of the present application provides a control method for a cardiac magnetic field simulation device based on a current dipole, which is used in the cardiac magnetic field simulation device based on a current dipole as described in any one of the first aspects above, comprising:

[0036] Setting the actual position of the current dipole simulator of the cardiac magnetic field simulation device to the designated through hole of the cardiac simulation shell;

[0037] Outputting a second simulated electrocardiogram signal to the current dipole simulator at the actual position through the electrocardiogram signal generator of the cardiac magnetic field simulation device;

[0038] determining a simulated magnetic signal generated by the conductive path of the cardiac magnetic field simulation device in response to the second simulated electrocardiographic signal;

[0039] Determining a detection magnetic signal obtained by the magnetocardiography device detecting a simulated magnetic signal of the cardiac magnetic field simulation device;

[0040] Determine the predicted position of the current dipole simulator based on the second simulated ECG signal, the detected magnetic signal and a preset magnetic heart inversion algorithm, wherein the magnetic heart inversion algorithm is used to reflect the correlation between the detected magnetic signal generated in response to the second simulated ECG signal when the current dipole simulator is located at the actual position and the predicted position of the current dipole simulator;

[0041] The prediction accuracy of the magnetic cardioinversion algorithm is determined based on the distance between the actual position and the predicted position of the current dipole simulator.

[0042] The above technical solution aims to solve the technical problem of high cost of simulating cardiac magnetic field by mathematical methods in related technologies. It uses current dipoles with adjustable position and direction as the source of electrical activity, and uses ECG signal generator as the input of current dipole to simulate ECG signal, thus completing the efficient simulation of cardiac magnetic field under limited resources. This cardiac magnetic field simulation device has a simple structure, low cost, and easy operation. It can be quickly built and widely used in practical scenarios such as experimental teaching, verification of cardiac magnetic inversion algorithm and inspection of cardiac magnetic imaging equipment, reducing the cost of cardiac magnetic simulation.

Brief Description of the Drawings

[0043] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0044] Figure 1 A schematic diagram of a cardiac magnetic field simulation device based on current dipole according to an embodiment of the present application is shown;

[0045] Figure 2 A schematic structural diagram of a current dipole simulator according to an embodiment of the present application is shown;

[0046] Figure 3 A schematic diagram showing a multi-channel magnetic field signal when an ECG signal generator outputs a normal ECG signal according to an embodiment of the present application is shown;

[0047] Figure 4 A flow chart showing a control method of a cardiac magnetic field simulation device based on current dipole according to an embodiment of the present application;

[0048] Figure 5 A flow chart showing a control method of a cardiac magnetic field simulation device based on current dipole according to another embodiment of the present application;

[0049] Figure 6 A two-dimensional isomagnetic diagram of a simulated magnetic signal measured when a current dipole simulator according to an embodiment of the present application is at the top of a porous spherical shell is shown;

[0050] Figure 7 A two-dimensional isomagnetic diagram of a simulated magnetic signal measured by a current dipole simulator according to an embodiment of the present application after changing the direction of the copper ball connection line when the current dipole simulator is at the top of a porous spherical shell;

[0051] Figure 8 A two-dimensional isomagnetic map of a simulated magnetic signal measured by a current dipole simulator according to an embodiment of the present application at a through-hole position on the lower hemisphere of a porous spherical shell is shown. [Specific implementation method]

[0052] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0053] Figure 1A schematic diagram of a cardiac magnetic field simulation device based on current dipole according to an embodiment of the present application is shown.

[0054] like Figure 1 As shown, a cardiac magnetic field simulation device based on current dipole according to an embodiment of the present application comprises: a trunk simulation container 1, a heart simulation shell 2, a conductive solution 3, a current dipole simulator 4, an ECG signal generator 5 and a support 6. In the present technical solution, the trunk of the organism is simulated by the trunk simulation container 1, the heart simulation shell 2 simulates the heart organ of the organism, and the conductive solution 3 simulates the heart survival environment in the trunk of the organism.

[0055] The support member 6 is located in the trunk simulation container 1, the first end of the support member 6 is fixedly connected to the inner wall of the trunk simulation container 1, and the heart simulation shell 2 is connected to the second end of the support member 6 and supported by the support member 6 in the inner space of the trunk simulation container 1. In other words, the support member 6 plays a role in supporting and fixing the heart simulation shell 2.

[0056] There are multiple through holes distributed on the surface of the heart simulation shell 2, each of which is an optional installation position of the current dipole simulator 4. When the current dipole simulator 4 is fixed at different through hole positions of the heart simulation shell 2, the conductive path has different magnetic field performances.

[0057] In one possible design, Figure 1 As shown, the shape of the heart simulation shell 2 is spherical, and a plurality of through holes are evenly distributed on the surface of the heart simulation shell 2 .

[0058] Optionally, the thickness of the heart simulation shell 2 is greater than or equal to 2 mm and less than or equal to 4 mm, the diameter of the heart simulation shell 2 is 100 mm, the aperture of each through hole is greater than or equal to 6 mm and less than or equal to 10 mm, and the distance between adjacent through holes is greater than 6 mm.

[0059] Of course, the thickness of the heart simulation shell 2, the diameter of the heart simulation shell 2, the aperture of each through hole and the distance between adjacent through holes may also be any other values ​​that meet the actual requirements of magnetic heart simulation, and are not limited to the example range given in this application.

[0060] In another possible design, the heart simulation shell is shaped like a biological heart, and a plurality of through holes are distributed at designated cardiac magnetometry detection positions on the surface of the heart simulation shell. Therefore, the positions of the through holes on the biological heart-shaped heart simulation shell are closer to the biological real heart than the positions of the through holes on the spherical heart simulation shell. Therefore, when the current dipole simulator is fixed at the designated cardiac magnetometry detection positions on the surface of the biological heart-shaped heart simulation shell to perform cardiac magnetometry simulation, a higher accuracy of cardiac magnetometry simulation can be obtained.

[0061] The conductive solution 3 is located in the trunk simulation container 1, and the highest point of the heart simulation shell 2 is located below the highest point of the liquid surface of the conductive solution 3, so as to simulate the protective environment of the biological heart in the biological trunk.

[0062] In a possible design, the conductive solution 3 is a 0.9% sodium chloride solution, and the height difference between the highest point of the liquid surface of the conductive solution 3 and the highest point of the heart simulation shell 2 is greater than or equal to 50 mm. Of course, the conductive solution 3 can also be a liquid of any other concentration similar to the environment of the biological heart, and the height difference can also be any other value that meets the actual requirements of cardiac magnetic simulation, and is not limited to the example range given in this application.

[0063] The current dipole simulator 4 is in the conductive solution 3 and fixed at any through-hole position on the surface of the heart simulation shell 2. The positive and negative electrodes of the current dipole simulator 4 are respectively connected to the ECG signal generator 5, which is configured to generate simulated ECG signals.

[0064] Based on the above structure, the ECG signal generator 5, the positive electrode of the current dipole simulator 4, the conductive solution 3 and the negative electrode of the current dipole simulator 4 form a conductive path, and the conductive path generates a heart simulated magnetic field in response to the simulated ECG signal from the ECG signal generator 5.

[0065] Among them, the ECG signal generator 5 can generate simulated ECG signals and other current signals of waveforms with adjustable position, direction and signal amplitude, which are used to simulate the electrical activity of the heart of a living organism. Furthermore, after these signals enter the conductive path, the conductive path will form a heart simulation magnetic field, which is the result of simulating the magnetic signals generated by the electrical activity of the heart of a living organism.

[0066] The above technical solution aims at the technical problem that the cost of simulating the cardiac magnetic field by mathematical methods in the related art is too high. The current dipole with adjustable position and direction is used as the source of electrical activity, and the ECG signal generator 5 is used as the current dipole input to simulate the ECG signal, so as to complete the efficient simulation of the cardiac magnetic field under limited resources. This cardiac magnetic field simulation device has a simple structure, low cost, and easy operation. It can be quickly built and widely used in practical scenarios such as experimental teaching, verification of cardiac magnetic inversion algorithm and inspection of cardiac magnetic imaging equipment, reducing the cost of cardiac magnetic simulation.

[0067] In a possible design, the current dipole simulator 4 includes: a positive electrode carrier 41 , a negative electrode carrier 42 , a twisted pair 43 (not marked in the drawings) and a fixing member 44 .

[0068] The fixing member 44 can be plugged and fixed in any through hole, the positive electrode carrier 41 is located on the surface of the fixing member 44 and is set at a first position outside the through hole, and the negative electrode carrier 42 is located on the surface of the fixing member 44 and is set at a second position outside the through hole. The first position and the second position are non-adjacent positions, and the positive electrode carrier 41 and the negative electrode carrier 42 are in a non-contact state.

[0069] The twisted pair 43 includes a first wire 431 and a second wire 432, which pass through the through hole, and the positive electrode carrier 41 and the negative electrode carrier 42 are connected to the electrocardiographic signal generator 5 through the first wire 431 and the second wire 432. The fixing member 44 fixes the first wire segment of the first wire 431 adjacent to the connection end with the positive electrode carrier 41 and the second wire segment of the second wire 432 adjacent to the connection end with the negative electrode carrier 42 in the through hole, so that the positive electrode carrier 41 and the negative electrode carrier 42 are fixed at the first position and the second position, respectively.

[0070] It can be seen that the fixing member 44 fixes the positive electrode carrier 41 and the negative electrode carrier 42 on its surface by pressing the first wire 431 and the second wire 432 respectively close to the positive electrode carrier 41 and the negative electrode carrier 42. In this way, the ECG signal generator 5 is connected to the positive electrode carrier 41 and the negative electrode carrier 42 of the current dipole simulator 4 through the first wire 431 and the second wire 432 respectively, and the positive electrode carrier 41 and the negative electrode carrier 42 are respectively connected to the conductive solution 3, so that the ECG signal generator 5, the positive electrode carrier 41, the conductive solution 3 and the negative electrode carrier 42 form a conductive path to generate a cardiac simulation magnetic field.

[0071] like Figure 2 As shown, in the current dipole simulator 4 , the positive electrode carrier 41 and the negative electrode carrier 42 are copper balls, and the fixing member 44 includes a fixing member body (not marked in the figure), a T-shaped fixing plug 441 and fixing teeth 442 .

[0072] The fixing body has a fixing hole, and the first wire 431 and the second wire 432 pass through the fixing hole to connect with the ECG signal generator 5. The T-shaped fixing plug 441 can be plugged and fixed in the fixing hole, and the first wire segment and the second wire segment are respectively pressed and fixed on the inner wall of the fixing hole. The fixing teeth 442 are located on the outer surface of the fixing body and match with the inner edge of the through hole, so that the fixing member 44 can be plugged and fixed in the through hole.

[0073] Of course, the T-shaped fixing plug 441 can also be a fixing tool of any other shape, and the fixing teeth 442 can also be of any shape, not limited to Figure 2 The example given.

[0074] In another possible design, the positive electrode carrier 41 and the negative electrode carrier 42 may also be coaxial cables.

[0075] like Figure 3 As shown, when the ECG signal generator 5 outputs a normal ECG signal, the multi-channel magnetic field signal measured by the extremely weak magnetic sensor panel of the magnetocardiography device is a superimposed butterfly diagram.

[0076] Figure 4 A flow chart of a control method of a cardiac magnetic field simulation device based on current dipole according to an embodiment of the present application is shown.

[0077] like Figure 4 As shown, according to an embodiment of the present application, a control method of a cardiac magnetic field simulation device based on a current dipole includes:

[0078] Step 402: Output a first simulated ECG signal through an ECG signal generator of a cardiac magnetic field simulation device.

[0079] Step 404 : determining a simulated magnetic signal generated by the conductive path of the cardiac magnetic field simulation device in response to the first simulated ECG signal.

[0080] Step 406 , determining a detected magnetic signal obtained by the magnetocardiographic imaging device detecting the simulated magnetic signal of the cardiac magnetic field simulation device.

[0081] Step 408 , determining a device consistency parameter of the magnetocardiography device based on a difference between a contrast magnetic signal obtained by a contrast device of the magnetocardiography device detecting the analog magnetic signal and the detection magnetic signal corresponding to the magnetocardiography device.

[0082] That is, the cardiac magnetic field simulation device is placed at the designated detection position of the magnetic heart imaging device, and is used as a simulated object of the biological heart for detection. In this detection, the first simulated electrocardiographic signal is output by the electrocardiographic signal generator of the cardiac magnetic field simulation device, so that the cardiac magnetic field simulation device forms a simulated magnetic field corresponding to the first simulated electrocardiographic signal, and the simulated magnetic field is expressed as a detectable simulated magnetic signal. In other words, the cardiac magnetic field simulation device is placed at the designated detection position of the magnetic heart imaging device in order to detect the simulated magnetic signal. Accordingly, the magnetic heart imaging device detects and obtains the detection magnetic signal.

[0083] At the same time, the same measures can be taken for the contrast device of the magnetocardiography device, so that the contrast device detects the analog magnetic signal to obtain a contrast magnetic signal.

[0084] The comparison device described here is an inspection device with the same magnetocardiography function as the magnetocardiography device, and the rated magnetocardiography detection capabilities of the two devices should be consistent. In other words, the comparison device is a device with a more standard magnetocardiography detection capability. If the difference between the comparison magnetic signal and the detection magnetic signal is within a reasonable range, it means that the magnetocardiography detection capabilities of the comparison device and the magnetocardiography device are consistent. In this case, the obtained device consistency parameter is high. Conversely, if the difference between the comparison magnetic signal and the detection magnetic signal exceeds a reasonable range, it means that the magnetocardiography detection capability of the magnetocardiography device is lower than that of the comparison device. In this case, the obtained device consistency parameter is low.

[0085] It can be understood that the device consistency parameter reflects the level of the magnetocardiographic detection capability of the magnetocardiographic imaging device.

[0086] In another possible design, the method of calculating the device consistency parameter includes: determining the device consistency parameter of the magnetocardiography device based on the difference between the multiple detected magnetic signals of the magnetocardiography device.

[0087] The plurality of detection magnetic signals of the magnetocardiographic imaging device are all measured when the first simulated electrocardiographic signal is input into the cardiac magnetic field simulation device. If the difference between any two of the plurality of detection magnetic signals is large, it indicates that the magnetocardiographic imaging device's magnetocardiographic detection capability is not stable, and at this time, the magnetocardiographic imaging device needs to be repaired. On the contrary, if the difference between any two of the plurality of detection magnetic signals is within a reasonable range, it indicates that the magnetocardiographic imaging device's magnetocardiographic detection capability is stable and can be put into normal use.

[0088] Through the above technical solution, complex mathematical methods can be replaced, and the standard level or stability of the magnetocardiac detection capability of the magnetocardiac imaging equipment can be verified only by a cardiac magnetic field simulation device based on current dipoles. This can effectively determine the appropriate maintenance time for the magnetocardiac imaging equipment and reduce the maintenance difficulty of the magnetocardiac imaging equipment.

[0089] Figure 5 A flow chart of a method for controlling a cardiac magnetic field simulation device based on current dipole according to another embodiment of the present application is shown.

[0090] like Figure 5 As shown, according to another embodiment of the present application, a control method of a cardiac magnetic field simulation device based on current dipole includes:

[0091] Step 502: setting the actual position of the current dipole simulator of the cardiac magnetic field simulation device to the designated through hole of the cardiac simulation shell.

[0092] Step 504: output a second simulated ECG signal to the current dipole simulator at the actual position through the ECG signal generator of the cardiac magnetic field simulation device.

[0093] Step 506: determine the simulated magnetic signal generated by the conductive path of the cardiac magnetic field simulation device in response to the second simulated ECG signal.

[0094] Step 508: determining a detected magnetic signal obtained by the magnetocardiography device detecting the simulated magnetic signal of the cardiac magnetic field simulation device.

[0095] Step 510: Determine the predicted position of the current dipole simulator based on the second simulated ECG signal, the detected magnetic signal and a preset magnetocardiographic inversion algorithm.

[0096] The magnetocardiographic inversion algorithm is used to reflect the correlation between the detected magnetic signal generated in response to the second simulated electrocardiographic signal when the current dipole simulator is located at the actual position and the predicted position of the current dipole simulator.

[0097] When the current dipole simulator is fixed at different through-hole positions of the heart simulation shell, the conductive path has different magnetic field performances. Therefore, the different positions of the current dipole simulator reflect different cardiac electrical activities. Therefore, the position of the current dipole simulator is an important factor in cardiac magnetometry simulation.

[0098] In this regard, the location of the current dipole simulator can be predicted by using a magnetic heart inversion algorithm. In other words, the magnetic heart inversion algorithm is actually used to infer the source location of the magnetic signal on the heart through the detected magnetic heart signal. The magnetic heart inversion algorithm can predict the possible detection location of the current dipole simulator when the current dipole simulator generates a simulated magnetic signal after being input with the second simulated ECG signal.

[0099] Among them, the magnetocardiographic inversion algorithm includes but is not limited to beamforming method, regularization method, deep learning algorithm and any other algorithm that can achieve data inversion.

[0100] Step 512: Determine the prediction accuracy of the magnetic cardioinversion algorithm based on the distance between the actual position and the predicted position of the current dipole simulator.

[0101] The smaller the distance between the actual position and the predicted position, the more accurate the prediction of the magnetic heart inversion algorithm. Conversely, the larger the distance between the actual position and the predicted position, the larger the prediction error of the magnetic heart inversion algorithm. It can be said that the prediction accuracy of the magnetic heart inversion algorithm can reflect the prediction ability of the magnetic heart inversion algorithm. By obtaining the prediction accuracy, the ability level of the magnetic heart inversion algorithm can be accurately judged, which can indicate the direction for algorithm optimization.

[0102] The two-dimensional isomagnetic map of the simulated magnetic signal measured by the current dipole simulator at the top of the porous spherical shell is shown in Figure 6shown.

[0103] The two-dimensional isomagnetic map of the simulated magnetic signal measured by the current dipole simulator at the top of the porous spherical shell after changing the direction of the copper ball connection line is shown in the figure. Figure 7 As shown in the figure, changing the direction of the copper ball connection line will change the location of the positive electrode carrier and the negative electrode carrier. Figure 6 and Figure 7 It can be seen that when the positive carrier and the negative carrier of the current dipole simulator are located at different relative positions outside the same through hole, the conductive path has different magnetic field performances. This relative position can be understood as the position of the positive carrier and the negative carrier around the circumference outside the through hole. If the distance between the positive carrier and the negative carrier is regarded as a line segment in space, when the line segment rotates outside the through hole to point to different directions at both ends, the positive carrier and the negative carrier change from the original relative position to the current relative position.

[0104] The two-dimensional isomagnetic map of the simulated magnetic signal measured by the current dipole simulator at the through hole position on the lower hemisphere of the porous spherical shell is shown in Figure 8 As shown. Figure 6 and Figure 8 It can be seen that the magnetic field of the current dipole simulator behaves differently at different through-hole positions of the heart simulation shell.

[0105] In addition, an embodiment of the present application provides a computer-readable storage medium storing computer-executable instructions, wherein the computer-executable instructions are used to perform the following steps:

[0106] Outputting a first simulated ECG signal through the ECG signal generator of the cardiac magnetic field simulation device;

[0107] determining a simulated magnetic signal generated by a conductive path of the cardiac magnetic field simulation device in response to the first simulated ECG signal;

[0108] Determining a detection magnetic signal obtained by a magnetocardiographic imaging device detecting a simulated magnetic signal of the cardiac magnetic field simulation device;

[0109] determining a device consistency parameter of the magnetocardiography device based on a difference between a contrast magnetic signal obtained by detecting the analog magnetic signal using a contrast device of the magnetocardiography device and the detection magnetic signal corresponding to the magnetocardiography device; or

[0110] Based on the differences between the plurality of detected magnetic signals of the magnetocardiograph device, a device consistency parameter of the magnetocardiograph device is determined.

[0111] The embodiment of the present application also provides another computer-readable storage medium storing computer-executable instructions, wherein the computer-executable instructions are used to perform the following steps: setting the actual position of the current dipole simulator of the cardiac magnetic field simulation device to a designated through hole of the cardiac simulation shell;

[0112] Outputting a second simulated electrocardiogram signal to the current dipole simulator at the actual position through the electrocardiogram signal generator of the cardiac magnetic field simulation device;

[0113] determining a simulated magnetic signal generated by the conductive path of the cardiac magnetic field simulation device in response to the second simulated electrocardiographic signal;

[0114] Determining a detection magnetic signal obtained by the magnetocardiography device detecting a simulated magnetic signal of the cardiac magnetic field simulation device;

[0115] Determine the predicted position of the current dipole simulator based on the second simulated ECG signal, the detected magnetic signal and a preset magnetic heart inversion algorithm, wherein the magnetic heart inversion algorithm is used to reflect the correlation between the detected magnetic signal generated in response to the second simulated ECG signal when the current dipole simulator is located at the actual position and the predicted position of the current dipole simulator;

[0116] The prediction accuracy of the magnetic cardioinversion algorithm is determined based on the distance between the actual position and the predicted position of the current dipole simulator.

[0117] It should be noted that the above functions or steps that can be implemented by the computer-readable storage medium or computer device can refer to the relevant description in the aforementioned method embodiment. In order to avoid repetition, they will not be described one by one here.

[0118] The above is a detailed description of the technical solution of the present application in combination with the accompanying drawings. Through the technical solution of the present application, a current dipole with adjustable position and direction is used as the source of electrical activity, and an ECG signal generator is used as the current dipole input to simulate the ECG signal, so that an efficient simulation of the cardiac magnetic field is completed under limited resources. This cardiac magnetic field simulation device has a simple structure, low cost, and is easy to operate. It can be quickly built and is widely used in practical scenarios such as experimental teaching, verification of cardiac magnetometry inversion algorithms, and inspection of cardiac magnetometry imaging equipment, reducing the cost of cardiac magnetometry simulation.

[0119] It should be understood that, although the terms first, second, etc. may be used to describe the simulated ECG signals in the embodiments of the present application, these simulated ECG signals should not be limited to these terms. These terms are only used to distinguish the simulated ECG signals from each other. For example, without departing from the scope of the embodiments of the present application, the first simulated ECG signal may also be referred to as the second simulated ECG signal, and similarly, the second simulated ECG signal may also be referred to as the first simulated ECG signal.

[0120] The word "if" as used herein may be interpreted as "at the time of" or "when" or "in response to determining" or "in response to detecting", depending on the context. Similarly, the phrases "if it is determined" or "if (stated condition or event) is detected" may be interpreted as "when it is determined" or "in response to determining" or "when detecting (stated condition or event)" or "in response to detecting (stated condition or event)", depending on the context.

[0121] The terms used in the embodiments of the present application are only for the purpose of describing specific embodiments, and are not intended to limit the present application. The singular forms "a", "said" and "the" used in the embodiments of the present application and the appended claims are also intended to include plural forms, unless the context clearly indicates other meanings.

[0122] Those skilled in the art can understand that all or part of the processes in the above-mentioned embodiment methods can be completed by instructing the relevant hardware through a computer program, and the computer program can be stored in a non-volatile computer-readable storage medium. When the computer program is executed, it can include the processes of the embodiments of the above-mentioned methods. Among them, any reference to memory, storage, database or other media used in the embodiments provided in this application can include non-volatile and / or volatile memory. Non-volatile memory can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM) or flash memory. Volatile memory can include random access memory (RAM) or external cache memory. As an illustration and not limitation, RAM is available in many forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDRSDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM).

[0123] The embodiments described above are only used to illustrate the technical solutions of the present invention, rather than to limit the same. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that the technical solutions described in the aforementioned embodiments may still be modified, or some of the technical features may be replaced by equivalents. Such modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included in the protection scope of the present invention.

Claims

1. A cardiac magnetic field simulation device based on current dipole, characterized in that: include: torso simulation container; A support member is located in the trunk simulation container, and a first end of the support member is fixedly connected to an inner wall of the trunk simulation container; A heart simulation shell connected to the second end of the support member and supported by the support member in the inner space of the trunk simulation container, wherein a plurality of through holes are distributed on the surface of the heart simulation shell; A conductive solution is located in the trunk simulation container, and the highest point of the heart simulation shell is located below the highest point of the liquid surface of the conductive solution; A current dipole simulator is in the conductive solution and fixed at any through-hole position on the surface of the heart simulation shell, wherein the positive electrode and the negative electrode of the current dipole simulator are respectively connected to an electrocardiogram signal generator; The ECG signal generator is configured to generate a simulated ECG signal, wherein: The ECG signal generator, the positive electrode of the current dipole simulator, the conductive solution and the negative electrode of the current dipole simulator form a conductive path, and the conductive path generates a heart simulation magnetic field in response to the simulated ECG signal from the ECG signal generator. When the current dipole simulator is fixed at different through-hole positions of the heart simulation shell, the conductive path has different magnetic field performances.

2. The device according to claim 1, characterized in that The heart simulation shell is spherical in shape, and the plurality of through holes are evenly distributed on the surface of the heart simulation shell.

3. The device according to claim 2, characterized in that The thickness of the heart simulation shell is greater than or equal to 2 mm and less than or equal to 4 mm, the diameter of the heart simulation shell is 100 mm, the aperture of each through hole is greater than or equal to 6 mm and less than or equal to 10 mm, and the distance between adjacent through holes is greater than 6 mm.

4. The device according to claim 1, characterized in that The heart simulation shell is in the shape of a biological heart, and the plurality of through holes are distributed at designated cardiac magnetometry detection positions on the surface of the heart simulation shell.

5. The device according to claim 1, characterized in that The conductive solution is a 0.9% sodium chloride solution, and the height difference between the highest point of the liquid surface of the conductive solution and the highest point of the heart simulation shell is greater than or equal to 50 mm.

6. The device according to any one of claims 1 to 5, characterized in that The current dipole simulator comprises: A fixing piece, which can be plugged and fixed in any through hole; A positive electrode carrier, located on the surface of the fixing member and arranged at a first position outside the through hole; a negative electrode carrier, located on the surface of the fixing member, and arranged at a second position outside the through hole, the first position and the second position are non-adjacent positions, the positive electrode carrier and the negative electrode carrier are in a non-contact state, and the conductive path has different magnetic field performances when the positive electrode carrier and the negative electrode carrier are located at different relative positions outside the same through hole; A twisted pair, comprising a first wire and a second wire, wherein the first wire and the second wire pass through the through hole, and the positive electrode carrier and the negative electrode carrier are connected to the electrocardiographic signal generator through the first wire and the second wire respectively; The fixing member fixes a first line segment of the first wire adjacent to the connection end with the positive electrode carrier and a second line segment of the second wire adjacent to the connection end with the negative electrode carrier in the through hole, respectively, so that the positive electrode carrier and the negative electrode carrier are fixed at the first position and the second position, respectively.

7. The device according to claim 6, characterized in that The fixing member comprises: A fixing body, wherein the fixing body has a fixing hole, and the first wire and the second wire pass through the fixing hole to be connected to the electrocardiographic signal generator; A T-shaped fixing plug is pluggable and fixed in the fixing hole, and the first line segment and the second line segment are respectively pressed and fixed on the inner wall of the fixing hole; The fixing teeth are located on the outer surface of the fixing member body and match with the inner edge of the through hole so that the fixing member can be plugged in and fixed in the through hole.

8. The device according to claim 6, characterized in that The positive electrode carrier and the negative electrode carrier are copper balls; or The positive electrode carrier and the negative electrode carrier are coaxial cables.

9. A control method for a cardiac magnetic field simulation device based on current dipole, characterized in that: The cardiac magnetic field simulation device based on current dipole according to any one of claims 1 to 8, comprising: Outputting a first simulated ECG signal through the ECG signal generator of the cardiac magnetic field simulation device; determining a simulated magnetic signal generated by a conductive path of the cardiac magnetic field simulation device in response to the first simulated ECG signal; Determining a detection magnetic signal obtained by a magnetocardiographic imaging device detecting a simulated magnetic signal of the cardiac magnetic field simulation device; determining a device consistency parameter of the magnetocardiography device based on a difference between a contrast magnetic signal obtained by detecting the analog magnetic signal using a contrast device of the magnetocardiography device and the detection magnetic signal corresponding to the magnetocardiography device; or Based on the differences between the plurality of detected magnetic signals of the magnetocardiograph device, a device consistency parameter of the magnetocardiograph device is determined.

10. A control method for a cardiac magnetic field simulation device based on current dipole, characterized in that: The cardiac magnetic field simulation device based on current dipole according to any one of claims 1 to 8, comprising: Setting the actual position of the current dipole simulator of the cardiac magnetic field simulation device to the designated through hole of the cardiac simulation shell; Outputting a second simulated electrocardiogram signal to the current dipole simulator at the actual position through the electrocardiogram signal generator of the cardiac magnetic field simulation device; determining a simulated magnetic signal generated by the conductive path of the cardiac magnetic field simulation device in response to the second simulated electrocardiographic signal; Determining a detection magnetic signal obtained by the magnetocardiography device detecting a simulated magnetic signal of the cardiac magnetic field simulation device; Determine the predicted position of the current dipole simulator based on the second simulated ECG signal, the detected magnetic signal and a preset magnetic heart inversion algorithm, wherein the magnetic heart inversion algorithm is used to reflect the correlation between the detected magnetic signal generated in response to the second simulated ECG signal when the current dipole simulator is located at the actual position and the predicted position of the current dipole simulator; The prediction accuracy of the magnetic cardioinversion algorithm is determined based on the distance between the actual position and the predicted position of the current dipole simulator.

Images