CN115970168A

CN115970168A - Magnetic stimulation unit, magnetic stimulation assembly and magnetic stimulation device

Info

Publication number: CN115970168A
Application number: CN202211639536.9A
Authority: CN
Inventors: 覃剑; 王跃; 韩鹏浩; 黄莹
Original assignee: Beijing Yone Galaxy Technology Co ltd; Beijing Yinhe Fangyuan Technology Co ltd
Current assignee: Beijing Yinhe Fangyuan Technology Co ltd
Priority date: 2022-12-20
Filing date: 2022-12-20
Publication date: 2023-04-18

Abstract

The invention discloses a magnetic stimulation unit, a magnetic stimulation assembly and a magnetic stimulation device, and belongs to the technical field of TMS magnetic stimulation. The magnetic stimulation unit includes: the magnetic stimulation coil is made of a hollow conductor wound into a preset pattern, the wall of the hollow conductor is provided with a circuit for electrifying, and the hollow cavity of the hollow conductor is filled with insulating refrigerating fluid; and an insulating case formed by vacuum-injecting a high voltage resistant material between adjacent portions of the hollow conductor, the insulating case having a shape conforming to that of the magnetic stimulation coil. The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device optimally design the peripheral coating structure of the magnetic stimulation coil, so that the weight of the magnetic stimulation coil is the lightest under the condition that the weight meets the safety requirement.

Description

Magnetic stimulation unit, magnetic stimulation assembly and magnetic stimulation device

Technical Field

The invention relates to the technical field of TMS magnetic stimulation, in particular to a magnetic stimulation unit, a magnetic stimulation assembly and a magnetic stimulation device.

Background

At present, in the process of regulating and controlling a testee by Transcranial Magnetic Stimulation (TMS) magnetic stimulation equipment in the market, the magnetic stimulation coil is found to be incapable of meeting the requirements of long-time continuous regulation and control and high-strength magnetic stimulation. In order to realize high-intensity magnetic stimulation, a TMS magnetic stimulation device is required to provide large output current. Accordingly, the current on the TMS magnetic stimulation coil is also large, which results in the magnetic stimulation coil and the connected cables being prone to heat, and the demand for power is greater.

Meanwhile, after a long-time high-intensity magnetic stimulation, the magnetic excitation coil is easy to stop outputting due to overheating, so that the treatment process cannot be completely carried out. In the case of preventing the magnetic excitation coil from overheating, for example, by reducing the time length or reducing the output magnetic field strength, the control effect is greatly reduced, and the control expectation cannot be achieved. In addition, the existing TMS magnetic stimulation equipment generally has the defect of inconvenient use due to large volume.

Therefore, the magnetic stimulation coil needs to be redesigned in structure to realize a larger current on the magnetic stimulation coil, and meet a larger power requirement without frequent overheating.

Disclosure of Invention

In order to solve at least one aspect of the above problems and disadvantages in the prior art, an embodiment of the present invention provides a magnetic stimulation unit, a magnetic stimulation assembly, and a magnetic stimulation device, where the technical solution is as follows:

according to an aspect of the present invention, there is provided a magnetic stimulation unit, wherein,

the magnetic stimulation unit includes:

the magnetic stimulation coil is made of a hollow conductor wound into a preset pattern, the pipe wall of the hollow conductor is provided with a power-on circuit, and the hollow cavity of the hollow conductor is filled with insulating refrigerating fluid;

and the insulating shell is formed by vacuum pouring high-voltage-resistant materials between the adjacent parts of the hollow conductors, and the shape of the insulating shell is consistent with that of the magnetic stimulation coil.

According to another aspect of the present invention, there is provided a magnetic stimulation assembly, wherein,

the magnetic stimulation assembly comprises:

a magnetic stimulation unit, wherein the magnetic stimulation unit is the magnetic stimulation unit of any one of the above items;

a driving unit configured to drive the magnetic stimulation unit to generate an alternating magnetic field;

a charging unit configured to charge the magnetic stimulation unit.

According to yet another aspect of the present invention, there is provided a magnetic stimulation apparatus, wherein,

the magnetic stimulation device comprises:

a magnetic stimulation unit, wherein the magnetic stimulation unit is the magnetic stimulation unit described in any one of the above;

an acquisition module configured to acquire electromyographic signals of a human body in real time; and

and the wireless time comparison module is used for acquiring the first time of the magnetic field output by the magnetic stimulation unit, adding the first time into the electromyographic signals to be transmitted, and then transmitting the electromyographic signals with the first time to a terminal for processing.

the magnetic stimulation device comprises:

a magnetic stimulation assembly as described in any of the above;

the wireless time setting module is used for collecting the first time of the magnetic field output by the magnetic stimulation unit in the magnetic stimulation assembly, adding the first time into the electromyographic signals to be transmitted, and then transmitting the electromyographic signals with the first time to a terminal for processing.

The magnetic stimulation unit, the magnetic stimulation component and the magnetic stimulation device provided by the embodiment of the invention have at least one of the following advantages:

(1) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device optimally design the peripheral coating structure of the magnetic stimulation coil, so that the weight of the magnetic stimulation coil is the lightest under the condition that the weight meets the safety requirement, high-pressure-resistant materials such as FR4 and resin are mainly used in the process, and the measures such as a vacuum infusion technology are adopted, so that the pressure-resistant requirements of all parts such as copper pipes of adjacent magnetic stimulation coils and the surfaces of the magnetic stimulation coils are met, and the body strength of the magnetic stimulation coil is improved;

(2) According to the magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device, the optimized winding pattern of the magnetic stimulation coil, such as a circular coil or an 8-shaped coil, is found through three stages of theoretical calculation, computer simulation, physical verification and the like, so that better comprehensive performance is realized;

(3) The magnetic stimulation unit, the magnetic stimulation component and the magnetic stimulation device provided by the invention adopt the magnetic stimulation coil with the four-layer structural design, so that the problems of large driving current, serious cable heating, heavy coil weight and the like are solved;

(4) According to the magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device, a half-bridge quasi-resonant topological circuit is adopted in the TMS charging unit, so that the high-voltage energy storage charging and discharging capacitor is always charged according to the TMS pulse working characteristics, a charging system meeting the TMS requirement is designed according to the dosage of the advantageous therapy, the rapid charging is realized, and the pulse time sequence of the advantageous therapy is reached. In the current TMS charging unit, a half-bridge quasi-resonant topology circuit is used, so that higher efficiency and stability can be obtained;

(5) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention design a cooling structure of the magnetic stimulation coil, for example, a refrigerant and electric separation technology is adopted, so that a refrigerant interface and an electric interface are separated, and the influence on electric safety when the refrigerant leaks is effectively eliminated;

(6) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device adopt a three-way connection mode for the refrigerant inlet of the magnetic stimulation coil, particularly for the 8-shaped magnetic stimulation coil, so that the copper pipes on two sides of the 8 shape can simultaneously input the refrigerant, the heat dissipation is accelerated, and the temperatures of the copper pipes on two sides are kept symmetrical and balanced;

(7) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention have the characteristics of high voltage and large heat generation amount in consideration of the magnetic stimulation coil, adopt a semiconductor refrigeration mode, and can also adopt a refrigeration mode of semiconductor refrigeration and air cooling under the condition of requirement so as to realize better heat dissipation effect and meet the requirement of low noise;

(8) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention adopt high-insulation silicon oil and the like as cooling refrigerants, so that the safety of a discharging process is ensured;

(9) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention adopt the pumping device, the storage tank, the cold row, the refrigerant pipeline, the quick plug and the like to form a refrigerant circulation loop so as to realize heat conduction to the magnetic stimulation coil and the corresponding refrigeration part;

(10) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention can carry out real-time temperature monitoring and real-time intelligent control on the cooling of the magnetic stimulation coil by configuring the temperature sensor and the control board;

(11) The magnetic stimulation unit, the magnetic stimulation component and the magnetic stimulation device provided by the invention use the key integrating the indicator light and the switch, so that the space is saved;

(12) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention solve the problem of synchronism between the acquisition of the Motion Evoked Potential (MEP) waveform and TMS stimulation through the designed wireless time synchronization module, and the wireless accurate time synchronization unit is also adopted in the TMS, so that the error can be controlled to microsecond level, and the error of the acquisition time of the MEP waveform can be almost ignored.

Drawings

These and/or other aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the preferred embodiments, taken in conjunction with the accompanying drawings of which:

fig. 1 is a perspective schematic structural view of a portion of a magnetic stimulation unit using a circular shaped magnetic stimulation coil according to an embodiment of the present invention;

fig. 2 is a schematic diagram of a figure-8 magnetic stimulation coil obtained through simulation calculation according to another embodiment of the present invention;

fig. 3 is a schematic perspective view of a portion of a magnetic stimulation unit using the figure-8 magnetic stimulation coil shown in fig. 2;

fig. 4 is a schematic view of a cooling unit of the magnetic stimulation assembly according to an embodiment of the present invention;

FIG. 5 is an exploded schematic view of a cooling unit for magnetic stimulation according to an embodiment of the present invention;

FIG. 6 shows a schematic structural view of the cooling module shown in FIG. 5;

fig. 7 shows a schematic diagram of a drive unit in a magnetic stimulation assembly according to an embodiment of the invention;

fig. 8 shows a schematic structural diagram of a drive unit according to an embodiment of the present invention;

FIG. 9 shows a schematic diagram of a charging unit in a magnetic stimulation assembly, according to an embodiment of the invention;

fig. 10 shows a schematic structural diagram of a charging unit according to an embodiment of the present invention;

fig. 11 shows an exploded schematic view of a magnetic stimulation device according to an embodiment of the invention.

Detailed Description

The technical scheme of the invention is further specifically described by the following embodiments and the accompanying drawings. In the specification, the same or similar reference numerals denote the same or similar components. The following description of the embodiments of the present invention with reference to the accompanying drawings is intended to explain the general inventive concept of the present invention and should not be construed as limiting the invention.

In order to solve the technical problems presented in the background section, the present invention contemplates a magnetic stimulation coil or a magnetic stimulation unit that is re-optimally designed to achieve a magnetic stimulation unit that can meet the requirements of the dominant therapy.

The first step is to design the whole system using the magnetic stimulation unit in a system theory, mainly considering all the restriction factors of the magnetic stimulation coil, refrigeration (power and mode), power and efficiency of the power supply, cable heating and the like, and then to design the system. Most importantly, the most suitable core discharge resonance (LC) parameters are designed. The LC parameters determine the discharge pulse width, while the system losses due to LC and its parasitic parameters, etc., also determine the charging speed, and thus the overall charging power, system volume, efficiency, etc. Meanwhile, the value of the parameter L also determines the range of designable structural size and shape of the magnetic stimulation coil.

From the LC resonance frequency equation: f = 1/(2 pi sqrt (L) C)),

energy loss formula: e = C (Vi-Vs)/2, where Vi is a capacitor discharge initial voltage and Vs is a capacitor discharge residual voltage.

Searching different LC combinations, combining parasitic parameters of coil materials of different models, performing circuit and coil magnetic field simulation to obtain parameter combinations which are most suitable for the therapy with advantages, including L, C, acceptable range of coil parasitic resistance and the like, and finally determining the L value.

Secondly, the core component, namely the body of the magnetic stimulation coil is designed. After the inductance L of the magnetic stimulation coil is determined in the first step, various performance indexes of the magnetic stimulation coil, such as focusing performance, maximum output magnetic field strength, driving current at the maximum output magnetic field strength, weight, inductance and the like, are considered. Firstly, the magnetic stimulation coil is optimally designed. The optimization means mainly comprises three stages of theoretical calculation, computer simulation and physical verification.

On the aspect of theoretical calculation:

the heating power P = I × R is the product of the driving current effective value I squared and the coil parasitic resistance R, which includes the direct current resistance and the alternating current resistance. And selecting the type of the coil (copper pipe) with the sectional area as large as possible under the condition of meeting the magnetic field intensity.

According to the ampere-loop theorem:

|. B dl = μ 0 ×, Σ i, the magnetic field distribution and the intensity of the energized conductor are calculated.

According to the rule and the requirement of the coil, the approximate shape is obtained.

In the aspect of computer simulation:

according to theoretical calculation, the approximate shape of the coil is estimated, then the coil structure design under the parameters of different intervals and the like in the specific shape is carried out, and then simulation is carried out.

The invention simulates dozens of coils with different structures and forms, integrates data to obtain several concerned coils with the best comprehensive performance, and finally carries out physical processing verification on the coils with the best comprehensive performance, and takes the coils which are actually measured and verified to be most suitable for the therapy with the advantages as final output.

Referring to fig. 1, a perspective schematic view of a magnetic stimulation unit according to an embodiment of the present invention is shown. It is shown that the magnetic stimulation unit takes the form of a circular coil 10. In fig. 1, only a part of the magnetic stimulation unit is shown, not a complete view, with the right side cut off in dashed lines indicating that the insulation shell, the refrigerant pipe and the power supply line may also have an extension and a subsequent corresponding joint. Fig. 3 is similar to fig. 1, and a complete view is not shown, and is not described again.

As mentioned above, theoretical calculation, computer simulation and physical verification suggest that setting the magnetic stimulation coil to a circular shape can achieve better overall performance indicators. In particular, the magnetic stimulation coil is made of any suitable material, such as a hollow conductor, e.g. a steel tube, by winding in a predetermined pattern, e.g. a circular coil. The cavity in the hollow conductor is cooled by a refrigerant such as highly insulating silicone oil, and the inner wall of the hollow conductor is energized to generate a magnetic field by the action of an electric current. The magnetic field acts on the corresponding region of the brain of the subject and induces induction current, thereby diagnosing or treating the subject. It should be noted that the provided magnetic stimulation device can be applied not only to diagnosis and treatment of the brain, but also to peripheral neuromuscular and the like.

In one embodiment, the magnetic stimulation coil is a circular coil 10, and the circular coil is a four-layer structure formed by winding a copper pipe from outside to inside in sequence in a circular shape for multiple turns, and then from inside to outside in sequence in a circular shape for multiple turns, and the four-layer structure is formed by repeatedly winding the copper pipe from outside to inside in sequence. Of course, one skilled in the art will appreciate that the circular coil may be a single layer multi-turn coil structure, a double layer multi-turn coil structure, or a multi-layer multi-turn coil structure. The magnetic stimulation coil has two ends because it is wound from a single piece of copper tubing.

In one example, the circular coil is preferably designed to be a four-layer structure, and the four-layer structure sequentially includes, from bottom to top, a first adjustment inductance layer (not shown), a second adjustment inductance layer (not shown), a third magnetic field application layer (not shown), and a fourth magnetic field application layer (not shown). Because the third magnetic field action layer and the fourth magnetic field action layer can directly act on the regulation and control part, the required magnetic field intensity is larger, the action range is wider, and the winding turn number range of the third magnetic field action layer and the fourth magnetic field action layer is set to be 3-4 turns. Meanwhile, the first regulating inductance layer and the second regulating inductance layer are mainly used for regulating inductance, so that the winding turn range of the first regulating inductance layer and the second regulating inductance layer is set to be 2-3 turns.

More preferably, the diameter of the circular coil is set to be in the range of 3.8 to 7.2cm. And the copper pipe of the circular coil is a hollow copper pipe with the outer diameter of 4-6mm and the inner diameter of 1-3 mm.

Through the setting of four-layer structure, circular coil diameter scope, can make the weight greatly reduced of circular coil, can also reduce the drive current of coil under the condition of guaranteeing long-time regulation and control simultaneously, solved the serious problem that the cable generates heat simultaneously.

Referring to fig. 2, an example of a magnetic stimulation coil according to another embodiment of the invention is shown. The magnetic stimulation coil is shaped as a figure 8 10'. The magnetic stimulation coil is a figure-8 coil and is divided into a left part 12 and a right part 16 of a figure-8 shape, the left part 12 having two ends 13, 14 and the right part 16 also having two ends 17, 18. The left part 12 and the right part 16 of the 8-shaped magnetic stimulation coil 10' are respectively circular coils, the four-layer structure is formed by winding a copper pipe 11 from outside to inside in sequence according to a circle for multiple turns, and from inside to outside in sequence according to a circle for multiple turns at the center, and the four-layer structure is formed by repeatedly winding, and the circular coils of the left part 12 and the right part 16 are wound in a mirror symmetry mode. Similarly, the magnetic stimulation coil 10' may have a single-layer coil structure, a double-layer coil structure, or a multi-layer coil structure.

In one example, the left portion 12 and the right portion 16 of the figure-8 coil are each preferably designed as a four-layer structure, and the four-layer structure sequentially comprises a first regulating inductance layer (not shown), a second regulating inductance layer (not shown), a third magnetic field acting layer (not shown) and a fourth magnetic field acting layer (not shown) from bottom to top. Because the third magnetic field action layer and the fourth magnetic field action layer can directly act on and regulate and control the position, the required magnetic field intensity is larger, the action range is wider, and the winding turn number range of the third magnetic field action layer and the fourth magnetic field action layer is set to be 3-4 turns. Meanwhile, the first regulating inductance layer and the second regulating inductance layer are mainly used for regulating inductance, so that the winding turn range of the first regulating inductance layer and the second regulating inductance layer is set to be 2-3 turns.

More preferably, the diameter of each of the left part 12 and the right part 16 of the figure-8 coil is set to be 3.8-7.2 cm. And the copper pipe of the 8-shaped coil is a hollow copper pipe with the outer diameter of 4-6mm and the inner diameter of 1-3 mm.

Through the setting of four-layer structure, circular coil diameter scope, can make 8 font coil's weight greatly reduced, can also guarantee under the condition of long-time regulation and control simultaneously, reduce the drive current of coil, solved the serious problem that the cable generates heat simultaneously.

It should be noted that only two simulated and verified versions of the magnetic stimulation coils are shown here, and those skilled in the art may select any other desired pattern.

As described above, in the present embodiment, after the magnetic stimulation coils are arranged in the special-shaped pattern such as the figure-8 coil 10' or the circular coil 10, they show relatively good overall performance indexes after simulation verification. And then, the insulating shell 20 is arranged at the periphery of the magnetic stimulation coil, so that the problems of large driving current, serious cable heating, heavy coil weight and the like of the magnetic stimulation coil are solved.

An embodiment of the present invention also provides an optimized design scheme for the outsourcing structure. I.e. the outer periphery of the magnetic stimulation coil comprises a material optimized design. The design goal is to make the insulation as light or as light as possible while meeting insulation safety requirements. In specific implementation, a copper pipe is selected as a hollow conductor to be wound to form the magnetic stimulation coil. Whereby an insulating shell 20 is formed by vacuum infusion of a high voltage resistant material between adjacent portions of the hollow conductor. The insulating case 20 is mainly made of a high-voltage-resistant material such as FR4, resin, or the like; by means of vacuum filling technology and the like, pressure resistance of all parts between adjacent copper pipes, between the copper pipes and the upper and lower surfaces of the magnetic stimulation coil and the like can meet requirements, and the strength of the coil body also meets requirements.

In terms of weight reduction, the following measures are mainly adopted: on the premise that the insulation meets the requirement of voltage resistance, the pouring material is as thin as possible; the potting material conforms to the shape of the coil itself as much as possible.

In one embodiment, the insulating housing 20 is shaped to conform to the shape of the magnetic stimulation coil 10, 10'. Referring to fig. 1, the insulating case 20 is also provided in a substantially circular shape. The height of the insulating shell 20 above the upper or lower surface of the magnetic stimulation coil 10, 10' is 1-5mm. The thickness of the insulating shell 20 is set to 1-5mm, so that the insulating shell is as thin as possible on the premise of meeting the requirement of voltage resistance, and the weight of the magnetic stimulation coils 10 and 10' is reduced. In addition, the shape of the insulating case 20 is made to conform to the shape of the magnetic stimulation coils 10 and 10', which can also help to reduce the weight and achieve a good magnetic stimulation effect.

Referring to fig. 2 and 3, in the case of the figure-8 magnetic stimulation coil 10', the shape of the insulation case 20 is also correspondingly arranged in a figure-8 shape to fit the shape of the magnetic stimulation coil 10' itself as much as possible, and the height of the insulation case 20 above the upper or lower surface of the magnetic stimulation coil 10' is 1-5mm.

In one embodiment, referring to fig. 1 or fig. 3, the magnetic stimulation unit further comprises an indicator light disposed at the end of the magnetic stimulation coil 10, 10' for indicating that the magnetic stimulation coil 10, 10' is turned on and a button 90 for switching the magnetic stimulation coil 10, 10'. The indicating lamp and the switch are arranged to be the same key, so that the space can be effectively saved.

In one embodiment, referring to fig. 1 or 3, the magnetic stimulation unit comprises at least one temperature sensor 30 arranged on the magnetic stimulation coil 10, 10' and within the insulating housing 20. By providing the temperature sensor 30, the heating of the magnetic stimulation coils 10, 10' can be effectively monitored for effective cooling.

As shown in fig. 1, the refrigerant inlet pipe and the refrigerant outlet pipe are communicated with the two ends after passing through the extension joint 80, the refrigerant connector 50 and the parallel connection block 40, respectively, to form a refrigerant circuit. Two power supply wires 6 are electrically connected to the two ends, respectively, after passing through the elongated connectors 80, the electrical interface (not shown) and the parallel connection block 40 to form an electrical circuit. The extended joint 80 leads the two power supply lines 6, the refrigerant inlet pipe, and the refrigerant outlet pipe out of the insulating case 20.

Similarly, as shown in fig. 3, the refrigerant inlet pipe and the refrigerant outlet pipe pass through the extension joint 80 and are connected with the three-way joint 70 to become two refrigerant inlet branch pipes and two refrigerant outlet branch pipes, the two refrigerant inlet branch pipes respectively communicate with one ends of the magnetic stimulation coils 10 'in the left part 12 and the right part 16 after passing through the refrigerant port 50 and the parallel connection block 40, and correspondingly, the two refrigerant outlet branch pipes respectively communicate with the other ends of the magnetic stimulation coils 10' in the left part 12 and the right part 16 after passing through the refrigerant port 50 and the parallel connection block 40 to form a refrigerant circuit. Two power supply wires are electrically connected with one end of the magnetic stimulation coil 10 'in the left part 12 and the right part 16 respectively through the lengthened joint 80, the insulated pipe 7, the electric interface 8 and one power supply wire 6 behind the electric connecting block 4, and correspondingly, the other power supply wire 6 is electrically connected with the other end of the magnetic stimulation coil 10' in the left part 11 and the right part 16 respectively to form an electric loop. The extended joint 80 leads the two power supply lines 6, the refrigerant inlet pipe, and the refrigerant outlet pipe out of the insulating case 20.

As shown, the parallel connection block 40 and the electrical connection block 4 are provided at substantially corresponding positions, for example, two members provided to oppose each other.

In fig. 3, not only is the refrigerant and the electric separation realized, but also the refrigerant can be simultaneously input into the copper pipes on both sides by connecting the refrigerant pipes with the three-way joint 70, so that the heat dissipation is accelerated, and the temperatures of the magnetic stimulation coils on both sides can be kept symmetrical and balanced.

For convenience of positioning, in fig. 3, a positioning projection 60 is provided on the periphery of the insulating case 20 corresponding to the three-way joint 70. The positioning protrusion 60 can be set to be in different shapes such as a circle, an ellipse, a square and a rectangle or any figure conforming to human engineering, in the embodiment, the positioning protrusion 60 is set to be a circular protrusion, the setting mode is simple and effective, and better positioning can be realized. Of course, the present embodiment is not limited to a circular protrusion. Whether the positioning circular protrusion is arranged or not can be selected by the person skilled in the art according to the needs.

For further improvement or better insulation design, the refrigerant inlet pipe, the refrigerant outlet pipe and the power line 6 are wrapped in an insulated pipe 7 extending from the parallel connection block 40 or the electrical connection block 4 to the elongated joint 8. Namely, the corresponding components are arranged in the insulating pipe 7 and then the connection assembly is performed.

The scheme adopts the optimal coil manufacturing material, and takes the output magnetic field intensity and the coil heating into consideration, so that the optimized physical characteristics of the coil become one of the guarantees of guaranteeing the output duration time of the therapeutic benefit with large dose;

the scheme adopts a method for optimizing the LC parameter design of the system, can improve the output intensity, can also obviously improve the duration of large-dose continuous output, and meets the equipment support of the advantage therapy.

The magnetic stimulation coil adopts an oil-electricity separation technology, so that a refrigerant interface of the cooling liquid is separated from an electrical interface, and the influence on electrical safety when the cooling liquid leaks is effectively eliminated.

In this embodiment, a cooling unit provided with the magnetic stimulation coil achieves a good heat dissipation effect. For example, the refrigerant and electric separation technology is adopted, so that the refrigerant interface and the electric interface are separated, and the adverse effect on electric safety when the refrigerant leaks is effectively eliminated.

Referring to fig. 4, a schematic diagram of a cooling unit or cooling mechanism in a magnetic stimulation assembly according to another embodiment of the invention is shown. Aiming at the problem that the heating of the magnetic stimulation coil 10 or 10' is serious, in order to improve the adaptability of the magnetic stimulation coil to various environmental temperatures, the invention provides a cooling unit which is cooled by adopting an active liquid cooling mode. The active liquid cooling mode can adopt a thermal refrigeration mode, a semiconductor refrigeration mode, a Peltier refrigeration mode and the like. In one embodiment, a semiconductor cooling mode is taken as an example for explanation.

The semiconductor refrigeration mode is adopted for cooling, so that the advantages of small size, low noise, long service life and the like of the whole equipment can be achieved. As shown in fig. 4, an overall schematic diagram of the cooling unit is shown. The cooling unit comprises a refrigeration module, a cooling pipeline, a pumping device, a storage tank for storing a refrigerant, a power supply and a corresponding controller.

A certain amount of refrigerant (e.g., high-insulation silicone oil) is stored in the storage tank in advance, but other refrigerants such as water, deionized water, and alcohol may be used. The pumping device pumps the refrigerant in the storage tank to the refrigeration module through the cooling pipeline, the refrigeration module cools the sucked refrigerant to a preset temperature, then the refrigerant is pumped to the magnetic stimulation coil 10 or 10', and finally the heat of the magnetic stimulation coil 10 or 10' is taken away by the refrigerant and stored in the storage tank. The above steps are repeated to solve the problem of serious coil heating in the beneficial therapy, so that the support coil continuously provides the output dose required by the beneficial therapy.

The controller controls the on of the pumping device and the power supply of the power supply, and can set the temperature of the refrigerant output by the refrigeration module according to requirements. That is, the controller can issue different refrigeration power demands to regulate and control the pumping device and the refrigeration module. Through so setting up, can guarantee that the refrigeration power of refrigeration module satisfies the demand of dominant therapy to make magnetic stimulation coil etc. be in work under the best efficiency state all the time, and can prolong the life of part.

In one embodiment, the refrigeration module can radiate heat in a double-sided cooling concentration mode, so that the size of components is reduced as much as possible, and the efficiency is improved.

In one embodiment, a machine learning technology can be built in the controller, and a refrigeration algorithm is automatically optimized and controlled according to different use habits, so that the whole equipment is in a working state with the lowest average power consumption, the highest efficiency and the longest service life.

Referring to fig. 5, a cooling unit 100 for a magnetic stimulation assembly is shown. The illustrated cooling unit 100 includes at least two quick-connect connectors 110, a storage tank 120, a cooling module 130, a pumping device 140, etc., which form a cooling refrigeration cycle for better cooling of the magnetic stimulation unit for magnetic stimulation.

In order to facilitate rapid plugging of the refrigerant pipe with the magnetic stimulation coil 10 or 10', at least two quick-plugging connectors 110 are used to connect the magnetic stimulation coil 10 or 10' with the cooling unit 100. The number of the quick-connect connectors 110 is not particularly limited, and those skilled in the art can select an appropriate number and an appropriate structure as needed. In one embodiment, the quick connector 110 may be directly connected to the copper tube of the magnetic stimulation coil 10 or 10'. It is of course also possible to connect the copper tubes again, as shown in fig. 5, by means of corresponding connections provided on the housing of the cooling unit 100.

The storage tank 120 stores a predetermined amount of refrigerant, such as highly insulating silicone oil, etc., in advance, but any other suitable refrigerant, such as distilled water, deionized water, transformer oil, alcohol, diesel oil, etc., may be used. The storage tank 120 is not limited in form, and draws out refrigerant through the refrigerant pipe 101, and is provided with a quick-connect coupling 110 at the end of the refrigerant pipe 101.

During operation, the pumping device 140, such as an oil pump, pumps the refrigerant from the storage tank 120 into the pumping device 140 and into the cooling module 130, the refrigerant enters the magnetic stimulation coil through the refrigerant pipe 101 after being cooled by the cooling module 130, and the refrigerant flows back into the storage tank 120 through the refrigerant pipe 101 after cooling the magnetic stimulation coil.

As shown in fig. 6, the cooling module 130 combines semiconductor refrigerant technology and air cooling. It will be appreciated that refrigeration may also be employed using either of them. The cooling module 130 is used to achieve heat exchange of the refrigerant.

The cooling module 130 includes a cold row 131, a cold plate 132, a heat sink 133, and a fan 134. The cooling plate 132 may be a thermoelectric cooling plate, a semiconductor cooling plate, or a peltier cooling plate. In one embodiment, the cooling plate 132 is a semiconductor cooling plate, and the cold side of the semiconductor cooling plate 132 is attached to the cold row 131, and the hot side is attached to the heat sink 133. In addition, a fan 134 is disposed on one side of the cooling module 130, and the fan 134 is used for cooling the heat sink by blowing the ambient air. The refrigerant first enters through one end of the cold row 131, and after heat exchange is completed, flows out from the other end of the cold row 131. In one embodiment, the specific form of the cooling rows 131, the semiconductor cooling fins 132 and the heat sink 133 is not limited, and the fan 134 may be a common fan or an axial fan with larger power.

In an embodiment, the thermal power consumption of the magnetic stimulation coil can be estimated according to the working conditions of the highest stimulation intensity, the maximum frequency and the longest time by combining the use working conditions of the magnetic stimulation coil and the information such as the temperature required to be kept by the magnetic stimulation coil 10 or 10'; and meanwhile, the heat transfer quantity between the coil and the medium is calculated according to the Newton's cooling law.

The type and number of the semiconductor chilling plates 132 are selected according to the thermal power consumption, the coil heat transfer capacity and the comprehensive performance coefficient of the semiconductor chilling plates 132.

In one embodiment, the cooling plate 131 and the heat sink 133 may be designed according to the power of the cold and hot surfaces of the semiconductor cooling plate 132, and a heat conducting interface material may be added, such as silicone grease (thermal grease), silicone gel (thermal gel), heat sink pad (thermal pad), and Phase change material (Phase change motor i a l); phase change metal sheet (Phase change metal l oy), thermal conductive paste (thermal conductive material).

For the selection of the fan 134, the air volume of the fan 34 is calculated according to the power consumption and the temperature rise of the semiconductor cooling plate 132, and the fan type selection is completed considering the space and the like.

In one embodiment, the fan 134 may be mounted on the heat sink 133 by a bracket.

The plurality of radiating fins 133 are stacked on each other to provide a better radiating effect.

In one embodiment, the cooling unit 100 includes an electromagnetic shielding box housing 150. The electromagnetic shielding box housing 150 is used to provide a space for electromagnetic shielding that conforms to the magnetic stimulation technique, for example, the inner walls thereof may be provided with any suitable shielding coating. The shape of the electromagnetic shielding box housing 150 is not limited, and may be rectangular or square.

The cooling module 130 is disposed at the right end inside the electromagnetic shielding box housing 150, and the refrigerant pipe 101 connected with the cooling module 130 is communicated with the corresponding interface 102 on the electromagnetic shielding box housing 150 through at least two quick-connect interfaces 110, the pumping device 140, the power supply 160 and the storage tank 120 are disposed inside the electromagnetic shielding box housing 150, and the refrigerant pipe 101 connected with the storage tank 120 is communicated with another corresponding interface 102 on the electromagnetic shielding box housing 150 through at least two quick-connect interfaces 110.

Specifically, one end of the refrigerant pipe 101 connected with the pumping device 140 communicates with the storage tank 120, then the pumping device 140 communicates with the cooling module 130 through another refrigerant pipe 101, the cooling module 130 connects with one quick connector 110 through the refrigerant pipe 101, the quick connector 110 connects with one interface 102 on the electromagnetic shielding box housing 150, the interface 102 in turn connects with one end of the copper pipe of the magnetic stimulation coil, the other end of the copper pipe connects with another interface 102 on the electromagnetic shielding box housing 150, the another interface 102 communicates with the storage tank 120 through the refrigerant pipe 101 through the quick connector 110, thereby realizing a cooling circuit of the refrigerant from the storage tank 120, the cooling module 130 to the magnetic stimulation coil 10 or 10'.

The cooling module 130 performs temperature adjustment control by the control board 135, and specifically, the control board 135 reads the temperature of the refrigerant in real time by the temperature sensor 136 provided on the refrigerant pipe 101 at the refrigerant outlet of the cooling module 130. The control board 135 may receive an external command in real time to turn on, turn off, and control the temperature of the cooling module 130.

The power source 160 is in turn electrically connected to the controller 141 of the pumping device 140, the pumping device 140 and the control board 135 to provide electrical power. The controller 141 is used to control the opening and closing of the pumping device 140.

Referring to fig. 7, a schematic diagram of a drive unit in a magnetic stimulation assembly of one embodiment of the present invention is shown. In the invention, in order to optimize the design volume, the optimal heat dissipation and the like, a parameter C in the core discharge resonance LC parameters, namely a high-voltage energy storage charging and discharging capacitor, is designed. In one embodiment, the shape and size of the high voltage energy storage charging and discharging capacitor can be set according to needs.

In fig. 7, the driving unit includes a DC power supply DC, a first switch S1, a second switch S2, a high-voltage energy storage charging/discharging capacitor C, and a controller. The high-voltage energy storage charging and discharging capacitor C is connected between the first switch S1 and the second switch S2 and is grounded, and control time sequences for controlling the first switch S1 and the second switch S2 to be opened and closed are mutually pulse waveforms.

In practical use, the half-bridge quasi-resonant topological circuit is adopted to obtain higher efficiency and stability for the magnetic stimulation component. The control time sequences of the first switch S1 and the second switch S2 are complementary pulse waveforms, namely when the first switch S1 is closed, the high-voltage energy storage charging and discharging capacitor C is charged, and the second switch S2 is disconnected. When the second switch S2 is closed, the high-voltage energy storage charging and discharging capacitor C discharges the magnetic stimulation coil 10 or 10', and the first switch S1 is in a closed state. It is understood that the control timing of the first switch S1 and the second switch S2 are controlled by the TMS control unit.

Secondly, in order to aim at the dose required by the dominant therapy, a charging unit meeting the requirement needs to be designed, namely, the rapid charging needs to be realized, so that the requirement of the dominant therapy on pulse timing is met.

According to the TMS pulse working characteristic, the high-voltage energy storage charging and discharging capacitor is required to be charged all the time. In the embodiment, a half-bridge quasi-resonant topology circuit is adopted to charge the capacitor. It should be noted that consideration is required for the selection of the topology circuit, and the general conventional topology circuit with high power and high efficiency is not suitable for the advantageous therapy or the TMS magnetic stimulation technique.

Referring to fig. 8, a schematic structural diagram of a driving unit 200 in a magnetic stimulation assembly according to an embodiment of the invention is shown. The driving unit 200 is also referred to as a discharging chamber. The driving unit 200 comprises a discharging box shell 201, a fan 202, a coil output driving connector 205, an input power supply relay 207, a discharging switch module 208, a discharging box upper cover 210, a current control board 211, a main control PCB assembly 212, a high-voltage energy storage charging and discharging capacitor 213, a power supply input connector 215, a control harness connector 216, a high-voltage charging power supply input connector 217, a control and power supply connector 218, an isolation cover 220 and the like.

As shown in fig. 8, the discharge casing case 201 is connected to the charging unit 300 (shown in fig. 10) and the magnetic stimulation unit control unit 400 (shown in fig. 11) by a wire harness. All components within the discharge case housing 201 are mounted to the case housing 201 by various fasteners (e.g., screws). The fan 202 is used for dissipating heat of each component in the discharge chamber. The fan 202 and the fan cover net 203 are fixed to the discharge case 201 by fixing members 204 such as long screws. The fan 202 is connected to the power input terminal 215 through a wire harness, thereby providing power supply thereto.

The coil output drive connector 205 is fixed to the discharge vessel case 201 by a fixing member 206 such as a screw. Is connected to the high-voltage energy-storage capacitor 213 through the negative high-voltage wire harness, and is connected to the discharge switch module 208 through the positive high-voltage wire harness.

The input power relay 207 is used to control the power of the charging unit 300. Connected to the control and power connector 218 of the charging unit 300 with a wire harness. The input power supply relay 207 is fixed to the case housing 201 by screws.

The discharge switch module 208 is connected to the current control board 211 through a control harness and to the coil output drive connector 205 and the high voltage energy storage capacitor 213 through a high voltage harness. In addition, the invention is also provided with a grounding bar 209, and all components needing grounding are connected with the grounding bar 209 through a wire harness.

The discharge vessel upper cover 210 and the discharge vessel housing 201 form a complete housing of the drive unit 200, providing similar protection thereto, and having a substantially rectangular or square shape.

The current control board 211 is connected to the main control PCB assembly 212 through a wiring harness, and is also connected to the discharge switch module 208 through a driving wiring harness and a high voltage signal collecting wiring harness. The master PCB assembly 212 is connected to a control harness connector 216 by a harness.

In order to insulate the high voltage energy storage charging and discharging capacitor 213, a nut cap 214 is also provided.

The power input connector 215 receives an external power input on the one hand and is connected to the input power relay 207 and the main control PCB assembly 212 through a wire harness on the other hand. The control harness connector 216 is connected to the main control PCB assembly 212 via a harness on the one hand and accepts the harness connection of an external controller on the other hand.

The high voltage charging power input connector 217 is externally connected to the charging unit 300 through a wire harness, and internally connected to the high voltage energy storage capacitor 213 through a wire harness.

The charging box control and power connector 218 is externally connected to the charging box by a wiring harness, and internally connected to the input power relay 207 and the main control PCB assembly 212 by a wiring harness.

Fasteners 219 such as mounting screws are used to secure the high voltage charging power input connector 217, the charging unit control and power connector 218 to the case housing 201. The isolation cover 220 is used for isolating the discharge switch module 208 from the input power supply relay 207, so as to enhance the insulation. Screws 221 are used to secure cage 220 to tank housing 201.

Referring to fig. 9, a schematic diagram of a charging unit 300 in a magnetic stimulation assembly is shown, according to an embodiment of the invention. In response to the need for a fast charging of the charging system for the benefit therapy, the present invention provides a charging unit 300 that is capable of achieving the pulse timing required for the benefit therapy.

And according to the TMS pulse working characteristic, the high-voltage energy storage capacitor charging capacitor 213 is always charged. Therefore, conventional high power and high efficiency topologies are less suitable in terms of topology selection. Thus in one embodiment a half-bridge quasi-resonant topology is chosen.

The charging unit 300, also referred to as a charging box, includes: EMI circuit, rectifying circuit, (high-voltage) energy storage capacitor, high-power waveform generating circuit, step-up transformer, output rectifying and charging circuit control board.

The energy in the energy storage capacitor is converted into pulse waveform by a high-power waveform generating circuit, the pulse waveform is input into a step-up transformer, the input voltage is low, the high-voltage pulse is obtained after the step-up of the transformer, the high-voltage direct current output is obtained after the step-up of the input voltage, and the voltage is charged into a customized high-voltage energy storage charging and discharging capacitor 213 in the driving unit 200. The power of this waveform generation circuit determines the charging speed of the charging unit 300.

Referring to fig. 10, a schematic structural diagram of a charging unit 300 according to an embodiment of the present invention is shown. The charging unit 300, also referred to as a charging box, includes a charging box case 301, a charging power supply board heat sink 302, a heat radiation fan 305, a fan cover 306, an output high voltage connector 308, an input power supply and control connector 309, a charging box cover 310, a charging circuit board 311, and the like.

Specifically, a charging box case 301 is provided for storing and fixing the above-described respective components. The charging power supply board heat sink 302 is fixed to the charging box case 301 by fixing members 303 such as screws. In addition, copper studs 304 are provided to secure the charging circuit board 311 to the charging power supply board heat sink 302, thereby dissipating heat from the charging circuit board 311. The heat radiation fan 305 is provided at one end of the charging box case 301, and is fixed to the charging box case 301 together with the fan cover 306 by a fixing member 307 such as a long screw.

The output high voltage connector 308 is externally connected to the discharge tank 200 by a high voltage harness, and internally connected to the charging circuit board 311 by a harness. The input power and control connector 309 is externally connected to the discharge tank 200 through a wire harness, and internally connected to the charging circuit board 311 through a wire harness. In order to form a complete charging box, a charging box cover 310 is also provided, which is disposed to cover the charging box 301 in a rectangular shape. In addition, can also set up pilot lamp board 312, be connected to charging control panel 11 through the pencil to instruct whether to charge and open.

According to another embodiment of the present invention, there is also provided a magnetic stimulation device (not shown). The magnetic stimulation device comprises:

the magnetic stimulation unit described above;

In particular, the magnetic stimulation device further comprises a first communication module (not shown) and a second communication module (not shown). The first communication module is in wireless connection with a first terminal and is configured to transmit the electromyographic signal to the terminal; the second communication module is connected with the magnetic stimulation unit and is configured to transmit the real-time synchronous signal sent by the magnetic stimulation unit to obtain the first time when the magnetic stimulation unit outputs energy.

In one example, the magnetic stimulation unit may be used for inducing an electromyographic signal, and may also be used for manipulating a body part by means of a magnetic field.

In one example, the terminal may be a personal computer (e.g., desktop, all-in-one, laptop, tablet, palmtop, ultrabook, etc.), a mobile phone, a digital television, a smart watch, a wearable device, a mobile intelligent terminal (e.g., a virtual computer tracked by a camera and projected by an infrared laser), and the like, capable of sending commands to the acquisition module, processing data transmitted by the magnetic stimulation device, and the like.

According to another embodiment of the present invention, there is provided a magnetic stimulation device (not shown) comprising:

the magnetic stimulation assembly described above;

the system comprises an acquisition module, a data processing module and a data processing module, wherein the acquisition module is configured to acquire electromyographic signals of a human body in real time; and

and the wireless time setting module is used for acquiring the first time of the magnetic field output by the magnetic stimulation unit in the magnetic stimulation assembly, adding the first time into the electromyographic signals to be transmitted, and then transmitting the electromyographic signals with the first time to a terminal for processing.

Specifically, the magnetic stimulation device further comprises a first communication module (not shown) and a second communication module (not shown). The first communication module is in wireless connection with a first terminal and is configured to transmit the electromyographic signal to the terminal; the second communication module is connected with the magnetic stimulation unit and is configured to transmit the real-time synchronization signal sent by the magnetic stimulation assembly to obtain a first time when the magnetic stimulation unit in the magnetic stimulation assembly outputs energy.

In one example, the magnetic stimulation component may be used to induce electromyographic signals.

Specifically, the acquisition module may adopt a wireless transmission technology to perform communication connection with the wireless time synchronization module. It can solve when gathering the MEP waveform with the amazing synchronism of TMS, the module to time of also adopting wireless accurate to TMS inside, its error is steerable at the microsecond level, makes MEP waveform acquisition time error almost negligible.

Referring to fig. 11, a schematic structural diagram of a magnetic stimulation apparatus according to an embodiment of the present invention is shown. The magnetic stimulation device includes a magnetic stimulation unit, a magnetic stimulation unit control unit 400 (e.g., TMS control unit), a drive unit 200 (e.g., TMS drive unit), and a charging unit 300 (e.g., TMS charging unit).

In one embodiment, the magnetic stimulation unit comprises a magnetic stimulation coil generating an alternating magnetic field.

In particular, the magnetic stimulation coil is a shaped coil, in one example the magnetic stimulation coil is 8-shaped or circular.

In addition, the magnetic stimulation unit control unit 400 is configured to control operations of various components in the magnetic stimulation apparatus, including, for example, controlling charging timing and discharging intensity, wirelessly timing with the muscle collecting unit, and communicating with software in the magnetic stimulation apparatus. The magnetic stimulation unit control unit 400 may be fixed to the charging unit 300 directly or through a cradle, and performs wired or wireless communication with various components within the magnetic stimulation device to achieve control thereof.

The driving unit 200 is connected to the magnetic stimulation unit, and its main function is to discharge and drive the magnetic stimulation unit, so as to generate an alternating magnetic field.

The charging unit 300 has a main function of charging the driving unit 200, specifically, charging a capacitor in the charging unit.

In the present embodiment, the driving unit 200 of the magnetic stimulation unit is newly designed for optimizing the volume and heat dissipation, etc. In addition, in order to meet the dosage requirement of the benefit therapy, a charging system of the magnetic stimulation unit meeting the requirement is designed to realize quick charging and meet the pulse timing requirement required by the benefit therapy.

As shown in fig. 1, the magnetic stimulation device further comprises a TMS shielding outer case 503, and the TMS shielding outer case 503 provides an integral EMC shield for the magnetic stimulation device. Specifically, the TMS shielding outer casing 503 may be made of a suitable electromagnetic shielding material or formed by coating an inner or outer surface thereof with a suitable electromagnetic shielding material. In one example, the charging unit 300 and the driving unit 200 are placed within the TMS shield case 503.

The charging unit 300 and the driving unit 200 may be fixedly mounted in the TMS shield case 503 by fixing members 507 such as screws.

In order to better protect the various components in the magnetic stimulation device, a TMS shielding outer casing cover 506 needs to be arranged and assembled with the TMS shielding outer casing 503.

In one embodiment, a TMS tray assembly 501 is also provided on the bottom of the TMS shield outer casing 503, and this TMS tray assembly 501 can provide support for the entire TMS shield outer casing 503.

It will be appreciated that the TMS shielding outer casing 503 may be shaped in any desired form such as rectangular parallelepiped or square, and accordingly, the TMS tray assembly 501 and the TMS shielding outer casing cover 506 are also configured in corresponding shapes to match.

In one embodiment, the magnetic stimulation unit control unit 400, the drive unit 200, and the charging unit 300 are removably secured to the TMS tray assembly 501 by fasteners 507 such as screws, bolts, or the like. Of course, other means, such as welding, may be used to securely attach the TMS tray assembly 501.

TMS shield

case connection terminals

508, 509 for connecting an external power supply line and a communication line are provided on one side of the TMS shield case 503, and the number of the connection terminals is not limited and may be set to 2, 3 or more. Those skilled in the art can make the settings accordingly as needed.

In the embodiment of fig. 1, two charging units 300 are provided, which are connected to the driving unit 200 through a wire harness to perform timing control and protection in the charging units 300. The driving unit is connected to the control unit 200 by a flat cable, and is used for controlling the discharge energy and the discharge timing.

(2) According to the magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device, the optimized winding pattern of the magnetic stimulation coil, such as a circular coil or an 8-shaped coil, is found through three stages of theoretical calculation, computer simulation, physical verification and the like, and the good comprehensive performance is realized;

(3) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention adopt the magnetic stimulation coil with a four-layer structure design, so that the problems of large driving current, serious cable heating, heavy coil weight and the like are solved;

(7) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention have the characteristics of high voltage and large heat generation amount in consideration of the magnetic stimulation coil, adopt a semiconductor refrigeration mode, and can adopt a refrigeration mode of semiconductor refrigeration and air cooling under the condition of requirement so as to realize better heat dissipation effect and meet the requirement of low noise;

(11) The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the invention use the key integrating the indicator light and the switch, so that the space is saved;

Although a few embodiments of the present general inventive concept have been shown and described, it will be appreciated by those skilled in the art that changes may be made in these embodiments without departing from the principles and spirit of the general inventive concept, the scope of which is defined in the appended claims and their equivalents.

Claims

1. A magnetic stimulation unit, characterized in that the magnetic stimulation unit comprises:

and the insulating shell is formed by pouring high-voltage-resistant materials between the adjacent parts of the hollow conductors through vacuum, and the shape of the insulating shell is consistent with that of the magnetic stimulation coil.

2. Magnetic stimulation unit according to claim 1,

the insulating refrigerating fluid comprises silicone oil; the height of the insulating shell higher than the upper surface or the lower surface of the magnetic stimulation coil is 1-5mm.

3. A magnetic stimulation unit according to claim 1,

the hollow conductor of the magnetic stimulation coil has two ends,

the refrigerant inlet pipe and the refrigerant outlet pipe are respectively communicated with the two tail ends after passing through the lengthened joint, the refrigerant interface and the parallel connection block to form a refrigerant loop;

two power lines are respectively and electrically connected with the two tail ends after passing through the lengthened joint, the electrical interface and the parallel connection block to form an electrical loop,

the lengthened joint leads the two power wires, the refrigerant inlet pipe and the refrigerant outlet pipe out of the insulating shell.

4. The magnetic stimulation unit of claim 3,

the magnetic stimulation coil is a circular coil, the circular coil is a four-layer structure formed by winding a hollow conductor from outside to inside in turn according to a circle for a plurality of turns, and from inside to outside in turn according to a circle for a plurality of turns at the center, and the four-layer structure is formed by repeatedly winding the hollow conductor.

5. A magnetic stimulation unit according to claim 1,

the magnetic stimulation coil is a figure-8 coil and is divided into left and right parts of the figure-8 coil, each of the left and right parts having two ends,

wherein the refrigerant inlet pipe and the refrigerant outlet pipe pass through the lengthened joint to be connected with the three-way joint and then become two refrigerant inlet branch pipes and two refrigerant outlet branch pipes, the two refrigerant inlet branch pipes are respectively communicated with one tail ends of the magnetic stimulation coils in the left part and the right part after passing through the refrigerant interface and the parallel connection block, correspondingly, the two refrigerant outlet branch pipes are respectively communicated with the other tail ends of the magnetic stimulation coils in the left part and the right part after passing through the refrigerant interface and the parallel connection block to form a refrigerant loop,

two power lines are respectively and electrically connected with one tail end of the magnetic stimulation coils in the left part and the right part through one power line behind the lengthened joint, the insulating pipeline, the electrical interface and the electrical connection block, correspondingly, the other power line is respectively and electrically connected with the other tail end of the magnetic stimulation coils in the left part and the right part to form an electrical loop,

6. A magnetic stimulation unit according to claim 5,

the left part and the right part of the 8-shaped coil are respectively circular coils, the circular coils are of a four-layer structure formed by winding a copper pipe from outside to inside in sequence according to a circle for multiple turns, and then from inside to outside in sequence according to the circle for multiple turns, and the left circular coil and the right circular coil are wound in a mirror symmetry manner and are connected in series;

a positioning bulge is arranged on the insulating shell.

7. A magnetic stimulation unit according to claim 4 or 6,

the four-layer structure sequentially comprises a first adjusting inductance layer, a second adjusting inductance layer, a third magnetic field action layer and a fourth magnetic field action layer from bottom to top, the winding number range of the first adjusting inductance layer and the second adjusting inductance layer is set to be 2-3 turns, and the winding number range of the third magnetic field action layer and the fourth magnetic field action layer is set to be 3-4 turns.

8. A magnetic stimulation unit according to claim 7,

the diameter range of the circular coil and the circular coil at the left part and the right part of the 8-shaped coil is set to be 3.8-7.2 cm.

9. A magnetic stimulation unit according to claim 3 or 5,

the refrigerant inlet pipe, the refrigerant outlet pipe and the power line are wrapped in the insulated pipeline and extend from the parallel connection block to the lengthened joint.

10. A magnetic stimulation assembly, characterized in that the magnetic stimulation assembly comprises:

a magnetic stimulation unit according to any one of claims 1-9;

a charging unit configured to charge the magnetic stimulation unit.

11. The magnetic stimulation assembly of claim 10,

the magnetic stimulation component is also provided with a control unit for controlling the magnetic stimulation component;

the driving unit comprises a direct current power supply, a first switch, a second switch, a high-voltage energy storage charging and discharging capacitor and a controller,

the high-voltage energy storage charging and discharging capacitor is connected between the first switch and the second switch, and control time sequences of the controller for controlling the first switch and the second switch to be switched on and off are pulse waveforms.

12. The magnetic stimulation assembly of claim 11,

the charging unit also comprises a half-bridge quasi-resonant topological circuit for charging the high-voltage energy storage charging and discharging capacitor;

the control unit also comprises a wireless accurate time setting unit adopting a muscle acquisition wireless transmission technology.

13. The magnetic stimulation assembly of claim 12,

the driving unit is connected with the charging unit through a wire harness, the driving unit is connected with the control unit through a flat cable, and the control unit is fixed on one end of the charging unit and is electrically connected with the charging unit.

14. The magnetic stimulation assembly of any of claims 10-13,

the magnetic stimulation assembly further comprises: and the cooling unit is used for actively refrigerating the magnetic stimulation unit, and the cooling unit is a semiconductor cooling system adopting a semiconductor refrigeration technology.

15. The magnetic stimulation assembly of claim 14,

the cooling unit includes:

a storage tank storing a refrigerant therein;

a cooling module for performing heat exchange of refrigerant by using semiconductor refrigeration technology;

a pumping device that draws refrigerant into the pumping device through a refrigerant conduit and pumps the refrigerant to the cooling module;

the refrigerant cooled by the cooling module enters the magnetic stimulation coil through the refrigerant pipeline, and flows back to the storage tank after cooling the magnetic stimulation coil.

16. The magnetic stimulation assembly of claim 15,

the cooling unit further includes:

the control panel is used for controlling the cooling module and reading the temperature of the refrigerant in real time through a sensor arranged on a refrigerant pipeline at the outlet of the cooling module;

the power supply is electrically connected with the controller of the pumping device, the pumping device and the control panel in sequence;

at least two quick-connect connectors connecting the magnetic stimulation coil with the cooling unit.

17. The magnetic stimulation assembly of claim 16,

the cooling unit comprises an electromagnetic shielding box shell, the cooling module is arranged at one end in the electromagnetic shielding box shell, the refrigerant pipeline connected with the cooling module is communicated with a corresponding interface on the electromagnetic shielding box shell through at least two quick-plugging ports, the pumping device, the power supply and the storage box are arranged in the electromagnetic shielding box shell, and the refrigerant pipeline connected with the storage box is communicated with another corresponding interface on the electromagnetic shielding box shell through at least two quick-plugging ports.

18. The magnetic stimulation assembly of claim 17,

the cooling module comprises a cold row, a semiconductor refrigeration piece and a radiating fin, the cold surface of the semiconductor refrigeration piece is attached to the cold row, the hot surface of the semiconductor refrigeration piece is attached to the radiating fin,

the cooling module further comprises

A thermally conductive interface material between the cold side and the cold row and between the hot side and the heat sink;

a fan disposed on the cooling module proximate the heat sink.

19. A magnetic stimulation device, characterized in that the magnetic stimulation device comprises:

a magnetic stimulation unit according to any one of claims 1-9;

the wireless time setting module is used for collecting the first time of the magnetic field output by the magnetic stimulation unit, adding the first time into the electromyographic signals to be transmitted, and then transmitting the electromyographic signals with the first time to a terminal for processing.

20. A magnetic stimulation device is characterized in that,

the magnetic stimulation device comprises:

a magnetic stimulation assembly according to any one of claims 10-18;