A cardiac magnetic field measurement system, method, electronic device and storage medium

Abstract

The present invention provides a cardiac magnetic field measurement system, comprising a signal magnetic field measurement module, a background magnetic field measurement module and a control coil module, wherein the signal magnetic field measurement module is used to measure the spatial magnetic field at the signal source; the background magnetic field measurement module is used to measure the dynamic background magnetic field at the signal source; the control coil module is located between the signal magnetic field measurement module and the background magnetic field measurement module, and surrounds the signal magnetic field measurement module, and is used to provide a magnetic field with multiple degrees of freedom for shielding the dynamic background magnetic field. The purpose of the present invention is to solve the problem in the prior art that when measuring cardiac magnetism on a patient, the measurement needs to be performed through a shielding tube or in a shielding room environment, so as to facilitate the operation of measuring the cardiac magnetic field more easily.

Description

Technical Field

[0001] The present invention relates to the field of magnetic field measurement technology, and in particular to a cardiac magnetic field measurement system, method, electronic equipment and storage medium. Background Art

[0002] Cardiovascular and cerebrovascular diseases are the main cause of death in my country. Cardiac magnetic field measurement is an effective solution for detecting early heart disease and an effective supplement to conventional electrocardiogram measurement.

[0003] Currently, cardiac magnetic field measurements are mainly performed using a superconducting quantum interference device (SQUID), but the SQUID needs to work in a liquid helium environment, so it is expensive and unreliable to use. In addition, the Dewar wall that isolates the human body from the low-temperature environment is often thicker, which reduces the signal size and increases the difficulty of measurement.

[0004] In recent years, weak magnetic detection technology has been developed, and a variety of probes have achieved technological breakthroughs, realizing weak magnetic field detection without liquid helium, and solving the low-temperature environment problem in cardiac magnetometry. However, since the earth's magnetic field is much larger than the heart's magnetic field, in order to improve the signal-to-noise ratio, it is necessary to reduce the background magnetic field and then turn on the low-range measurement mode. Medical staff are also required to use shielding tubes or perform measurements in a shielded room environment, which makes the operation of cardiac magnetometry complicated, and requires the use of shielding tubes or measurements in a shielded room, which creates great psychological pressure on patients with claustrophobia. Summary of the invention

[0005] The present invention provides a cardiac magnetic field measurement system, method, electronic device and storage medium, which are used to solve the problem in the prior art that when measuring cardiac magnetism of a patient, the measurement needs to be performed through a shielding tube or in a shielding room environment, resulting in complicated operation.

[0006] The present invention provides a cardiac magnetic field measurement system, comprising:

[0007] A signal magnetic field measurement module, used to measure the spatial magnetic field at the signal source;

[0008] A background magnetic field measurement module, used to measure the dynamic background magnetic field located at the signal source; and

[0009] The control coil module is located between the signal magnetic field measurement module and the background magnetic field measurement module and surrounds the signal magnetic field measurement module, and is used to provide magnetic fields with multiple degrees of freedom for shielding the dynamic background magnetic field.

[0010] Furthermore, the signal magnetic field measurement module includes a plurality of signal magnetic field measurement probes, the signal magnetic field measurement probes include: at least one of a fluxgate probe, a magnetoresistive probe and a Hall probe, and the plurality of signal magnetic field measurement probes are arranged in a matrix.

[0011] Furthermore, the background magnetic field measurement module includes one or more background magnetic field measurement probes, and the background magnetic field measurement probes include at least one of a fluxgate probe, a magnetoresistive probe and a Hall probe.

[0012] Furthermore, the control coil module includes a plurality of coils, and the plurality of coils are arranged in layers.

[0013] Furthermore, the control coil module is used to provide a magnetic field with 9 to 12 degrees of freedom.

[0014] Furthermore, the control coil module is a hollow parallelepiped, and the signal magnetic field measurement module is located inside the parallelepiped.

[0015] Furthermore, the thickness of each layer of coils in the plurality of coils is 0.15 mm-0.25 mm, the spacing between the coils is 0.15 mm-0.25 mm, the length of each layer of coils is 11 cm-13 cm, the width is 10 cm-13 cm, and the height is 2 cm-4 cm.

[0016] The present invention provides a method for measuring the cardiac magnetic field of more than one system, comprising the following steps:

[0017] Obtain the dynamic background magnetic field and spatial position coordinates measured by the background magnetic field measurement module;

[0018] Get the number of control coils in the control coil module;

[0019] Calculating the current of the control coil module for shielding the dynamic background magnetic field according to the dynamic background magnetic field, the spatial position coordinates and the number of control coils;

[0020] After the current is passed into the control coil module, the signal magnetic field measurement module measures the magnetic field of the actual signal source.

[0021] The present invention also provides an electronic device, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor implements the cardiac magnetic field measurement method as described above when executing the program.

[0022] The present invention also provides a non-transitory computer-readable storage medium having a computer program stored thereon, and the computer program implements the above-mentioned cardiac magnetic field measurement method when executed by a processor.

[0023] The present invention provides a cardiac magnetic field measurement system, which measures the dynamic background magnetic field through a background magnetic field measurement module, and at the same time, uses a control coil module to provide a magnetic field to shield the dynamic background magnetic field, and then can measure the actual magnetic field data through a signal magnetic field measurement module, thereby facilitating the operation of medical staff. At the same time, it can be measured in an open environment, reducing the psychological burden of patients. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] In order to more clearly illustrate the technical solutions in the present invention or the prior art, a brief introduction will be given below to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0025] Figure 1 It is a schematic diagram of a top view structure of a cardiac magnetic field measurement system provided by the present invention;

[0026] Figure 2 It is a structural schematic diagram of a control coil module of a cardiac magnetic field measurement system provided by the present invention.

[0027] Reference numerals:

[0028] 1: Signal magnetic field measurement module; 2: Control coil module; 3: Background magnetic field measurement module. DETAILED DESCRIPTION

[0029] In order to make the purpose, technical solution and advantages of the present invention clearer, the technical solution of the present invention will be clearly and completely described below in conjunction with the drawings 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.

[0030] Combine the following Figure 1 and Figure 2 A cardiac magnetic field measurement system of the present invention is described, comprising a signal magnetic field measurement module 1, a control coil module 2 and a background magnetic field measurement module 3.

[0031] Specifically, the signal magnetic field measurement module 1 is used to measure the spatial magnetic field at the signal source.

[0032] The signal magnetic field measurement module 1 includes a plurality of signal magnetic field measurement probes, and the signal magnetic field measurement probes include at least one of a fluxgate probe, a magnetoresistance probe, and a Hall probe. The plurality of signal magnetic field measurement probes are arranged in a matrix. By setting a plurality of signal magnetic field measurement probes and arranging the plurality of signal magnetic field measurement probes in a matrix, the accuracy of magnetic heart measurement can be improved.

[0033] Specifically, a 4*4*1 fluxgate probe can be used, and the signal source is placed in a layer along the direction outward from the human chest, and arranged in a 2D vertical direction. If a 4*4*4 fluxgate probe is used, the signal source is placed in four layers along the direction outward from the human chest, and arranged in a 3D vertical direction. Each fluxgate probe is 2cm*2cm*2cm, and the probe interval is 2cm. At the same time, the fluxgate probe can also be replaced with a magnetoresistive probe or a Hall probe.

[0034] Specifically, the background magnetic field measurement module 3 is used to measure the dynamic background magnetic field.

[0035] The background magnetic field measurement module includes one or more background magnetic field measurement probes, and the background magnetic field measurement probes include at least one of a fluxgate probe, a magnetoresistive probe and a Hall probe.

[0036] Specifically, magnetoresistive probes are arranged above, in front of, behind, and on the left and right sides of the signal magnetic field measurement module, wherein the magnetoresistive probes are preferably tunneling magnetoresistive probes, so as to measure the dynamic background magnetic field. The magnetoresistive probes can realize the heart magnetic detection without liquid helium.

[0037] The control coil module 2 is located between the signal magnetic field measurement module and the background magnetic field measurement module, and surrounds the signal magnetic field measurement module, and is used to provide a magnetic field of multiple degrees of freedom that shields the dynamic background magnetic field. The magnetic field strength interval provided is -1 millitesla to 1 millitesla. The magnetic field strength interval is preferably -0.1 millitesla to 0.1 millitesla. Wherein, there is a spacing between the control coil module and the signal magnetic field measurement module.

[0038] The control coil module comprises a plurality of coils, and the plurality of coils are arranged in layers.

[0039] The control coil module can provide a magnetic field with 9 to 12 degrees of freedom. For example, the control coil module provides a magnetic field with 9 degrees of freedom or a magnetic field with 12 degrees of freedom. In this embodiment, the coils in the control coil module are distributed in three dimensions, and a magnetic field with 12 degrees of freedom can be obtained: including 3 0-order uniform fields and 9 gradient fields in the x, y and z directions. If the coils in the control coil module are distributed in two dimensions: that is, the coils are arranged on a plane (such as the xy plane), there is no need to compensate for the 3 gradient fields (Bxz, Byz, Bzz) in a certain direction (z), that is, a magnetic field with 9 degrees of freedom is obtained. Thus, the dynamic background magnetic field can be offset by the magnetic field generated by the control coil module, so as to shield the dynamic background magnetic field.

[0040] The thickness of each layer of coils among the plurality of coils is 0.15 mm to 0.25 mm, the spacing between the coils is 0.15 mm to 0.25 mm, the length of each layer of coils is 11 cm to 13 cm, the width is 10 cm to 13 cm, and the height is 2 cm to 4 cm.

[0041] In this embodiment, a control coil group consisting of 9 layers of control coils is used as a control coil module, so that each layer of control coils provides a magnetic field degree of freedom, thereby providing a magnetic field with 9 degrees of freedom, and the 9 degrees of freedom include uniform fields in 3 directions of x, y and z and 6 gradient fields in various directions. It is convenient to offset the dynamic background magnetic field, so that the weak magnetic measurement probe can work stably in the low range state.

[0042] Each layer of control coil is a hollow parallelepiped, so that the size of the control coil module is 12cm*12cm*3cm. The thickness of each layer of control coil is 0.2mm, and the interlayer spacing is 0.2mm. Each layer of active control coil provides a magnetic field degree of freedom.

[0043] Here, current is passed through each layer of control coil to generate a magnetic field, thereby shielding the dynamic background magnetic field.

[0044] The signal magnetic field measurement module is placed at the position of the heart, and the dynamic background magnetic field measured by the background magnetic field measurement module is shielded by the control coil magnetic field provided by the control coil module, so as to provide a stable near-zero magnetic environment for the signal magnetic field measurement module, and then the actual magnetic field data can be measured by the signal magnetic field measurement module, so as to facilitate the operation of medical staff. At the same time, the present invention can be measured in an open environment, which reduces the psychological burden of patients.

[0045] The cardiac magnetic field measurement method provided by the present invention is described below. The cardiac magnetic field measurement method described below and the weak magnetic field measurement system described above can correspond to each other.

[0046] A method for measuring a cardiac magnetic field comprises the following steps:

[0047] Step 1: Obtain the dynamic background magnetic field and spatial position coordinates measured by the background magnetic field measurement module.

[0048] In this embodiment, five magnetoresistive probes are selected as background magnetic field measurement modules, and the five magnetoresistive probes are respectively installed outside five surfaces of the front, back, left, right and top of the control coil module.

[0049] The dynamic background magnetic field measured by the magnetoresistive probes set outside the five planes of the front, back, left, right and top of the control coil module is obtained, and the spatial position (x, y, z) of each magnetoresistive probe is recorded.

[0050] At the same time, the magnetic field B(x, y, z) in space can be decomposed into three components: x, y and z, as shown in formula (1):

[0051]

[0052] Among them, x, y, z are spatial position coordinates, B0 is a uniform field, and K is a spatial first-order gradient field matrix. That is, the distribution of the magnetic field B(x, y, z) in space is mainly determined by B0 and K.

[0053] By fitting formula (1) using the least squares method, we can get the dynamic background magnetic field B bg , as shown in formula (2):

[0054]

[0055] Where t represents time, that is, the dynamic background magnetic field B bg It is dynamic and needs to be calculated through time measurement. bg0 (t) represents the 0th-order uniform field at a certain time point, K bg (t) represents the gradient field at a certain time point, B bg_x0 (t) represents the uniform field in the x direction at a certain time point,

[0056] K bg_xx (t) represents the gradient field in the x direction at a certain time point.

[0057] Step 2: Obtain the number of control coils in the control coil module.

[0058] Specifically including: obtaining the number of control coils in the control coil mold as 12 layers.

[0059] Step 3: Calculate the current used by the control coil module to shield the dynamic background magnetic field according to the dynamic background magnetic field, the spatial position coordinates and the number of control coils.

[0060] The steps include forming a diagonal matrix M of the magnetic field of the degrees of freedom that each layer of control coil can provide, as shown in formula (3):

[0061]

[0062] M x0 It means that when the first coil is passed with a current of 1A, M is generated in the x direction. x0 Tesla's magnetic field. The rest of the elements in the first row are 0, indicating that the coil does not generate other magnetic field components.

[0063] M zy It means that when a current of 1A is passed through the 12th coil, a magnetic field M is generated in the z direction. zy The y-direction gradient field in Tesla per meter. The remaining elements in the last row are 0, indicating that the coil does not generate other magnetic field components.

[0064] The control coil magnetic field B coil , as shown in formula (4):

[0065]

[0066] Among them, B coil0 represents the 0th order uniform field generated by the coil, K coil Represents the gradient field generated by the coil. Specifically: B coil_x0 , B coil_y0 and B coil_z0 are the uniform fields in the x direction, y direction and z direction of the coil, respectively, K coil_xx Represents the gradient field of one component of the coil.

[0067] When the control coil magnetic field B coil For the dynamic background magnetic field B bg When performing magnetic field shielding, the following equation (5) can be obtained:

[0068]

[0069] Formula (5) can be expanded according to formula (2) and formula (4) to obtain formula (6):

[0070]

[0071] Among them, B bg_x0 and K bg_xx Equal variables and B coil_x0 and K coil_xx And so on one to one correspondence.

[0072] Multiply formula (6) by M -1 We can get formula (7):

[0073]

[0074] Thus, the current I used by the control coil module to shield the dynamic background magnetic field is obtained. n (n=1-12). The control coil magnetic field generated by the control coil module is used to shield the dynamic background magnetic field.

[0075] Step 4: After the current is passed into the control coil module, the signal magnetic field measurement module is used to measure the magnetic field data of the actual signal source.

[0076] The control coil module replaces the shielding tube or shielding room to provide a stable near-zero magnetic environment, so that the weak magnetic probe can work normally under low-range conditions. At the same time, the signal magnetic field measurement module, background magnetic field measurement module and control coil module can measure the magnetic field of the heart, which is not only simple and stable, but also can effectively improve the economy of cardiac magnetometry. It can also be operated in an open environment, which is more friendly to the person being tested.

[0077] The present invention also provides an electronic device that may include: a processor, a communications interface, a memory, and a communications bus, wherein the processor, the communications interface, and the memory communicate with each other via the communications bus. The processor may call logic instructions in the memory to execute a cardiac magnetic field measurement method, the method comprising:

[0078] Obtain the dynamic background magnetic field and spatial position coordinates measured by the background magnetic field measurement module;

[0079] Get the number of control coils in the control coil module;

[0080] According to the dynamic background magnetic field, the spatial position coordinates and the number of control coils, a current of the control coil module for shielding the dynamic background magnetic field is obtained;

[0081] After the current is passed into the control coil module, the signal magnetic field measurement module measures the magnetic field data of the actual signal source.

[0082] In addition, the logic instructions in the above-mentioned memory can be implemented in the form of software functional units and can be stored in a computer-readable storage medium when sold or used as an independent product. Based on such an understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art or the part of the technical solution, can be embodied in the form of a software product, which is stored in a storage medium and includes several instructions for a computer device (which can be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the method described in each embodiment of the present invention. The aforementioned storage medium includes: various media that can store program codes, such as a USB flash drive, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk or an optical disk.

[0083] The present invention also provides a non-transitory computer-readable storage medium having a computer program stored thereon, wherein the computer program implements a cardiac magnetic field measurement method when executed by a processor. The method comprises:

[0084] Obtain the dynamic background magnetic field and spatial position coordinates measured by the background magnetic field measurement module;

[0085] Get the number of control coils in the control coil module;

[0086] According to the dynamic background magnetic field, the spatial position coordinates and the number of control coils, a current of the control coil module for shielding the dynamic background magnetic field is obtained;

[0087] After the current is passed into the control coil module, the signal magnetic field measurement module measures the magnetic field data of the actual signal source.

[0088] The device embodiments described above are merely illustrative, wherein the units described as separate components may or may not be physically separated, and the components displayed as units may or may not be physical units, that is, they may be located in one place, or they may be distributed on multiple network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the scheme of this embodiment. Ordinary technicians in this field can understand and implement it without paying creative labor.

[0089] Through the description of the above implementation methods, those skilled in the art can clearly understand that each implementation method can be implemented by means of software plus a necessary general hardware platform, and of course, it can also be implemented by hardware. Based on this understanding, the above technical solution is essentially or the part that contributes to the prior art can be embodied in the form of a software product, and the computer software product can be stored in a computer-readable storage medium, such as ROM / RAM, a disk, an optical disk, etc., including a number of instructions for a computer device (which can be a personal computer, a server, or a network device, etc.) to execute the methods described in each embodiment or some parts of the embodiments.

[0090] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these 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.

Claims

1. A cardiac magnetic field measurement system, characterized in that: include: A signal magnetic field measurement module, used to measure the spatial magnetic field at the signal source; A background magnetic field measurement module, used to measure the dynamic background magnetic field at the signal source; as well as A control coil module, located between the signal magnetic field measurement module and the background magnetic field measurement module, and surrounding the signal magnetic field measurement module, and used for providing a magnetic field with multiple degrees of freedom for shielding the dynamic background magnetic field; The background magnetic field measurement module and the control coil module are used to calculate the current used by the control coil module to shield the dynamic background magnetic field according to the dynamic background magnetic field, the spatial position coordinates and the number of control coils, including: Based on the decomposition of the magnetic field B(x, y, z) in space into three components of x, y and z, the magnetic field B(x, y, z) in space is expressed as formula (1): Wherein, x, y, z are the spatial position coordinates; B0 is the uniform field, and K is the spatial first-order gradient field matrix; The dynamic background magnetic field B is obtained by fitting formula (1) based on the least squares method: bg , the dynamic background magnetic field B bg It is expressed as formula (2): Where, t represents time; B bg0 (t) represents the 0th-order uniform field at time t; K bg (t) represents the gradient at time point t; B bg_x0 (t) represents the uniform field in the x direction at time point t; K bg_xx (t) represents the gradient field in the x direction at time point t; The number of control coils is 12; The magnetic field of the degrees of freedom provided by each layer of control coil forms a diagonal matrix M expressed as formula (3): Among them, M x0 It means that when the first coil is passed with a current of 1A, M is generated in the x direction. x0 Tesla's magnetic field; M zy It means that when the 12th coil is fed with a current of 1A, a magnetic field M is generated in the z direction. zy Tesla per meter y-direction gradient field; The control coil magnetic field B coil It is expressed as formula (4): Among them, B coil0 represents the 0th order uniform field generated by the coil, K coil represents the gradient field generated by the coil; B coil_x0 , B coil_y0 and B coil_z0 are the uniform fields in the x direction, y direction and z direction of the coil respectively; K coil_xx represents the gradient field of one component of the coil; When the control coil magnetic field B coil For the dynamic background magnetic field B bg When magnetic field shielding is performed, equation (5) is obtained: Expand formula (5) according to formula (2) and formula (4) to obtain formula (6): Multiply formula (6) by M -1 Formula (7) is obtained: The current of the dynamic background magnetic field is represented by I n (n=1~12).

2. The cardiac magnetic field measurement system according to claim 1, characterized in that: The signal magnetic field measurement module includes a plurality of signal magnetic field measurement probes, and the signal magnetic field measurement probes include at least one of a fluxgate probe, a magnetoresistive probe and a Hall probe, and the plurality of signal magnetic field measurement probes are arranged in a matrix.

3. The cardiac magnetic field measurement system according to claim 1, characterized in that: The background magnetic field measurement module includes one or more background magnetic field measurement probes, and the background magnetic field measurement probes include at least one of a fluxgate probe, a magnetoresistive probe and a Hall probe.

4. The cardiac magnetic field measurement system according to any one of claims 1 to 3, characterized in that: The control coil module includes a plurality of coils, and the plurality of coils are arranged in layers.

5. The cardiac magnetic field measurement system according to claim 4, characterized in that: The control coil module is used to provide a magnetic field with 9 to 12 degrees of freedom.

6. The cardiac magnetic field measurement system according to claim 4, characterized in that: The control coil module is a hollow parallelepiped, and the signal magnetic field measurement module is located in the parallelepiped.

7. The cardiac magnetic field measurement system according to claim 4, characterized in that: The thickness of each layer of coils among the plurality of coils is 0.15mm-0.25mm, the spacing between the coils is 0.15mm-0.25mm, the length of each layer of coils is 11cm-13cm, the width is 10cm-13cm, and the height is 2cm-4cm.

8. A cardiac magnetic field measurement method based on the system according to any one of claims 1 to 7, characterized in that: The following steps are involved: Obtain the dynamic background magnetic field and spatial position coordinates measured by the background magnetic field measurement module; Get the number of control coils in the control coil module; Calculating the current of the control coil module for shielding the dynamic background magnetic field according to the dynamic background magnetic field, the spatial position coordinates and the number of control coils; After the current is passed into the control coil module, the signal magnetic field measurement module is used to measure the magnetic field of the actual signal source; The method of calculating the current of the control coil module for shielding the dynamic background magnetic field according to the dynamic background magnetic field, the spatial position coordinates and the number of control coils includes: Based on the decomposition of the magnetic field B(x, y, z) in space into three components of x, y and z, the magnetic field B(x, y, z) in space is expressed as formula (1): Wherein, x, y, z are the spatial position coordinates; B0 is the uniform field, and K is the spatial first-order gradient field matrix; The dynamic background magnetic field B is obtained by fitting formula (1) based on the least squares method: bg , the dynamic background magnetic field B bg It is expressed as formula (2): Where, t represents time; B bg0 (t) represents the 0th-order uniform field at time t; K bg (t) represents the gradient at time point t; B bg_x0 (t) represents the uniform field in the x direction at time point t; K bg_xx (t) represents the gradient field in the x direction at time point t; The number of control coils is 12; The magnetic field of the degrees of freedom provided by each layer of control coil forms a diagonal matrix M expressed as formula (3): Among them, M x0 It means that when the first coil is passed with a current of 1A, M is generated in the x direction. x0 Tesla's magnetic field; M zy It means that when the 12th coil is fed with a current of 1A, a magnetic field M is generated in the z direction. zy Tesla per meter y-direction gradient field; The control coil magnetic field B coil It is expressed as formula (4): Among them, B coil0 represents the 0th order uniform field generated by the coil, K coil represents the gradient field generated by the coil; B coil_x0 , B coil_y0 and B coil_z0 are the uniform fields in the x direction, y direction and z direction of the coil respectively; K coil_xx represents the gradient field of one component of the coil; When the control coil magnetic field B coil For the dynamic background magnetic field B bg When magnetic field shielding is performed, equation (5) is obtained: Expand formula (5) according to formula (2) and formula (4) to obtain formula (6): Multiply formula (6) by M -1 Formula (7) is obtained: The current of the dynamic background magnetic field is represented by I n (n=1~12).

9. An electronic device comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein: When the processor executes the program, the cardiac magnetic field measurement method as claimed in claim 8 is implemented.

10. A non-transitory computer-readable storage medium having a computer program stored thereon, characterized in that: When the computer program is executed by a processor, the cardiac magnetic field measurement method as claimed in claim 8 is implemented.

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