A dual-plane coil based magnetomyography device

Abstract

The application discloses a kind of muscle magnetic detection devices based on double plane coil, comprising, magnetic shielding, cross-sectional shape is rectangle;Non-magnetic pressure sensor assembly, fixed at one end of magnetic shielding and its grip end is located in magnetic shielding;Muscle magnetic detection probe assembly is set at the other end of magnetic shielding, muscle magnetic detection probe assembly is located outside magnetic shielding away from the opening end of magnetic shielding and is used for arm to extend into, muscle magnetic detection probe assembly other end is used for gripping the grip end of non-magnetic pressure sensor assembly;Two double plane coil groups are fixed at the opposite two inner walls of magnetic shielding, and muscle magnetic detection probe assembly is located between two double plane coil groups.The application can realize the deterioration problem of the internal magnetic field environment of single-end opening magnetic shielding device, and provide a kind of weak magnetic test environment with high stability and small gradient.

Description

Technical Field

[0001] This invention belongs to the technical field of myoma detection equipment, and particularly relates to a myoma detection device based on a dual-plane coil. Background Technology

[0002] Muscle signals in the human body can be used not only to diagnose muscle damage and check for conditions such as uterine contractions during pregnancy, but also to some extent to predict disability and even death. For decades, electromyography (EMG) and electromyography (EMG) have been used to study these technologies. Figure 1 Electromyography (EMG) is an important method for assessing peripheral nerve and muscle diseases. During this process, nerves are briefly electrically stimulated, and nerve conduction is indirectly determined by the behavior of the muscles innervated by the nerves. The resulting magnetic field of the muscle response can also be recorded using a novel uncooled magnetometer, which is very attractive for various medical applications. Compared to EMG, MMG has significant advantages, such as eliminating the need for electrode-skin contact, thus avoiding skin preparation, potential infection, or allergic reactions, and the magnetic field signal is unaffected by the fat layer, making the study of muscle magnetic field signals crucial.

[0003] The magnitude of muscle magnetic field signals ranges from tens to hundreds of pTesla levels, and their study primarily utilizes a superconducting quantum interference device (SQUID). In recent years, the successful development of the SERF magnetometer has provided a new approach for further in-depth research on muscle magnetic signals. However, muscle magnetic measurement devices based on SERF magnetometers require a highly stable, low-gradient weak magnetic testing environment. Single-ended magnetic shielding devices significantly deteriorate the internal magnetic environment, causing the SERF magnetometer to malfunction. Summary of the Invention

[0004] To address the aforementioned technical problems, this invention proposes a myomagnetic detection device based on a dual-plane coil, which can solve the problem of deterioration of the internal magnetic field environment of a single-ended open magnetic shielding device and provide a highly stable, small-gradient weak magnetic testing environment.

[0005] To achieve the above objectives, the present invention provides a myomagnetic detection device based on a dual-plane coil, comprising:

[0006] The magnetic shielding component has a rectangular cross-sectional shape.

[0007] A non-magnetic pressure sensor assembly is fixed to one end of the magnetic shielding and its gripping end is located inside the magnetic shielding.

[0008] A myoma magnetic detection probe assembly is disposed at the other end of the magnetic shield. The open end of the myoma magnetic detection probe assembly away from the magnetic shield is located outside the magnetic shield and is used for arm insertion. The other end of the myoma magnetic detection probe assembly is used for gripping the gripping end of the non-magnetic pressure sensor assembly.

[0009] Two dual-plane coil groups are respectively fixed on the two opposite inner walls of the magnetic shield, and the myomagnetic detection probe assembly is located between the two dual-plane coil groups.

[0010] Furthermore, the magnetic shielding component is a magnetic shielding box, and the magnetic shielding box has a cuboid structure.

[0011] Furthermore, the dual-plane coil group includes a plurality of dual-plane coils arranged in sequence, and the side of the dual-plane coil closest to the inner wall of the magnetic shielding box is fixedly connected to the inner wall of the magnetic shielding box.

[0012] Furthermore, the wiring connection of the dual-plane coil is twisted in two.

[0013] Furthermore, the gripping end of the non-magnetic pressure sensor assembly is a non-magnetic airbag, which is fixed to the inner wall of the magnetic shielding box. The air outlet of the non-magnetic airbag is connected to a non-magnetic pipe, and the other end of the non-magnetic pipe extends out of the magnetic shielding box and is connected to a detection element.

[0014] Furthermore, the detection element includes a pressure-sensitive element fixed to the outer wall of the magnetic shielding box, the pressure-sensitive element being connected to the non-magnetic pipe, and the pressure-sensitive element being electrically connected to an external processing circuit.

[0015] Furthermore, the myomagnetic detection probe assembly includes a non-magnetic detection arm, the open end of which is located outside the magnetic shielding box and is used for the arm to be inserted, and the myomagnetic detection probe group is fixedly arranged on the surface of the non-magnetic detection arm.

[0016] Compared with the prior art, the present invention has the following advantages and technical effects:

[0017] By applying corresponding current to the two double-plane coil groups, the magnetic field offset in the single-ended open magnetic shielding device is effectively counteracted, the magnetic field uniformity of the target area is improved, and it is beneficial to carry out the myoma detection experiment. Attached Figure Description

[0018] The accompanying drawings, which form part of this application, are used to provide a further understanding of this application. The illustrative embodiments and descriptions of this application are used to explain this application and do not constitute an undue limitation of this application. In the drawings:

[0019] Figure 1 A perspective view of the myomagnetic detection device;

[0020] Figure 2 This is a three-dimensional diagram of a two-plane coil;

[0021] Figure 3 A 3D view of the magnetic myocardiogram (MMI) detection probe assembly;

[0022] Figure 4 A 3D view of a non-magnetic pressure sensor assembly;

[0023] Figure 5 This is a flowchart illustrating the operating principle of the myomagnetic detection device.

[0024] Figure 6 A three-dimensional diagram showing the positional relationship between the dual-plane coil and the magnetic myocardiogram detection probe assembly;

[0025] Among them, 1-non-magnetic pressure sensor assembly, 101-non-magnetic airbag, 102-non-magnetic pipe, 103-pressure-sensitive element, 104-external processing circuit, 2-magnetic shielding box, 3-dual-plane coil, 4-myomagnetic detection probe assembly, 401-non-magnetic detection arm, 402-myomagnetic detection probe group. Detailed Implementation

[0026] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0027] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0028] Reference Figure 1-6 This invention provides a myomagnetic detection device based on dual-plane coils, comprising: a magnetic shield with a rectangular cross-section; a non-magnetic pressure sensor assembly 1 fixed to one end of the magnetic shield with its gripping end located inside the magnetic shield; a myomagnetic detection probe assembly 4 disposed at the other end of the magnetic shield, the open end of the myomagnetic detection probe assembly 4 away from the magnetic shield being located outside the magnetic shield and used for arm insertion, the other end of the myomagnetic detection probe assembly 4 being used for gripping the gripping end of the non-magnetic pressure sensor assembly 1; and two dual-plane coil groups respectively fixed to two opposite inner walls of the magnetic shield, with the myomagnetic detection probe assembly 4 located between the two dual-plane coil groups.

[0029] The magnetic shield has a rectangular cross-section, with a non-magnetic pressure sensor assembly 1 and a myomagnetic detection probe assembly 4 installed at its two ends. The myomagnetic detection probe assembly 4 is wearable. The human arm is inserted into the myomagnetic detection probe assembly 4 and grasps the grasping end of the non-magnetic pressure sensor assembly 1, reducing the air inside the grasping end. By monitoring and analyzing the amount of air outflow, the condition of the muscles can be diagnosed.

[0030] The two sets of dual-plane coils work together to ensure that the myomagnetic detection probe assembly 4 operates within a uniform magnetic field region.

[0031] The scheme was further optimized so that the magnetic shielding component is a magnetic shielding box 2, which has a cuboid structure.

[0032] The magnetic shielding box 2 is made of magnetic shielding material and has an opening at one end. It is used to place the magnetic muscle detection probe assembly 4 into or out of the magnetic shielding box 2. At the same time, the shielding coefficient of the magnetic shielding box 2 should be as large as possible. The shielding coefficient is calculated as follows:

[0033]

[0034] Where S represents the shielding coefficient, B0 represents the magnetic field strength at the center of the target area of ​​the magnetic shielding box 2 when the magnetic shielding box 2 is present, and B1 represents the magnetic field strength at the same location when the magnetic shielding box 2 is absent. This parameter characterizes the shielding performance of the magnetic shielding box 2.

[0035] In one embodiment of the present invention, the internal dimensions of the magnetic shielding box 2 are 250mm×250mm×650mm. This size, while meeting the arm size parameters in the "Chinese Adult Anthropometric Dimensions (GB10000-88)", enables the shielding coefficient to meet the requirements of subsequent design. The box has a single-end opening for the arm to be inserted.

[0036] Further optimize the plan, referring to Figure 1 , Figure 2 The dual-plane coil group includes several dual-plane coils 3 arranged in sequence, with the side of the dual-plane coil 3 closest to the inner wall of the magnetic shielding box 2 being fixedly connected to the inner wall of the magnetic shielding box 2.

[0037] Understandably, several pairs of dual-plane coils 3 are placed parallel to the MRI detection probe assembly 4, and the dual-plane coils 3 on the two sets of dual-plane coils are set one-to-one. The function of the dual-plane coils 3 is to generate a reverse magnetic field over a large range in the rectangular magnetic shielding box 2 for compensation and to suppress external magnetic field fluctuations, thereby forming a zero magnetic environment for the MRI detection probe assembly 4 to work.

[0038] According to the Biot-Savart law, taking the generation of a uniform magnetic field Bx as an example, the magnetic field produced by the coil on the XOY plane at the point (x,y,z) is:

[0039]

[0040] Among them, J y dA' represents the current density in the y direction on the XOY plane, μ0 is the permeability of vacuum, z and z' are the z coordinates of the field point and the source point, respectively, and r-r' is the distance between the field point and the source point.

[0041] Then, points are selected uniformly within the target region, resulting in an overdetermined system of equations:

[0042] B x (x, y, z) = B targ et

[0043] Where Btarget is the setpoint for the magnetic field generated by the coil. Solving this overdetermined system of equations yields the current density J. y The distribution on the XOY plane leads to the coil configuration.

[0044] The shimming and gradient coils designed in this way can effectively compensate for residual magnetism in the magnetic shielding device and fluctuations in the ambient magnetic field, providing a good magnetic working environment and a higher signal-to-noise ratio for the subsequent operation of the magnetometer.

[0045] The dual-plane coil 3 is preferably fixed to the inner wall of the magnetic shielding box 2 using resin material to ensure that the relative position of the coil with respect to the magnetic shielding device remains unchanged.

[0046] The design was further optimized by twisting the wires at the connection points of the dual-plane coil 3. Twisting the wires reduces the impact of current entering and exiting the wires on the internal magnetic field of the magnetic shielding box 2.

[0047] Further optimize the plan, referring to Figure 4 The gripping end of the non-magnetic pressure sensor assembly 1 is a non-magnetic airbag 101. The non-magnetic airbag 101 is fixed to the inner wall of the magnetic shielding box 2. The air outlet of the non-magnetic airbag 101 is connected to a non-magnetic pipe 102. The other end of the non-magnetic pipe 102 extends out of the magnetic shielding box 2 and is connected to a detection element.

[0048] The scheme is further optimized. The detection component includes a pressure-sensitive element 103 fixed on the outer wall of the magnetic shielding box 2. The pressure-sensitive element 103 is connected to the non-magnetic pipe 102 and is electrically connected to an external processing circuit 104.

[0049] The non-magnetic airbag 101 is made of non-magnetic material. The non-magnetic airbag 101 and the pressure-sensitive element 103 are fixed to the inner and outer walls of the magnetic shielding box 2 respectively using resin material. By squeezing the non-magnetic airbag 101, the grip force signal is converted into a pressure signal. Then, the gas is forced to the outside of the magnetic shielding box 2 through the non-magnetic pipe 102, and the resulting pressure change is converted into a corresponding electrical signal by the pressure-sensitive element 103. By filtering, shaping, and comparing the electrical signal, and combining it with the myomagnetic signal collected by the magnetometer, a preliminary diagnosis of the muscle condition at the probe location can be made.

[0050] The magnetic shielding box 2 has a hole on its end face for the non-magnetic pipe 102 to pass through.

[0051] Specifically, the external processing circuit 104 includes a filtering circuit and a shaping and comparison circuit, which are used to improve the signal-to-noise ratio of the muscle magnetic field signal, facilitating subsequent diagnosis of the muscle condition.

[0052] Further optimize the plan, referring to Figure 3 The myoma detection probe assembly 4 includes a non-magnetic detection arm 401. The open end of the non-magnetic detection arm 401 is located outside the magnetic shielding box 2 and is used for the arm to be inserted. The myoma detection probe assembly 402 is fixedly arranged on the surface of the non-magnetic detection arm 401.

[0053] Understandably, the wearable non-magnetic detection arm 401 is fixed to the muscle site to be tested in a uniform magnetic field area. It is made of non-magnetic plastic material to ensure that the position of the magnetometer and the relative position of the muscle site to be tested remain unchanged. An array of myoma detection probes 402 is arranged on it, allowing the myoma detection probes 402 to operate within the uniform magnetic field area. During operation, the subject's arm is inserted into the single-ended open non-magnetic detection arm 401 to collect the subject's muscle magnetic field signals in real time.

[0054] Specifically, refer to Figure 5 In actual operation, the subject first inserts their arm, equipped with the non-magnetic detection arm 401 and the myoma detection probe assembly 402, into the single-ended open magnetic shielding box 2 and grasps the non-magnetic airbag 101. A corresponding current is applied to the dual-plane coil 3, creating a zero-magnetic space near the myoma detection probe assembly 402. The subject then firmly grasps the non-magnetic airbag 101, which converts the grip force signal into a pressure signal. The gas is then forced through the non-magnetic pipe 102 to the outside of the magnetic shielding box 2, and the resulting pressure change is converted into a corresponding electrical signal by the pressure-sensitive element 103. By filtering, shaping, and comparing the electrical signal, combined with the myoma signal collected by the magnetometer, a preliminary diagnosis of the muscle condition at the probe location can be made.

[0055] The above are merely preferred embodiments of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A myomagnetic detection device based on a dual-plane coil, characterized in that: include, The magnetic shielding component has a rectangular cross-sectional shape. A non-magnetic pressure sensor assembly (1) is fixed at one end of the magnetic shielding and its gripping end is located inside the magnetic shielding; A myoma detection probe assembly (4) is disposed at the other end of the magnetic shield. The open end of the myoma detection probe assembly (4) away from the magnetic shield is located outside the magnetic shield and is used for arm insertion. The other end of the myoma detection probe assembly (4) is used to grasp the gripping end of the non-magnetic pressure sensor assembly (1). Two dual-plane coil groups are respectively fixed on the two opposite inner walls of the magnetic shielding, and the myomagnetic detection probe assembly (4) is located between the two dual-plane coil groups; The magnetic shielding component is a magnetic shielding box (2), and the magnetic shielding box (2) has a cuboid structure; The dual-plane coil group includes several dual-plane coils (3) arranged in sequence, and the side of the dual-plane coil (3) close to the inner wall of the magnetic shielding box (2) is fixed to the inner wall of the magnetic shielding box (2); The wiring connection of the dual-plane coil (3) is twisted in two.

2. The myoma magnetic detection device based on dual-plane coils according to claim 1, characterized in that: The gripping end of the non-magnetic pressure sensor assembly (1) is a non-magnetic airbag (101), which is fixed to the inner wall of the magnetic shielding box (2). The air outlet of the non-magnetic airbag (101) is connected to a non-magnetic pipe (102), and the other end of the non-magnetic pipe (102) extends out of the magnetic shielding box (2) and is connected to a detection element.

3. The myoma magnetic detection device based on dual-plane coils according to claim 2, characterized in that: The detection device includes a pressure-sensitive element (103) fixed to the outer wall of the magnetic shielding box (2), the pressure-sensitive element (103) is connected to the non-magnetic pipe (102), and the pressure-sensitive element (103) is electrically connected to an external processing circuit (104).

4. The myoma magnetic detection device based on dual-plane coils according to claim 1, characterized in that: The myoma detection probe assembly (4) includes a non-magnetic detection arm (401), the open end of which is located outside the magnetic shielding box (2) and is used for the arm to be inserted. The surface of the non-magnetic detection arm (401) is fixed with an array of myoma detection probes (402).

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