A magnetic stimulation device

Abstract

The present application discloses a magnetic stimulation device, which includes a positioning and fixing connection device and an electromagnetic wave emitting device. The positioning and fixing connection device includes a spherical fixing frame composed of two identical hemispherical frames. The electromagnetic wave emitting device includes first, second, and third electromagnetic generating coil groups, and each electromagnetic generating coil group includes two coils symmetrically arranged about the center. The first, second, and third electromagnetic generating coil groups respectively form a pair of dual-focus magnetic stimulation coils, which emit electromagnetic waves towards the center point of the spherical fixing frame. Since the magnetic stimulation device includes three pairs of dual-focus magnetic stimulation coils, the magnetic stimulation signal is focused, so that the stimulation depth of transcranial magnetic stimulation can be controlled, the stimulation focus can be controlled, the stimulation range can be more controllable, and on the premise of greatly improving the treatment effect of transcranial magnetic stimulation, the complications caused by magnetic stimulation can be reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of biomedical engineering, and particularly relates to a magnetic stimulation device. Background Art

[0002] Transcranial magnetic stimulation (TMS) is an important technology in the field of biomedical engineering. It is a technology based on the principle of electromagnetic induction of the brain electric field. Through a pulsed electromagnetic field with a high field strength, it can penetrate the skull and act on nerve tissues at a deeper position for nerve stimulation and nerve regulation. Moreover, it does not require penetrating the skin to install the device, and has advantages such as non-invasive and painless. The magnetic field used for TMS can have an intensity and density sufficient to depolarize neurons. And when TMS pulses are repeatedly applied, when the parameters of magnetic stimulation (frequency, amplitude, pulse width, pulse width gradient, etc.) are selected, transcranial magnetic stimulation can regulate the excitability of the cerebral cortex, and can even regulate the excitability of the cortex throughout the stimulation period. In the past few decades, the application of TMS in studying the cognition of various nervous system and mental diseases, the relationship between brain behavior and pathophysiology has increased rapidly.

[0003] In the transcranial magnetic stimulation systems applied in the prior art, during actual use, transcranial magnetic stimulation will have adverse side effects such as slight pain, discomfort, mental fluctuations, fainting, syncope, and even epileptic seizures. The main reasons for these adverse side effects are that the stimulation range area of TMS is large, and the selection of magnetic stimulation power and magnetic stimulation method is inappropriate, etc. Among them, the most important reason is that the magnetic stimulation target positioning is inaccurate, and it cannot accurately target the magnetic stimulation target or area for accurate positioning, and thus cannot achieve accurate quantitative and range-defined magnetic stimulation. Summary of the Invention

[0004] The main technical problem to be solved by the present invention is that the magnetic stimulation coil of the transcranial magnetic stimulation device in the prior art has the disadvantages of shallow stimulation depth and inability to perform magnetic focusing.

[0005] According to a first aspect, in one embodiment, a magnetic stimulation device is provided, including a positioning and fixing connection device and an electromagnetic wave emitting device;

[0006] The positioning and fixing connection device includes a spherical fixing frame, and the spherical fixing frame is composed of two completely identical hemispherical frames; the spherical fixing frame is used for fixedly connecting the skull and setting the target area to be magnetically stimulated at the center point of the spherical fixing frame;

[0007] The electromagnetic wave emitting device includes a first electromagnetic generating coil group, a second electromagnetic generating coil group, and a third electromagnetic generating coil group; the first electromagnetic generating coil group includes two first coils with the same structure, and the two first coils are symmetrically arranged about the center on the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame; the second electromagnetic generating coil group includes two second coils with the same structure, and the two second coils are symmetrically arranged about the center on the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame; the third electromagnetic generating coil group includes two third coils with the same structure, and the two third coils are symmetrically arranged about the center on the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame;

[0008] The first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are respectively used to form a pair of dual-focus magnetic stimulation coil pairs to emit electromagnetic waves to the center point of the spherical fixing frame for magnetic stimulation of the target area.

[0009] In one embodiment, the winding turns, shapes, materials, and / or dimensions of the first coil, the second coil, and the third coil are the same;

[0010] and / or, the materials of the first coil, the second coil, and the third coil include copper, iron, silver, and / or gold;

[0011] and / or, the shapes of the first coil, the second coil, and the third coil include oval, figure-eight, or H-shaped.

[0012] In one embodiment, the winding turns of the first coil, the second coil, and the third coil are 20 to 60 turns;

[0013] and / or, the effective diameters of the first coil, the second coil, and the third coil are 200 mm;

[0014] and / or, the size of the winding wire of the first coil, the second coil, and the third coil is 3 mm 2 .

[0015] In one embodiment, the central axes of the first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are coplanar.

[0016] In one embodiment, the included angles between the central axes of the first electromagnetic generating coil group and the second electromagnetic generating coil group and the central axis of the third electromagnetic generating coil group are the same.

[0017] In one embodiment, one of the first coils of the first electromagnetic generating coil group is tangent to one of the second coils of the second electromagnetic generating coil group, and the tangent point is located at the center point of one of the third coils of the third electromagnetic generating coil group.

[0018] In one embodiment, the diameter of the outer spherical surface of the spherical fixing frame is 720 mm, and the diameter of the inner spherical surface of the spherical fixing frame is 700 mm;

[0019] And / or, the material of the spherical fixing frame is polyvinyl chloride synthetic resin material.

[0020] In one embodiment, a stimulation driving control module is further included, which is electrically connected to the first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group respectively; the stimulation driving control module is used to perform timing control of the driving current on the first coil of the first electromagnetic generating coil group, the second coil of the second electromagnetic generating coil group, and the third coil of the third electromagnetic generating coil group simultaneously or respectively according to the preset coil stimulation intensity and stimulation timing.

[0021] In one embodiment, the currents of the stimulation driving control module driving the first coil, the second coil, and the third coil are 1 A to 10 kA;

[0022] In one embodiment, the frequencies of the stimulation driving control module driving the first coil, the second coil, and the third coil are 1 kHz to 10 kHz.

[0023] According to the magnetic stimulation device of the above embodiment, since the magnetic stimulation device includes three groups of dual-focus magnetic stimulation coil pairs, the magnetic stimulation signal is focused, so that the stimulation depth of transcranial magnetic stimulation can be controlled, the stimulation focus can be controlled, and the stimulation range can be controlled. On the premise of greatly improving the treatment effect of transcranial magnetic stimulation, the complications caused by magnetic stimulation are reduced.

[0024] The magnetic stimulation device provided by the present application has a magnetic stimulation focusing function, and is a new type of transcranial magnetic coil that can perform deep magnetic stimulation, realizing controllable depth of coil magnetic stimulation and focusing control of magnetic stimulation intensity, and can achieve precise magnetic stimulation during the transcranial magnetic treatment process, greatly improving the treatment effect of transcranial magnetic stimulation. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 It is a schematic structural diagram of a magnetic stimulation device in one embodiment;

[0026] Figure 2 It is a schematic diagram of magnetic stimulation timing control of a magnetic stimulation device in one embodiment;

[0027] Figure 3Schematic diagram of the connection of the spherical fixing bracket in an embodiment;

[0028] Figure 4 Schematic diagram of the connection of the spherical fixing bracket in an embodiment. Detailed implementation manners

[0029] The present invention will be further described in detail below in conjunction with the accompanying drawings through specific implementation manners. Similar elements in different implementation manners adopt related similar element numbers. In the following implementation manners, many detailed descriptions are provided to enable a better understanding of the present application. However, those skilled in the art can easily recognize that some of the features can be omitted in different situations, or can be replaced by other elements, materials, or methods. In some cases, some operations related to the present application are not shown or described in the specification to avoid the core part of the present application being overwhelmed by excessive descriptions. For those skilled in the art, it is not necessary to describe these related operations in detail, and they can fully understand the related operations based on the description in the specification and the general technical knowledge in the art.

[0030] In addition, the features, operations, or characteristics described in the specification can be combined in any appropriate manner to form various implementation manners. At the same time, the steps or actions in the method description can also be reordered or adjusted in an obvious manner by those skilled in the art. Therefore, the various sequences in the specification and the drawings are only for clearly describing a certain embodiment and do not mean that they are the necessary sequences, unless it is stated that a certain sequence must be followed.

[0031] The serial numbers assigned to the components herein, such as "first", "second", etc., are only used to distinguish the described objects and do not have any sequential or technical meanings. The "connection" and "coupling" mentioned in the present application, unless otherwise specified, both include direct and indirect connections (couplings).

[0032] In the prior art, the usual depth of transcranial magnetic brain stimulation is generally about 1-3 centimeters, which can only stimulate the superficial areas of the brain and is difficult to reach the deep areas of the brain such as the frontal lobe, thalamus, cingulate gyrus, putamen, caudate nucleus, hippocampus, ventral striatum, and amygdala, or it is difficult to perform precise magnetic stimulation on the deep areas of the brain. Just by increasing the magnetic field intensity of the transcranial magnetic stimulation coil, adverse effects such as headache, fainting, and even induced epilepsy limit the application of transcranial magnetic brain stimulation. It is of great significance to urgently develop a new type of transcranial magnetic stimulator device with the ability of deep brain magnetic stimulation or deep-focusing magnetic stimulation function.

[0033] In TMS technology, brief magnetic pulses are used to cause depolarization of targeted neurons in the brain using Faraday's law of electromagnetic induction. When TMS is performed in a repetitive manner (termed rTMS), long-term potentiation-like or depression-like effects can be achieved. Conventional magnetic stimulation techniques and coils are mostly designed for surface stimulation of brain tissue but generally cannot deliver deeper stimulation. Since surface stimulation does not cause effective stimulation of the ventral prefrontal cortex and other reward- and emotion-related brain structures such as the nucleus accumbens (ventral striatum), it is predictable that deeper brain stimulation can more effectively treat major depressive disorder and other psychiatric and neurological diseases. Stimulating deep brain regions (dTMS), known as deep TMS, requires high intensity and accuracy, which cannot be achieved by currently available conventional magnetic stimulators using standard coil configurations without causing undesirable side effects such as seizures or other problems associated with overstimulating cortical regions. In the past, the rTMS process could not directly stimulate targets more than 2 cm below the skull surface. Deep rTMS technology is being developed to improve the depth penetration of the electromagnetic field using an H-coil, in which multiple windings are arranged such that the magnetic fields generated thereby are summed together to allow direct simulation down to 4 cm below the skull surface.

[0034] The geometry of the TMS coil plays an important role in determining the focus and penetration depth of the induced electric field responsible for stimulation. Many coils designed in the past have employed different geometric layouts, but none has shown a greater focal length than the figure-eight coil while maintaining the field strength required for deep stimulation of the brain surface. The breakthrough development of the TMS coil can stimulate beyond the resolution of the figure-eight coil, which will provide the opportunity to stimulate specific depth-organizing neural circuits that play important roles in neurological diseases. At the same time, it can also avoid stimulating brain regions adjacent to the stimulation site for specific disease management goals.

[0035] In order to effectively trigger action potentials in neural structures (such as deep target sites in the brain, cingulate gyrus, thalamus, etc.), sufficient stimulation must be generated within a shortest time period less than that required for the target neural membrane to repolarize. Otherwise, the stimulation threshold for generating action potentials will not be reached. Neurons are usually highly interconnected, and the actual final target neurons to be stimulated may receive inputs from multiple sources of stimulation. Stimulation of the target deep brain region can be achieved by optimizing the power applied to the TMS electromagnet without stimulating or inhibiting the nearby non-target brain regions, especially the brain regions between the target deep brain region and the TMS electromagnet, so that the electromagnetic field reaches the target sum to achieve the desired stimulation. In the patent solution, by carefully arranging and controlling multiple magnetic stimulation coils, using the magnetic field enhancement effect on the deep target brain region and the cumulative reinforcement effect of biological stimulation, synchronous stimulation of multiple stimulation points in the deep target brain region or adjacent regions is achieved, and effective stimulation of the deep target brain region is realized.

[0036] The generation of evoked action potentials in neuron cells by magnetic stimulation is affected by the stimulation threshold. When the stimulation intensity generated by the magnetic stimulation coil in the neuron is greater than the evoked action potential threshold of the neuron cell, the neuron cell may generate evoked action potentials. In this case, it is required that the magnetic stimulation coil generates a very strong magnetic field in the deep target brain region. If a traditional single magnetic stimulation coil is used, considering that the attenuation of the magnetic field intensity is inversely proportional to the square of the distance of magnetic field transmission, the magnetic field intensity of a single magnetic stimulation coil will be very large, which will stimulate the high-intensity stimulation of the deep target brain region and the non-stimulated target brain regions on the path of the magnetic stimulation coil (and the magnetic stimulation intensity is greater than the magnetic stimulation intensity of the deep target brain region), and the size of the single magnetic stimulation coil is also large, making it inconvenient to use. In the solution of the present invention, the synthesis effect of the magnetic field is utilized, and multiple magnetic stimulation coils precisely configured and controlled in space and time are used to stimulate the deep target brain region. While the stimulation magnetic field intensity of a single magnetic stimulation coil is much lower than the magnetic stimulation threshold of the evoked action potential, the synthesized stimulation magnetic field intensity in the deep target brain region can be higher than the magnetic stimulation threshold of the evoked action potential, and at the same time, the stimulation magnetic field intensity and the coil size of a single magnetic stimulation coil can be greatly reduced; According to the principles of neurobiology, when neuron cells receive multiple stimulations (not only magnetic stimulations) below the magnetic stimulation threshold of the evoked action potential, they can also probabilistically generate evoked action potentials. By precisely arranging multiple magnetic stimulation coils as magnetic stimulation induced compensation coils, multi-point stimulation of the deep target brain region can be achieved, the probability of generating evoked action potentials in the deep target brain region can be increased, and thus the overall effect of magnetic stimulation can be improved.

[0037] There are many types of commonly used transcranial magnetic stimulation coils, such as circular, figure-eight, butterfly, H-shaped, etc. The focusing and stimulation depth of various coils are different. The H-shaped coil can achieve deep target brain stimulation, but the H-shaped coil has a complex structure, high cost, and poor focusing of the stimulation magnetic field. The present invention adopts a double equal-circular parallel coaxial paired magnetic stimulation coil model. The magnetic field strength is the largest on the axis of the two circular coils, and the approximate magnetic field B is:

[0038] B = 0.5×μ 0 ×N×I×R 2 ×[R 2 +(d / 2 + x) 2 -（3 / 2） ;

[0039] μ 0 = 4×π×10 -7 Tm / A;

[0040] Wherein, N is the number of turns of the coil, I is the coil current, R is the radius of the effective equivalent circular area of the coil, x is the distance from a point on the axis of the coil to the center of the coil, and d is the effective width of the coil.

[0041] By reasonably arranging such multiple groups of double equal-circular parallel coaxial magnetic stimulation coils in space, the magnetic field synthesis at a specific spatial position can be achieved, and the precise focusing of magnetic stimulation and the enhancement of the synthetic stimulation magnetic field can be realized.

[0042] In the existing transcranial magnetic stimulation technology treatment equipment, only a single coil aimed at directly affecting the superficial cerebral cortex area is used, and the stimulation target position in the network is undetermined. Transcranial magnetic stimulation usually affects the main stimulation site on the superficial cortex, rather than the site of deep neural tissue that is synaptically connected to the main stimulation site. However, many diseases and symptoms of diseases may benefit from direct neuromodulation of deeper brain target areas. This directly leads to poor treatment effects of transcranial magnetic stimulation, a long treatment course cycle, and high costs. Developing a new type of transcranial magnetic coil with magnetic stimulation focusing function and deep magnetic stimulation has important theoretical and clinical significance.

[0043] ​In an embodiment of the present invention, a magnetic stimulation device is disclosed, which includes a positioning and fixing connection device and an electromagnetic wave emitting device. The positioning and fixing connection device includes a spherical fixing frame composed of two identical hemispherical frames. The electromagnetic wave emitting device includes first, second, and third electromagnetic generating coil groups, and each electromagnetic generating coil group includes two coils symmetrically arranged about the center. The first, second, and third electromagnetic generating coil groups respectively form a pair of dual-focus magnetic stimulation coil pairs, which emit electromagnetic waves towards the center point of the spherical fixing frame. Since the magnetic stimulation device includes three pairs of dual-focus magnetic stimulation coil pairs, the magnetic stimulation signal is focused, so that the stimulation depth of transcranial magnetic stimulation can be controlled, the stimulation focus can be controlled, the stimulation range can be more controllable, and on the premise of greatly improving the treatment effect of transcranial magnetic stimulation, the complications caused by magnetic stimulation can be reduced.

[0044] Embodiment 1

[0045] Please refer to Figure 1, is a schematic structural diagram of a magnetic stimulation device in an embodiment. The magnetic stimulation device includes a positioning and fixing connection device and an electromagnetic wave emitting device. The positioning and fixing connection device includes a spherical fixing frame 1, and the spherical fixing frame 1 is composed of two identical hemispherical frames. The spherical fixing frame 1 is used to fixedly connect to the skull and set the target area to be magnetically stimulated at the center point of the spherical fixing frame 1. The electromagnetic wave emitting device includes a first electromagnetic generating coil group, a second electromagnetic generating coil group, and a third electromagnetic generating coil group. The first electromagnetic generating coil group includes two first coils 11 with the same structure. The two first coils 11 are symmetrically arranged on the spherical fixing frame 1 of the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame 1. The second electromagnetic generating coil group includes two second coils 12 with the same structure. The two second coils 12 are symmetrically arranged on the spherical fixing frame 1 of the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame 1. The third electromagnetic generating coil group includes two third coils 13 with the same structure. The two third coils 13 are symmetrically arranged on the spherical fixing frame 1 of the positioning and fixing connection device, and the center of symmetry coincides with the center point of the spherical fixing frame 1. The first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are respectively used to form a pair of dual-focus magnetic stimulation coil pairs to emit electromagnetic waves to the center point of the spherical fixing frame 1 for magnetic stimulation of the target area. In one embodiment, the number of turns, shape, material, and / or size of the first coil 11, the second coil 12, and the third coil 13 are the same. In one embodiment, the materials of the first coil 11, the second coil 12, and the third coil 13 include copper, iron, silver, and / or gold. In one embodiment, the shapes of the first coil 11, the second coil 12, and the third coil 13 include oval, "8"-shaped, or "H"-shaped. In one embodiment, the number of turns of the first coil 11, the second coil 12, and the third coil 13 is 20 to 60 turns. In one embodiment, the effective diameter of the first coil 11, the second coil 12, and the third coil 13 is 200 mm. In one embodiment, the size of the winding wire of the first coil 11, the second coil 12, and the third coil 13 is 3 mm 2 .

[0046] In one embodiment, the central axes of the first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are coplanar. In one embodiment, the included angles between the central axes of the first electromagnetic generating coil group and the second electromagnetic generating coil group and the central axis of the third electromagnetic generating coil group are the same. In one embodiment, the included angles between the central axes of the first electromagnetic generating coil group and the second electromagnetic generating coil group and the central axis of the third electromagnetic generating coil group are both 30 degrees. In one embodiment, one first coil 11 of the first electromagnetic generating coil group is tangent to one second coil 12 of the second electromagnetic generating coil group, and the tangent point is located at the center point of one third coil 13 of the third electromagnetic generating coil group.

[0047] In one embodiment, the diameter of the outer spherical surface of the spherical fixing bracket 1 is 720 mm, and the diameter of the inner spherical surface of the spherical fixing bracket 1 is 700 mm. In one embodiment, the material of the spherical fixing bracket 1 is polyvinyl chloride synthetic resin material.

[0048] In one embodiment, the magnetic stimulation device further includes a stimulation driving control module, which is electrically connected to the first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group respectively. The stimulation driving control module is used to perform timing control of the driving current on the first coil 11 of the first electromagnetic generating coil group, the second coil 12 of the second electromagnetic generating coil group, and the third coil 13 of the third electromagnetic generating coil group according to the preset coil stimulation intensity and stimulation timing. In one embodiment, the currents of the stimulation driving control module driving the first coil 11, the second coil 12, and the third coil 13 are 1 A to 10 kA. In one embodiment, the frequencies of the stimulation driving control module driving the first coil 11, the second coil 12, and the third coil 13 are 1 kHz to 10 kHz.

[0049] In the embodiment of the present application, the disclosed magnetic stimulation device includes a positioning and fixing connection device and an electromagnetic wave emitting device. The positioning and fixing connection device includes a spherical fixing bracket composed of two identical hemispherical frames. The electromagnetic wave emitting device includes a first, a second, and a third electromagnetic generating coil group, and each electromagnetic generating coil group includes two coils arranged centrosymmetrically. The first, second, and third electromagnetic generating coil groups respectively form a pair of dual-focus magnetic stimulation coil pairs, and emit electromagnetic waves towards the center point of the spherical fixing bracket. Since the magnetic stimulation device includes three pairs of dual-focus magnetic stimulation coil pairs, the magnetic stimulation signal is focused, so that the stimulation depth of transcranial magnetic stimulation can be controlled, the stimulation focus is controllable, the stimulation range is more controllable, and on the premise of greatly improving the treatment effect of transcranial magnetic stimulation, the complications caused by magnetic stimulation are reduced.

[0050] Please refer to Figure 2, which is a schematic diagram of the magnetic stimulation timing control of a magnetic stimulation device in an embodiment. The stimulation drive control module includes timing control and drive circuit 1, timing control and drive circuit 2, and timing control and drive circuit 3. The two first coils are fully synchronous magnetic stimulation coils, and the timing and magnitude of the current are obtained by shunting from timing control and drive circuit 1, which are timing 1 and drive current I1 respectively. The two second coils are fully synchronous magnetic stimulation coils, and the timing and magnitude of the current are obtained by shunting from timing control and drive circuit 2, which are timing 2 and drive current I2 respectively. The two third coils are fully synchronous magnetic stimulation coils, and the timing and magnitude of the current are obtained by shunting from timing control and drive circuit 3, which are timing 3 and drive current I3 respectively. In one embodiment, timing 1, timing 2, and timing 3 can be the same or different. In one embodiment, drive current I1, drive current I2, and drive current I3 can be the same or different. The stimulation drive control module can intelligently stimulate the first coil, the second coil, and the third coil to achieve intelligent control of the magnetic field strength and direction at a specific point.

[0051] Please refer to Figure 3 , which is a schematic diagram of the connection of a spherical fixing bracket in an embodiment. After the spherical fixing bracket is fixedly connected to the skull, the first coil is positioned in the front and rear of the head. In one embodiment, one hemispherical frame of the spherical fixing bracket is arranged in front of the forehead (in front of the prefrontal lobe), and the other hemispherical frame is arranged at the back of the head. The two hemispherical frames are at the same horizontal height position or form an angle not greater than 15 degrees with the horizontal plane.

[0052] Please refer to Figure 4 , which is a schematic diagram of the connection of a spherical fixing bracket in an embodiment. After the spherical fixing bracket is fixedly connected to the skull, the first coil is positioned on the left and right sides of the head. In one embodiment, one hemispherical frame of the spherical fixing bracket is arranged on the left side of the skull, and the other hemispherical frame is arranged on the right side of the skull. The two hemispherical frames are at the same horizontal height position or form an angle not greater than 15 degrees with the horizontal plane.

[0053] In one embodiment, the value of the drive current is 1A to 10kA. In one embodiment, the frequency of the timing is 1kHz to 10kHz. The two first coils generate an electric field in the head sufficient to depolarize cortical neurons.

[0054] In one embodiment, the target area for pre-magnetic stimulation by the magnetic stimulation device includes one of the following: frontal lobe, thalamus, cingulate gyrus, putamen, caudate nucleus, hippocampus, ventral striatum, and amygdala.

[0055] The present invention adopts a precise and flexible structural design, realizing controllability of the stimulation depth of transcranial magnetic coil stimulation and controllability of magnetic stimulation focusing of coil magnetic stimulation. Based on the intelligent control of coil current, intelligent control of the intensity and direction of the magnetic field focusing point of transcranial magnetic coil stimulation can be achieved, providing a powerful tool for precise stimulation treatment in transcranial magnetic stimulation therapy and for the research of brain science and neuroscience.

[0056] Those skilled in the art can understand that all or part of the functions of the various methods in the above embodiments can be implemented in a hardware manner or in a computer program manner. When all or part of the functions in the above embodiments are implemented in a computer program manner, the program can be stored in a computer-readable storage medium, and the storage medium can include: read-only memory, random access memory, magnetic disk, optical disk, hard disk, etc. The above functions are realized by a computer executing the program. For example, the program is stored in the memory of the device, and when the processor executes the program in the memory, the above all or part of the functions can be realized. In addition, when all or part of the functions in the above embodiments are implemented in a computer program manner, the program can also be stored in a storage medium such as a server, another computer, magnetic disk, optical disk, flash drive or mobile hard disk, and is saved to the memory of the local device by downloading or copying, or the system of the local device is updated in version. When the processor executes the program in the memory, all or part of the functions in the above embodiments can be realized.

[0057] The above uses specific examples to elaborate on the present invention, which is only used to help understand the present invention and is not intended to limit the present invention. For those skilled in the technical field to which the present invention pertains, based on the idea of the present invention, several simple deductions, deformations or substitutions can also be made.

Claims

1. A magnetic stimulation device, characterized in that, it includes a positioning and fixing connection device and an electromagnetic wave emitting device; The positioning and fixing connection device includes a spherical fixing frame, and the spherical fixing frame is composed of two identical hemispherical frames; the spherical fixing frame is used to fixedly connect the skull, and the target area to be magnetically stimulated is set at the center point of the spherical fixing frame; The electromagnetic wave emitting device includes a first electromagnetic generating coil group, a second electromagnetic generating coil group, and a third electromagnetic generating coil group; the first electromagnetic generating coil group includes two first coils with the same structure, and the two first coils are symmetrically arranged on the positioning and fixing connection device in a central symmetry manner, and the central symmetry point coincides with the center point of the spherical fixing frame; the second electromagnetic generating coil group includes two second coils with the same structure, and the two second coils are symmetrically arranged on the positioning and fixing connection device in a central symmetry manner, and the central symmetry point coincides with the center point of the spherical fixing frame; the third electromagnetic generating coil group includes two third coils with the same structure, and the two third coils are symmetrically arranged on the positioning and fixing connection device in a central symmetry manner, and the central symmetry point coincides with the center point of the spherical fixing frame; The first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are respectively used to form a pair of dual-focus magnetic stimulation coil pairs, and emit electromagnetic waves to the center point of the spherical fixing frame to magnetically stimulate the target area; The central axes of the first electromagnetic generating coil group, the second electromagnetic generating coil group, and the third electromagnetic generating coil group are coplanar; The included angle between the central axes of the first electromagnetic generating coil group and the second electromagnetic generating coil group and the central axis of the third electromagnetic generating coil group is the same; One of the first coils of the first electromagnetic generating coil group is tangent to one of the second coils of the second electromagnetic generating coil group, and the tangent point is located at the center point of one of the third coils of the third electromagnetic generating coil group; The effective diameters of the first coil, the second coil, and the third coil are 200 mm.

2. The magnetic stimulation device according to claim 1, characterized in that, The winding turns, shapes, materials, and / or dimensions of the first coil, the second coil, and the third coil are the same; and / or, the materials of the first coil, the second coil, and the third coil include copper, iron, silver, and / or gold; and / or, the shapes of the first coil, the second coil, and the third coil include oval, "8"-shaped, or "H"-shaped.

3. The magnetic stimulation device according to claim 2, characterized in that, The winding turns of the first coil, the second coil, and the third coil are 20 to 60 turns; And / or, the size of the winding wire of the first coil, the second coil and the third coil is 3 mm 2 .

4. The magnetic stimulation device according to claim 1, characterized in that, The diameter of the outer spherical surface of the spherical fixing frame is 720 mm, and the diameter of the inner spherical surface of the spherical fixing frame is 700 mm; and / or, the material of the spherical fixing frame is a polyvinyl chloride synthetic resin material.

5. The magnetic stimulation device according to claim 1, characterized in that, It further includes a stimulus-driven control module, which is electrically connected to the first electromagnetic coil group, the second electromagnetic coil group, and the third electromagnetic coil group respectively; the stimulus-driven control module is used to perform timing control of the drive current on the first coil of the first electromagnetic coil group, the second coil of the second electromagnetic coil group, and the third coil of the third electromagnetic coil group simultaneously or separately according to a preset coil stimulus intensity and stimulus timing.

6. The magnetic stimulation device according to claim 5, wherein, the current of the first coil, the second coil, and the third coil driven by the stimulus-driven control module is 1A to 10kA.

7. The magnetic stimulation device according to claim 5, wherein, the frequency of the first coil, the second coil, and the third coil driven by the stimulus-driven control module is 1KHz to 10KHz.

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