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

Abstract

The application 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 comprises a magnetic stimulation coil which is made of a hollow conductor wound into a predetermined pattern, a pipe wall of the hollow conductor is arranged as an electrified circuit, and an insulating refrigerant is filled in a hollow cavity of the hollow conductor; and an insulating shell which is formed by filling a high-pressure-resistant material through vacuum between adjacent parts of the hollow conductor, and a shape of the insulating shell is consistent with a shape of the magnetic stimulation coil. The magnetic stimulation unit, the magnetic stimulation assembly and the magnetic stimulation device provided by the application optimize the peripheral coating structure of the magnetic stimulation coil, so that the weight of the magnetic stimulation coil is the lightest under the condition of meeting safety requirements.

Description

Technical Field

[0001] This invention relates to the field of TMS magnetic stimulation technology, and in particular to a magnetic stimulation unit, magnetic stimulation component, and magnetic stimulation device. Background Technology

[0002] Currently, transcranial magnetic stimulation (TMS) devices on the market have found that the magnetic stimulation coils cannot meet the demands for prolonged, continuous, and high-intensity magnetic stimulation during the adjustment of subjects. To achieve high-intensity magnetic stimulation, TMS devices require a larger output current. Consequently, the current in the TMS magnetic stimulation coils is also larger, leading to overheating of the coils and connected cables, and thus a greater demand for electrical power.

[0003] Meanwhile, after prolonged high-intensity magnetic stimulation, the magnetic excitation coil is prone to overheating and stopping its output, preventing the treatment process from being completed. While measures can prevent the magnetic excitation coil from overheating, such as reducing the duration or the intensity of the output magnetic field, this significantly reduces the modulation effect, failing to achieve the desired modulation. Furthermore, existing TMS magnetic stimulation devices generally suffer from large size, making them inconvenient to use.

[0004] Therefore, the structure of the magnetic stimulation coil needs to be redesigned to achieve a larger current in the magnetic stimulation coil, meet greater power requirements, and avoid frequent overheating. Summary of the Invention

[0005] To address at least one of the aforementioned problems and deficiencies in the prior art, embodiments of the present invention provide a magnetic stimulation unit, a magnetic stimulation component, and a magnetic stimulation device, the specific technical solutions of which are as follows:

[0006] According to one aspect of the present invention, a magnetic stimulation unit is provided, wherein,

[0007] The magnetic stimulation unit includes:

[0008] The magnetic stimulation coil is made of a hollow conductor wound into a predetermined pattern, the tube wall of the hollow conductor is configured as an energized circuit, and the hollow cavity of the hollow conductor is filled with insulating refrigerant.

[0009] An insulating shell is formed by vacuum-filling high-voltage resistant material between adjacent portions of the hollow conductor, and the shape of the insulating shell is consistent with the shape of the magnetic stimulation coil.

[0010] According to another aspect of the present invention, a magnetic stimulation component is provided, wherein,

[0011] The magnetic stimulation component includes:

[0012] A magnetic stimulation unit, wherein the magnetic stimulation unit is any one of the magnetic stimulation units described above;

[0013] A driving unit configured to drive the magnetic stimulation unit to generate an alternating magnetic field;

[0014] A charging unit, configured as a magnetic stimulation unit for charging.

[0015] According to another aspect of the present invention, a magnetic stimulation device is provided, wherein,

[0016] The magnetic stimulation device includes:

[0017] A magnetic stimulation unit, wherein the magnetic stimulation unit is any one of the magnetic stimulation units described above;

[0018] The acquisition module is configured to acquire electromyographic signals from the human body in real time; and

[0019] The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

[0020] According to another aspect of the present invention, a magnetic stimulation device is provided, wherein,

[0021] The magnetic stimulation device includes:

[0022] A magnetic stimulation component, wherein the magnetic stimulation component is any one of the magnetic stimulation components described above;

[0023] The acquisition module is configured to acquire electromyographic signals from the human body in real time; and

[0024] The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit in the magnetic stimulation component, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

[0025] The magnetic stimulation unit, magnetic stimulation assembly, and magnetic stimulation device provided in the embodiments of the present invention have at least one of the following advantages:

[0026] (1) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention have optimized the outer covering structure of the magnetic stimulation coil so that the weight of the magnetic stimulation coil is minimized while meeting safety requirements. In this process, high pressure-resistant materials such as FR4 and resin are mainly used, and vacuum infusion technology is adopted to ensure that the copper tubes between adjacent magnetic stimulation coils, the surfaces between magnetic stimulation coils and other parts meet the pressure resistance requirements, thereby improving the strength of the magnetic stimulation coil body.

[0027] (2) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention have found an optimized winding pattern of the magnetic stimulation coil through three stages: theoretical calculation, computer simulation and physical verification, such as circular coil or figure-eight coil, and achieved better comprehensive performance.

[0028] (3) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopts a four-layer structure design of magnetic stimulation coil, which solves the problems of large driving current, serious cable heating and large coil weight.

[0029] (4) The magnetic stimulation unit, magnetic stimulation component, and magnetic stimulation device provided by this invention employ a half-bridge quasi-resonant topology circuit in the TMS charging unit. This ensures that the high-voltage energy storage capacitor is continuously charged according to the TMS pulse operating characteristics. Therefore, a charging system designed to meet the TMS requirements for the optimal therapeutic dose is achieved, enabling rapid charging and reaching the optimal pulse timing for the therapeutic. In current TMS charging units, the use of a half-bridge quasi-resonant topology circuit results in relatively high efficiency and stability.

[0030] (5) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention are designed with a cooling structure for the magnetic stimulation coil, for example, by using the technology of refrigerant and electrical separation, so that the refrigerant interface and the electrical interface are separated, effectively eliminating the impact on electrical safety when the refrigerant leaks.

[0031] (6) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopt a three-way connection for the refrigerant inlet of the magnetic stimulation coil, especially for the figure-eight magnetic stimulation coil, so that the copper tubes on both sides of the figure-eight can simultaneously input refrigerant, accelerate heat dissipation, and at the same time keep the temperature of the copper tubes on both sides symmetrical and balanced.

[0032] (7) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention take into account the characteristics of high voltage and large heat generation when the magnetic stimulation coil performs magnetic stimulation. They adopt a semiconductor cooling mode. When necessary, a cooling mode of semiconductor cooling plus air cooling can also be adopted to achieve better heat dissipation effect and at the same time achieve the requirement of low noise.

[0033] (8) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention use highly insulating silicone oil and the like as cooling refrigerant to ensure the safety of the discharge process.

[0034] (9) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopt a pumping device, storage tank, cold air radiator, refrigerant pipe and quick connector to form a refrigerant circulation loop to realize heat conduction to the magnetic stimulation coil and the corresponding cooling part.

[0035] (10) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention can perform real-time temperature monitoring and real-time intelligent control of the cooling of the magnetic stimulation coil by configuring a temperature sensor and a control board.

[0036] (11) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention use a button that integrates indicator light and switch, which saves space;

[0037] (12) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention solve the synchronization problem between the acquisition of motion evoked potential (MEP) waveform and TMS stimulation through the designed wireless time synchronization module. The TMS also adopts a wireless precision time synchronization unit, whose error can be controlled at the microsecond level, so that the MEP waveform acquisition time error can be almost ignored. Attached Figure Description

[0038] These and / or other aspects and advantages of the present invention will become apparent and readily understood from the following description of preferred embodiments taken in conjunction with the accompanying drawings, in which:

[0039] Figure 1 This is a perspective structural schematic diagram of a portion of a magnetic stimulation unit using a circular magnetic stimulation coil according to an embodiment of the present invention.

[0040] Figure 2 This is a schematic diagram of a figure-eight magnetic stimulation coil obtained through simulation calculation according to another embodiment of the present invention;

[0041] Figure 3 Is using Figure 2 A perspective view of a portion of the magnetic stimulation unit of the figure-eight shaped magnetic stimulation coil shown.

[0042] Figure 4 This is a schematic diagram of the cooling unit of a magnetic stimulation assembly according to an embodiment of the present invention;

[0043] Figure 5 This is a schematic diagram of the explosion and disassembly of a cooling unit for magnetic stimulation according to an embodiment of the present invention.

[0044] Figure 6 It shows Figure 5 The diagram shows the structure of the cooling module.

[0045] Figure 7 A schematic diagram of the driving unit in a magnetic stimulation assembly according to an embodiment of the present invention is shown;

[0046] Figure 8 A schematic diagram of the structure of a drive unit according to an embodiment of the present invention is shown;

[0047] Figure 9 A schematic diagram of the charging unit in a magnetic stimulation assembly according to an embodiment of the present invention is shown;

[0048] Figure 10 A schematic diagram of the structure of a charging unit according to an embodiment of the present invention is shown;

[0049] Figure 11 A schematic diagram of the explosion and disassembly of a magnetic stimulation device according to an embodiment of the present invention is shown. Detailed Implementation

[0050] The technical solution of the present invention will be further described in detail below through embodiments and in conjunction with the accompanying drawings. In this specification, the same or similar reference numerals indicate 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 overall inventive concept of the present invention and should not be construed as a limitation thereof.

[0051] In order to solve the technical problems raised in the background section, the present invention aims to redesign magnetic stimulation coils or magnetic stimulation units to obtain magnetic stimulation units that can meet the requirements of advantageous therapies.

[0052] The first step is to conduct a theoretical system design for the entire system using the magnetic stimulation unit. This mainly considers all constraints such as the magnetic stimulation coil, cooling (power and method), power supply power and efficiency, and cable heating. The most important aspect is designing the optimal core discharge resonance (LC) parameters. The LC parameters determine the discharge pulse width, and the system losses caused by LC and its parasitic parameters also determine the charging speed, which in turn determines the overall charging power, system size, and efficiency. Furthermore, the L value also determines the designable structural dimensions and shape range of the magnetic stimulation coil.

[0053] From the LC resonant frequency formula: F=1 / (2*Pi*Sqrt(L*C)),

[0054] Energy loss formula: E=C*(Vi*Vi-Vs*Vs) / 2, where Vi is the initial voltage of capacitor discharge and Vs is the residual voltage of capacitor discharge.

[0055] Different LC combinations were explored, and the parasitic parameters of different coil materials were combined to simulate the circuit and coil magnetic field. The most suitable parameter combination for the therapeutic effect was obtained, including L, C, and the acceptable range of coil parasitic resistance. Finally, the value of L was determined.

[0056] The second step involves addressing the core component—designing the magnetic stimulation coil itself. After determining the inductance L of the magnetic stimulation coil in the first step, various performance indicators of the coil were considered, such as focusing ability, maximum output magnetic field strength, drive current at maximum output magnetic field strength, weight, and inductance. The magnetic stimulation coil was then optimized. The optimization process primarily involved three stages: theoretical calculations, computer simulations, and physical verification.

[0057] In terms of theoretical calculations:

[0058] The heating power P = I*I*R, which is the product of the square of the effective value of the driving current I and the parasitic resistance R of the coil, where R includes both DC and AC resistance. When selecting a coil (copper tube) model with the largest possible cross-sectional area while still meeting the required magnetic field strength, choose one that meets these requirements.

[0059] According to Ampère's circuital law:

[0060] ∫B dl=μ0*Σi, calculate the magnetic field distribution and intensity of the current-carrying conductor.

[0061] Based on the rules and requirements for the coil, the approximate shape is derived.

[0062] In terms of computer simulation:

[0063] Based on theoretical calculations, the approximate shape of the coil is estimated, and then the coil structure is designed under different parameters such as spacing for specific shapes, followed by simulation.

[0064] This invention simulated dozens of coils with different structures and forms. Finally, by combining the data, the best-performing coils for several key indicators were identified. These best coils were then physically fabricated and verified. The coil that was most suitable for the therapeutic effect was then used as the final output.

[0065] See Figure 1 The diagram shows a perspective view of a magnetic stimulation unit according to an embodiment of the present invention. It shows that the magnetic stimulation unit takes the form of a circular coil 10. Figure 1 The image shows only a portion of the magnetic stimulation unit, not the complete view. The right side is cut off by a dashed line to indicate that the insulating shell, refrigerant pipes, and power cord may also have extensions and subsequent corresponding joints. Figure 3 and Figure 1 Similarly, a complete view is not shown, and will not be described further.

[0066] As described above, theoretical calculations, computer simulations, and physical verification suggest that arranging the magnetic stimulation coil in a circular shape achieves better overall performance. Specifically, the magnetic stimulation coil is made from any suitable material, such as a hollow conductor like steel pipe, wound into a predetermined pattern, such as a circular coil. The cavity inside the hollow conductor is cooled with a refrigerant such as highly insulating silicone oil, and the inner wall of the hollow conductor is energized, generating a magnetic field under the influence of the current. The magnetic field acts on the corresponding area of ​​the subject's brain and induces a current, thereby enabling diagnosis or treatment of the subject. It should be noted that the provided magnetic stimulation device can be applied not only to the diagnosis and treatment of the brain but also to peripheral neuromuscular systems.

[0067] In one embodiment, the magnetic stimulation coil is a circular coil 10, which is a four-layer structure formed by repeatedly winding a copper tube in a circular fashion from the outside to the inside, then winding it in a circular fashion from the inside to the outside again at the center. Of course, those skilled in the art will understand that the circular coil can be a single-layer multi-turn coil structure, a double-layer multi-turn coil structure, or a multi-layer multi-turn coil structure. Because it is wound from a single copper tube, the magnetic stimulation coil has two ends.

[0068] In one example, the circular coil is preferably designed as a four-layer structure, which, from bottom to top, includes a first regulating inductance layer (not shown), a second regulating inductance layer (not shown), a third magnetic field layer (not shown), and a fourth magnetic field layer (not shown). Since the third and fourth magnetic field layers can directly act on the control area, they require a stronger magnetic field and a wider range of action; therefore, the number of turns in the third and fourth magnetic field layers is set to 3-4 turns. Meanwhile, since the first and second regulating inductance layers are mainly used to adjust the inductance, the number of turns in the first and second regulating inductance layers is set to 2-3 turns.

[0069] More preferably, the diameter of the circular coil is set to be in the range of 3.8 to 7.2 cm. Furthermore, the copper tube of the circular coil is a hollow copper tube with an outer diameter of 4-6 mm and an inner diameter of 1-3 mm.

[0070] By using a four-layer structure and a range of circular coil diameters, the weight of the circular coil can be greatly reduced. At the same time, the driving current of the coil can be reduced while ensuring long-term control, and the problem of severe cable overheating can be solved.

[0071] See Figure 2An example of a magnetic stimulation coil according to another embodiment of the present invention is shown. The magnetic stimulation coil is shaped like a figure 8 10'. The magnetic stimulation coil is a figure 8 coil divided into a left portion 12 and a right portion 16 of the figure 8. The left portion 12 has two ends 13 and 14, and the right portion 16 also has two ends 17 and 18. The left portion 12 and the right portion 16 of the figure 8 magnetic stimulation coil 10' are both circular coils, which are formed by winding a copper tube 11 in a circular pattern from the outside to the inside, and then winding it in a circular pattern from the inside to the outside again at the center, forming a four-layer structure. The circular coils of the left portion 12 and the right portion 16 are mirror-symmetrically wound. Similarly, the magnetic stimulation coil 10' can have a single-layer coil structure, a double-layer coil structure, or a multi-layer coil structure.

[0072] In one example, the left portion 12 and the right portion 16 of the figure-eight coil are preferably designed as a four-layer structure, and the four-layer structure includes, from bottom to top, a first regulating inductance layer (not shown), a second regulating inductance layer (not shown), a third magnetic field layer (not shown), and a fourth magnetic field layer (not shown). Since the third and fourth magnetic field layers can directly act on the regulating part, they require a larger magnetic field strength and a wider range of action. Therefore, the number of turns of the third and fourth magnetic field layers is set to 3 to 4 turns. At the same time, since the first and second regulating inductance layers are mainly used to adjust the inductance, the number of turns of the first and second regulating inductance layers is set to 2 to 3 turns.

[0073] More preferably, the diameters of the left portion 12 and the right portion 16 of the figure-eight coil are both set to be between 3.8 and 7.2 cm. Furthermore, the copper tube of the figure-eight coil is a hollow copper tube with an outer diameter of 4-6 mm and an inner diameter of 1-3 mm.

[0074] By using a four-layer structure and a range of circular coil diameters, the weight of the figure-eight coil can be greatly reduced. At the same time, the driving current of the coil can be reduced while ensuring long-term control, and the problem of severe cable overheating can be solved.

[0075] It should be noted that only the forms of the two magnetic stimulation coils after two simulation verifications are given here. Those skilled in the art can choose any other desired pattern.

[0076] As described above in this embodiment, by setting the magnetic stimulation coils into irregular patterns such as figure-eight coils 10' or circular coils 10, simulation verification showed that they exhibited relatively good overall performance indicators. Subsequently, an insulating shell 20 was set around the magnetic stimulation coils, which solved problems such as large driving current, severe cable heating, and heavy coil weight.

[0077] One embodiment of the present invention also provides an optimized design scheme for the outer casing structure, specifically an optimized design of the materials surrounding the magnetic stimulation coil. The design goal is to achieve the lightest possible weight while meeting insulation safety requirements. In practice, copper tubing is selected as the hollow conductor to be wound into the magnetic stimulation coil. An insulating shell 20 is then formed between adjacent portions of the hollow conductor by vacuum-filling a high-voltage resistant material. The insulating shell 20 is primarily made of high-voltage resistant materials such as FR4 and resin; vacuum-filling technology is used to ensure that the voltage resistance between adjacent copper tubing, and between the copper tubing and the upper and lower surfaces of the magnetic stimulation coil, meets the requirements, and the coil body strength also meets the requirements.

[0078] In terms of weight reduction, the following measures were mainly adopted: the insulation was made as thin as possible while meeting the withstand voltage requirements; the filling material was made to fit the shape of the coil itself as closely as possible.

[0079] In one embodiment, the insulating shell 20 is shaped to match the shape of the magnetic stimulation coils 10, 10'. See also Figure 1 The insulating shell 20 is also generally circular. The insulating shell 20 protrudes 1-5 mm above the upper or lower surface of the magnetic stimulation coils 10 and 10'. The thickness of the insulating shell 20 is set to 1-5 mm primarily to achieve the thinnest possible thickness while meeting voltage withstand requirements, thereby reducing the weight of the magnetic stimulation coils 10 and 10'. Furthermore, making the shape of the insulating shell 20 consistent with the shape of the magnetic stimulation coils 10 and 10' also helps reduce weight and achieve a good magnetic stimulation effect.

[0080] See Figure 2 and Figure 3 For the figure-eight magnetic stimulation coil 10', the shape of the insulating shell 20 is also set to be figure-eight to fit the shape of the magnetic stimulation coil 10' as closely as possible, and the height of the insulating shell 20 above the upper or lower surface of the magnetic stimulation coil 10' is 1-5mm.

[0081] In one embodiment, see Figure 1 or Figure 3 The magnetic stimulation unit also includes indicator lights located at the ends of the magnetic stimulation coils 10 and 10' for indicating that the magnetic stimulation coils 10 and 10' are turned on, and a button 90 for switching the magnetic stimulation coils 10 and 10' on and off. Combining the indicator light and the switch into a single button effectively saves space.

[0082] In one embodiment, see Figure 1 or Figure 3The magnetic stimulation unit includes at least one temperature sensor 30 disposed on the magnetic stimulation coils 10 and 10' and located within the insulating shell 20. By providing the temperature sensor 30, the heating status of the magnetic stimulation coils 10 and 10' can be effectively monitored for effective cooling.

[0083] like Figure 1 As shown, the refrigerant inlet pipe and refrigerant outlet pipe pass through the extension joint 80, refrigerant interface 50, and parallel connecting block 40, and are then connected to the two ends to form a refrigerant circuit. Two power lines 6 pass through the extension joint 80, electrical interface (not shown), and parallel connecting block 40, and are then electrically connected to the two ends to form an electrical circuit. The extension joint 80 leads the two power lines 6, the refrigerant inlet pipe, and the refrigerant outlet pipe outside the insulating shell 20.

[0084] Similarly, such as Figure 3 As shown, the refrigerant inlet pipe and the refrigerant outlet pipe, after passing through the extension joint 80 and connecting to the tee joint 70, become two refrigerant inlet branch pipes and two refrigerant outlet branch pipes. The two refrigerant inlet branch pipes, after passing through the refrigerant interface 50 and the parallel connecting block 40, are respectively connected to one end of the magnetic stimulation coil 10' in the left part 12 and the right part 16. Correspondingly, the two refrigerant outlet branch pipes, after passing through the refrigerant interface 50 and the parallel connecting block 40, are respectively connected to the other end of the magnetic stimulation coil 10' in the left part 12 and the right part 16 to form a refrigerant circuit. Two power lines, after passing through the extension joint 80, the insulating pipe 7, the electrical interface 8, and the electrical connecting block 4, connect one power line 6 to one end of the magnetic stimulation coil 10' in the left part 12 and the right part 16, respectively. Correspondingly, the other power line 6 connects to the other end of the magnetic stimulation coil 10' in the left part 11 and the right part 16 to form an electrical circuit. The extended connector 80 leads the two power lines 6, the refrigerant inlet pipe, and the refrigerant outlet pipe out of the insulating shell 20.

[0085] As shown in the figure, the parallel connection block 40 and the electrical connection block 4 are arranged in roughly corresponding positions, for example, as two components facing each other.

[0086] exist Figure 3 Not only does it achieve refrigerant and electrical separation, but it also allows refrigerant to be introduced into both copper pipes simultaneously through the refrigerant pipe and the T-joint 70, which accelerates heat dissipation and keeps the temperature of the magnetic stimulation coils on both sides symmetrical and balanced.

[0087] For easier location tracking, Figure 3In this embodiment, a positioning protrusion 60 is provided on the outer periphery of the insulating shell 20 corresponding to the tee connector 70. The shape of this positioning protrusion 60 can be set to different shapes such as circular, elliptical, square, rectangular, or any ergonomic graphic. In this embodiment, the positioning protrusion 60 is set as a circular protrusion, which is simple and effective and helps to achieve better positioning. Of course, this embodiment is not limited to a circular protrusion. Whether or not to provide this circular positioning protrusion can be selected by those skilled in the art as needed.

[0088] To further improve or enhance the insulation design, the refrigerant inlet pipe, refrigerant outlet pipe, and power cord 6 are enclosed within an insulating pipe 7, extending from the parallel connection block 40 or electrical connection block 4 to the extension joint 8. In other words, the corresponding components are housed within the insulating pipe 7 before being connected and assembled.

[0089] This solution uses the best coil manufacturing materials, taking into account both the output magnetic field strength and coil heating, so that the optimized physical characteristics of the coil become one of the guarantees for the long duration of high-dose output of the superior therapy.

[0090] This solution employs an optimized system LC parameter design method, which can improve output intensity while significantly extending the duration of high-dose continuous output, thus meeting the equipment support requirements for advantageous therapies.

[0091] The magnetic stimulation coil uses oil-electric separation technology to separate the coolant refrigerant interface from the electrical interface, effectively eliminating the impact on electrical safety when coolant leaks.

[0092] In this embodiment, a good heat dissipation effect is achieved by setting a cooling unit for the magnetic stimulation coil. For example, the refrigerant and electrical separation technology is used to separate the refrigerant interface and the electrical interface, effectively eliminating the adverse effects on electrical safety when refrigerant leakage occurs.

[0093] See Figure 4 The diagram illustrates a cooling unit or cooling mechanism in a magnetic stimulation assembly according to another embodiment of the present invention. Addressing the problem of excessive heat generation in the magnetic stimulation coils 10 or 10', and to improve their adaptability to various ambient temperatures, the present invention provides a cooling unit that employs active liquid cooling. This active liquid cooling method can employ thermal cooling, semiconductor cooling, Peltier cooling, etc. In one embodiment, semiconductor cooling is used as an example.

[0094] Using semiconductor cooling can result in advantages such as smaller overall device size, lower noise, and longer lifespan. For example... Figure 4The diagram shows the overall principle of the cooling unit. The cooling unit includes a refrigeration module, cooling pipes, a pumping device, a refrigerant storage tank, a power supply, and a corresponding controller.

[0095] A certain amount of refrigerant (such as highly insulating silicone oil) is pre-stored in the storage tank; other refrigerants such as water, deionized water, and alcohol are also acceptable. A pumping device pumps the refrigerant from the storage tank to the cooling module via cooling pipes. The cooling module cools the incoming refrigerant to a pre-set temperature, then pumps it to the magnetic stimulation coil 10 or 10'. Finally, the refrigerant carries away the heat from the magnetic stimulation coil 10 or 10' and stores it in the storage tank. This cycle repeats to address the issue of severe coil overheating in therapeutic applications, thereby ensuring the coil can continuously deliver the required output dose for therapeutic purposes.

[0096] The controller controls the activation of the pumping device and the power supply, and can set the temperature of the refrigerant output from the cooling module as needed. In other words, the controller can issue different cooling power demands, thereby adjusting and controlling the pumping device and the cooling module. This configuration ensures that the cooling power of the cooling module meets the needs of the therapeutic approach, allowing the magnetic stimulation coil and other components to operate at optimal efficiency and extending their lifespan.

[0097] In one embodiment, the cooling module can employ a dual-sided cooling centralized method for heat dissipation, thereby minimizing the size of the components and improving efficiency.

[0098] In one embodiment, the controller can incorporate machine learning technology to automatically optimize the cooling control algorithm for different usage habits, so that the entire device operates at the lowest average power consumption, highest efficiency, and longest lifespan.

[0099] See Figure 5 The diagram illustrates a cooling unit 100 for a magnetic stimulation assembly. The cooling unit 100 includes at least two quick-connect connectors 110, a storage tank 120, a cooling module 130, a pumping device 140, and other components, which together form a cooling cycle for better cooling of the magnetic stimulation unit performing magnetic stimulation.

[0100] To facilitate quick and easy connection of the refrigerant pipe to the magnetic stimulation coil 10 or 10', at least two quick-connect fittings 110 are used to connect the magnetic stimulation coil 10 or 10' to the cooling unit 100. The number of quick-connect fittings 110 is not particularly limited; those skilled in the art can select an appropriate number and structure as needed. In one embodiment, the quick-connect fitting 110 can be directly connected to the copper tubing of the magnetic stimulation coil 10 or 10'. Alternatively, it can be... Figure 5As shown, it is then connected to the copper pipe through a corresponding connector provided on the housing of the cooling unit 100.

[0101] The storage tank 120 contains a pre-stored amount of refrigerant, such as highly insulating silicone oil. Of course, any other suitable refrigerant, such as distilled water, deionized water, water, transformer oil, alcohol, diesel oil, etc., is also acceptable. The form of the storage tank 120 is not limited. The refrigerant is led out through the refrigerant pipe 101, and a quick-connect fitting 110 is provided at the end of the refrigerant pipe 101.

[0102] During operation, the pumping device 140, such as an oil pump, draws refrigerant from the storage tank 120 into the pumping device 140 and pumps it into the cooling module 130. After being cooled by the cooling module 130, the refrigerant enters the magnetic stimulation coil through the refrigerant pipe 101. After cooling the magnetic stimulation coil, it flows back to the storage tank 120 through the refrigerant pipe 101.

[0103] Combination Figure 6 As shown, the cooling module 130 employs a combination of semiconductor refrigerant technology and air cooling. It can be understood that either of these methods could be used for cooling. The cooling module 130 is used to achieve heat exchange with the refrigerant.

[0104] The cooling module 130 includes a radiator 131, a cooling chip 132, a heat sink 133, and a fan 134. The cooling chip 132 can be a thermoelectric cooler, a thermoelectric cooler, or a Peltier cooler. In one embodiment, the cooling chip 132 is a thermoelectric cooler, with its cold side attached to the radiator 131 and its hot side attached to the heat sink 133. Additionally, a fan 134 is provided on one side of the cooling module 130, which blows ambient air onto the heat sink for cooling. The refrigerant first enters through one end of the radiator 131, completes heat exchange, and then flows out from the other end. In one embodiment, the specific forms of the radiator 131, the thermoelectric cooler 132, and the heat sink 133 are not limited, and the fan 134 can be a conventional fan or a high-power axial fan.

[0105] In the embodiment, the thermal power consumption of the magnetic stimulation coil can be estimated for the conditions with the highest stimulation intensity, the highest frequency, and the longest duration by combining the operating conditions of the magnetic stimulation coil and the temperature that the magnetic stimulation coil 10 or 10' needs to maintain. At the same time, the heat transfer between the coil and the medium can be calculated according to Newton's law of cooling.

[0106] Based on the heat dissipation, coil heat transfer, and the comprehensive performance coefficient of the thermoelectric cooler 132, the model and quantity of the thermoelectric cooler 132 are selected.

[0107] In one embodiment, the radiator 131 and heat sink 133 can be designed according to the hot and cold surface power of the thermoelectric cooler 132. In addition, thermal interface materials can be added, such as thermal grease, thermal gel, thermal pad, phase change material, phase change metal sheet, and thermally conductive adhesive.

[0108] The selection of fan 134 is based on the power consumption and temperature rise of the semiconductor cooling chip 132 to calculate the air volume of fan 34, while also taking into account space and other factors.

[0109] In one embodiment, the fan 134 can be mounted on the heat sink 133 via a bracket.

[0110] Multiple heat sinks 133 are stacked together to achieve better heat dissipation.

[0111] In one embodiment, the cooling unit 100 includes an electromagnetic shielding enclosure 150. The electromagnetic shielding enclosure 150 provides a space for electromagnetic shielding conforming to magnetic stimulation technology; for example, its inner walls may be provided with any suitable shielding coating. The shape of the electromagnetic shielding enclosure 150 is not limited and can be rectangular or square, etc.

[0112] The cooling module 130 is located at the right end inside the electromagnetic shielding box shell 150, and the refrigerant pipe 101 connected to the cooling module 130 is connected to the corresponding interface 102 on the electromagnetic shielding box shell 150 through at least two quick-connect interfaces 110. The pumping device 140, the power supply 160, and the storage tank 120 are placed inside the electromagnetic shielding box shell 150, and the refrigerant pipe 101 connected to the storage tank 120 is connected to another corresponding interface 102 on the electromagnetic shielding box shell 150 through at least two quick-connect interfaces 110.

[0113] Specifically, one end of the refrigerant pipe 101 connected to the pumping device 140 is connected to the storage tank 120. Then, the pumping device 140 is connected to the cooling module 130 through another refrigerant pipe 101. The cooling module 130 is connected to a quick connector 110 through the refrigerant pipe 101. The quick connector 110 is connected to an interface 102 on the electromagnetic shielding box shell 150. The interface 102 is then connected to one end of the copper tube of the magnetic stimulation coil. The other end of the copper tube is connected to another interface 102 on the electromagnetic shielding box shell 150. The other interface 102 is connected to the storage tank 120 through the refrigerant pipe 101 via the quick connector 110, thereby realizing a cooling circuit for the refrigerant from the storage tank 120, the cooling module 130 to the magnetic stimulation coil 10 or 10'.

[0114] The cooling module 130 is temperature-controlled via a control board 135. Specifically, the control board 135 reads the refrigerant temperature in real time using a temperature sensor 136 located on the refrigerant pipe 101 at the refrigerant outlet of the cooling module 130. The control board 135 can receive external commands in real time to control the opening, closing, and temperature of the cooling module 130.

[0115] Power supply 160 is electrically connected in sequence to the controller 141 of the pumping device 140, the pumping device 140, and the control board 135 to provide power. The controller 141 is used to control the opening and closing of the pumping device 140.

[0116] See Figure 7 The diagram illustrates the principle of a drive unit in a magnetic stimulation assembly according to an embodiment of the present invention. In this invention, to optimize design volume and heat dissipation, parameter C, i.e., the high-voltage energy storage charging and discharging capacitor, is first designed in the core discharge resonance LC parameters. In one embodiment, the shape and size of the high-voltage energy storage charging and discharging capacitor can be set as needed.

[0117] exist Figure 7 The drive 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 DC power supply (DC), the first switch (S1), the second switch (S2), and the magnetic stimulation coil 10 or 10' are connected in sequence via wires. The high-voltage energy storage charging / discharging capacitor C is connected between the first switch (S1) and the second switch (S2) and grounded. The controller controls the opening and closing of the first switch (S1) and the second switch (S2) using pulse waveforms.

[0118] In practical applications, using a half-bridge quasi-resonant topology circuit can achieve relatively high efficiency and stability for the magnetic stimulation component. The control timing of the first switch S1 and the second switch S2 is a complementary pulse waveform. That is, 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 open. When the second switch S2 is closed, the high-voltage energy storage charging and discharging capacitor C discharges to the magnetic stimulation coil 10 or 10', and the first switch S1 is closed. It can be understood that the control timing of the first switch S1 and the second switch S2 is controlled by the TMS control unit.

[0119] Secondly, in order to meet the dosage requirements of the superior therapy, a charging unit that meets its requirements also needs to be designed, that is, rapid charging needs to be achieved to meet the pulse timing requirements of the superior therapy.

[0120] Based on the operating characteristics of TMS pulses, a continuous charging / discharging state is required for the high-voltage energy storage capacitor. In this embodiment, a half-bridge quasi-resonant topology circuit is used for charging. It should be noted that the selection of the topology circuit needs careful consideration; conventional high-power, high-efficiency topologies are generally unsuitable for this therapy or TMS magnetic stimulation technology.

[0121] See Figure 8 The diagram shows a schematic of the drive unit 200 in a magnetic stimulation assembly according to an embodiment of the present invention. The drive unit 200 is also referred to as a discharge chamber. The drive unit 200 includes a discharge chamber housing 201, a fan 202, a coil output drive connector 205, an input power relay 207, a discharge switch module 208, a discharge chamber 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 input connector 215, a control wiring harness connector 216, a high-voltage charging power input connector 217, a control and power connector 218, and an isolation cover 220, among other components.

[0122] like Figure 8 As shown, the discharge box housing 201 is connected to the charging unit 300 via a wiring harness (e.g., ...). Figure 10 (as shown) and magnetic stimulation unit control unit 400 (as shown) Figure 11 (As shown). All components inside the discharge chamber housing 201 are mounted to the housing 201 using various fasteners (e.g., screws). A fan 202 is used to dissipate heat from the components inside the discharge chamber. The fan 202 and fan guard 203 are secured to the discharge chamber housing 201 using fasteners 204 such as long screws. The fan 202 is connected to the power input terminal 215 via a wiring harness to provide it with power.

[0123] The coil output drive connector 205 is fixed to the discharge box housing 201 by screws or other fasteners 206. It is connected to the high-voltage energy storage capacitor 213 via a negative high-voltage wire harness and to the discharge switch module 208 via a positive high-voltage wire harness.

[0124] The input power relay 207 is used to control the power supply of the charging unit 300. It is connected to the control and power connector 218 of the charging unit 300 by a wiring harness. The input power relay 207 is fixed to the housing 201 by screws.

[0125] The discharge switch module 208 is connected to the current control board 211 via a control harness, and to the coil output drive connector 205 and the high-voltage energy storage capacitor 213 via a high-voltage harness. Additionally, the invention includes a grounding busbar 209, to which all components requiring grounding are connected via harnesses.

[0126] The discharge box cover 210 and the discharge box housing 201 together form the housing of the complete drive unit 200, thus providing it with protection similar to a housing. Its shape is generally rectangular or square.

[0127] The current control board 211 is connected to the main control PCB assembly 212 via a wiring harness, and is also connected to the discharge switch module 208 via a drive wiring harness and a high-voltage signal acquisition wiring harness. The main control PCB assembly 212 is connected to the control wiring harness connector 216 via a wiring harness.

[0128] In order to insulate the high-voltage energy storage charging and discharging capacitor 213, a nut cap 214 is also provided.

[0129] The power input connector 215 accepts external power input on one hand and connects to the input power relay 207 and the main control PCB assembly 212 via a wiring harness on the other hand. The control wiring harness connector 216 connects to the main control PCB assembly 212 via a wiring harness on one hand and accepts wiring harness connections from external controllers on the other hand.

[0130] The high-voltage charging power input connector 217 is externally connected to the charging unit 300 via a wiring harness, and internally connected to the high-voltage energy storage capacitor 213 via a wiring harness.

[0131] The charging box control and power connector 218 is externally connected to the charging box via a wiring harness, and internally connected to the input power relay 207 and the main control PCB assembly 212 via a wiring harness.

[0132] Mounting screws and other fasteners 219 are used to secure the high-voltage charging power input connector 217, the charging unit control and power connector 218 to the housing 201. An isolation cover 220 is used to isolate the discharge switch module 208 from the input power relay 207, enhancing insulation. Screws 221 are used to secure the isolation cover 220 to the housing 201.

[0133] See Figure 9 The diagram illustrates a schematic of a charging unit 300 in a magnetic stimulation assembly according to an embodiment of the present invention. Addressing the requirement for rapid charging of the charging system in therapeutic applications, the present invention provides a charging unit 300 capable of achieving the pulse timing required by therapeutic applications.

[0134] Based on the pulse operating characteristics of the TMS, it is constantly charging the high-voltage energy storage capacitor 213. Therefore, conventional high-power, high-efficiency topologies are not suitable for topology selection. Thus, a half-bridge quasi-resonant topology was chosen in one embodiment.

[0135] The charging unit 300, also known as the charging box, includes: EMI circuit, rectifier circuit, (high voltage) energy storage capacitor, high power waveform generation circuit, step-up transformer, output rectification and charging circuit control board.

[0136] The charging unit 300 primarily relies on a high-power waveform generation circuit to convert the energy in the energy storage capacitor into a pulse waveform, which is then input to a step-up transformer. The low input voltage is stepped up by the transformer to obtain a high-voltage pulse, which is then rectified by the subsequent output stage to obtain a high-voltage DC output. This voltage is then used to charge the custom-designed high-voltage energy storage charging and discharging capacitor 213 in the drive unit 200. The power of this waveform generation circuit determines the charging speed of the charging unit 300.

[0137] See Figure 10 The diagram shows a schematic of the structure of a charging unit 300 according to an embodiment of the present invention. The charging unit 300 is also called a charging box, and includes components such as a charging box body 301, a charging power board heat sink 302, a cooling fan 305, a fan cover 306, an output high voltage connector 308, an input power and control connector 309, a charging box cover 310, and a charging circuit board 311.

[0138] Specifically, the charging case 301 is equipped with a structure for storing and securing the aforementioned components. The charging power board heat sink 302 is fixed to the charging case 301 using screws or other fasteners 303. Additionally, copper studs 304 are provided to secure the charging circuit board 311 to the charging power board heat sink 302, thereby dissipating heat from the charging circuit board 311. A cooling fan 305 is located at one end of the charging case 301 and is fixed to the charging case 301 together with a fan cover 306 using long screws or other fasteners 307.

[0139] The output high-voltage connector 308 is externally connected to the discharge box 200 via a high-voltage wiring harness, and internally connected to the charging circuit board 311 via a wiring harness. The input power and control connector 309 is externally connected to the discharge box 200 via a wiring harness, and internally connected to the charging circuit board 311 via a wiring harness. To form a complete enclosure, a charging box cover 310 is also provided, which is configured as a rectangular cover on the charging box body 301. In addition, an indicator light panel 312 can be provided, connected to the charging control board 11 via a wiring harness, to indicate whether charging is on.

[0140] According to another embodiment of the present invention, a magnetic stimulation device (not shown) is also provided. The magnetic stimulation device includes:

[0141] The aforementioned magnetic stimulation unit;

[0142] The acquisition module is configured to acquire electromyographic signals from the human body in real time; and

[0143] The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

[0144] Specifically, the magnetic stimulation device further includes a first communication module (not shown) and a second communication module (not shown). The first communication module is wirelessly connected to a first terminal and is configured to transmit the electromyographic signals to the terminal; the second communication module is connected to the magnetic stimulation unit and is configured to transmit a real-time synchronization signal sent by the magnetic stimulation unit to obtain the first time of the magnetic stimulation unit's output energy.

[0145] In one example, the magnetic stimulation unit can be used to induce electromyographic signals or to modulate body parts using a magnetic field.

[0146] In one example, the terminal could be a personal computer (such as a desktop, all-in-one, laptop, tablet, PDA, and ultrabook), mobile phone, digital TV, smartwatch, wearable device, and mobile smart terminal (such as a virtual computer that tracks data via a camera and projects data via an infrared laser) capable of sending commands to the acquisition module and processing data transmitted by the magnetic stimulation device.

[0147] According to another embodiment of the present invention, a magnetic stimulation device (not shown) is provided, the magnetic stimulation device comprising:

[0148] The aforementioned magnetic stimulation components;

[0149] The acquisition module is configured to acquire electromyographic signals from the human body in real time; and

[0150] The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit in the magnetic stimulation component, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

[0151] Specifically, the magnetic stimulation device further includes a first communication module (not shown) and a second communication module (not shown). The first communication module is wirelessly connected to a first terminal and is configured to transmit the electromyographic signals to the terminal; the second communication module is connected to the magnetic stimulation unit and is configured to transmit a real-time synchronization signal sent by the magnetic stimulation assembly to obtain the first time the magnetic stimulation unit in the magnetic stimulation assembly outputs energy.

[0152] In one example, the magnetic stimulation component can be used to induce electromyographic signals.

[0153] In one example, the terminal could be a personal computer (such as a desktop, all-in-one, laptop, tablet, PDA, and ultrabook), mobile phone, digital TV, smartwatch, wearable device, and mobile smart terminal (such as a virtual computer that tracks data via a camera and projects data via an infrared laser) capable of sending commands to the acquisition module and processing data transmitted by the magnetic stimulation device.

[0154] Specifically, the acquisition module can use wireless transmission technology to communicate with the wireless time synchronization module. This can solve the synchronization problem between the acquisition of MEP waveforms and TMS stimulation. The TMS also uses a wireless precision time synchronization module, whose error can be controlled at the microsecond level, making the MEP waveform acquisition time error almost negligible.

[0155] See Figure 11 The diagram illustrates a schematic structure of a magnetic stimulation device according to an embodiment of the present invention. The magnetic stimulation device includes a magnetic stimulation unit, a magnetic stimulation unit control unit 400 (e.g., a TMS control unit), a driving unit 200 (e.g., a TMS driving unit), and a charging unit 300 (e.g., a TMS charging unit).

[0156] In one embodiment, the magnetic stimulation unit includes a magnetic stimulation coil that generates an alternating magnetic field.

[0157] Specifically, the magnetic stimulation coil is an irregularly shaped coil; in one example, the magnetic stimulation coil is shaped like a figure eight or a circle.

[0158] Furthermore, the magnetic stimulation unit control unit 400 is configured to control the operation of various components within the magnetic stimulation device, including controlling the charging timing and discharge intensity, wirelessly synchronizing with the muscle acquisition unit, and communicating with the software within the magnetic stimulation device. The magnetic stimulation unit control unit 400 can be directly or via a bracket fixed to the charging unit 300 and can communicate with the various components within the magnetic stimulation device via wired or wireless communication to control them.

[0159] The drive unit 200 is connected to the magnetic stimulation unit, and its main function is to drive the magnetic stimulation unit by discharge, thereby generating an alternating magnetic field.

[0160] The main function of the charging unit 300 is to charge the driving unit 200, specifically by charging the capacitors within the charging unit.

[0161] In this embodiment, the drive unit 200 of the magnetic stimulation unit is redesigned to optimize size and heat dissipation. Additionally, a charging system for the magnetic stimulation unit needs to be designed to meet the dosage requirements of the therapeutic approach, enabling rapid charging and achieving the pulse timing requirements of the therapeutic approach.

[0162] like Figure 1 As shown, the magnetic stimulation device also includes a TMS shielding enclosure 503, which provides overall EMC shielding for the magnetic stimulation device. Specifically, the TMS shielding enclosure 503 can be made of a suitable electromagnetic shielding material, or formed by coating its inner or outer surfaces with an appropriate electromagnetic shielding material. In one example, the charging unit 300 and the driving unit 200 are housed within the TMS shielding enclosure 503.

[0163] The charging unit 300 and the drive unit 200 can be fixedly installed inside the TMS shielded enclosure 503 by fasteners 507, such as screws.

[0164] To better protect the various components inside the magnetic stimulation device, a TMS shielding outer casing cover 506 is also required, which is assembled together with the TMS shielding outer casing 503.

[0165] In one embodiment, a TMS tray assembly 501 is also provided on the bottom of the TMS shielding outer casing 503, which can provide support for the entire TMS shielding outer casing 503.

[0166] It is understood that the shape of the TMS shielding outer box 503 can be any desired shape, such as a cuboid or a cube, and correspondingly, the TMS tray assembly 501 and the TMS shielding outer box cover 506 are also set to the corresponding shapes to match it.

[0167] In one embodiment, the magnetic stimulation unit control unit 400, drive unit 200, and charging unit 300 are detachably fixed to the TMS tray assembly 501 using screws, bolts, or similar fasteners 507. Of course, other methods, such as welding, can also be used to securely fix them to the TMS tray assembly 501.

[0168] On one side of the TMS shielded enclosure 503, TMS shielded enclosure connection terminals 508 and 509 are provided for connecting external power lines and communication lines. The number of these connection terminals is not limited and can be set to two, three, or more. Those skilled in the art can make corresponding settings as needed.

[0169] exist Figure 1 In this embodiment, two charging units 300 are provided, which are connected to the drive unit 200 via wiring harnesses to complete the timing control and protection within the charging units 300. The drive unit and the control unit 200 are connected via ribbon cables for functions such as controlling the discharge energy and discharge timing control.

[0170] The magnetic stimulation unit, magnetic stimulation assembly, and magnetic stimulation device provided in the embodiments of the present invention have at least one of the following advantages:

[0171] (1) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention have optimized the outer covering structure of the magnetic stimulation coil so that the weight of the magnetic stimulation coil is minimized while meeting safety requirements. In this process, high pressure-resistant materials such as FR4 and resin are mainly used, and vacuum infusion technology is adopted to ensure that the copper tubes between adjacent magnetic stimulation coils, the surfaces between magnetic stimulation coils and other parts meet the pressure resistance requirements, thereby improving the strength of the magnetic stimulation coil body.

[0172] (2) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention have found an optimized winding pattern of the magnetic stimulation coil through three stages: theoretical calculation, computer simulation and physical verification, such as circular coil or figure-eight coil, and achieved better comprehensive performance.

[0173] (3) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopts a four-layer structure design of magnetic stimulation coil, which solves the problems of large driving current, serious cable heating and large coil weight.

[0174] (4) The magnetic stimulation unit, magnetic stimulation component, and magnetic stimulation device provided by this invention employ a half-bridge quasi-resonant topology circuit in the TMS charging unit. This ensures that the high-voltage energy storage capacitor is continuously charged according to the TMS pulse operating characteristics. Therefore, a charging system designed to meet the TMS requirements for the optimal therapeutic dose is achieved, enabling rapid charging and reaching the optimal pulse timing for the therapeutic. In current TMS charging units, the use of a half-bridge quasi-resonant topology circuit results in relatively high efficiency and stability.

[0175] (5) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention are designed with a cooling structure for the magnetic stimulation coil, for example, by using the technology of refrigerant and electrical separation, so that the refrigerant interface and the electrical interface are separated, effectively eliminating the impact on electrical safety when the refrigerant leaks.

[0176] (6) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopt a three-way connection for the refrigerant inlet of the magnetic stimulation coil, especially for the figure-eight magnetic stimulation coil, so that the copper tubes on both sides of the figure-eight can simultaneously input refrigerant, accelerate heat dissipation, and at the same time keep the temperature of the copper tubes on both sides symmetrical and balanced.

[0177] (7) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention take into account the characteristics of high voltage and large heat generation when the magnetic stimulation coil performs magnetic stimulation. They adopt a semiconductor cooling mode. When necessary, a cooling mode of semiconductor cooling plus air cooling can also be adopted to achieve better heat dissipation effect and at the same time achieve the requirement of low noise.

[0178] (8) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention use highly insulating silicone oil and the like as cooling refrigerant to ensure the safety of the discharge process.

[0179] (9) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention adopt a pumping device, storage tank, cold air radiator, refrigerant pipe and quick connector to form a refrigerant circulation loop to realize heat conduction to the magnetic stimulation coil and the corresponding cooling part.

[0180] (10) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention can perform real-time temperature monitoring and real-time intelligent control of the cooling of the magnetic stimulation coil by configuring a temperature sensor and a control board.

[0181] (11) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention use a button that integrates indicator light and switch, which saves space;

[0182] (12) The magnetic stimulation unit, magnetic stimulation component and magnetic stimulation device provided by the present invention solve the problem of synchronization between the acquisition of motor evoked potential (MEP) waveform and TMS stimulation through the designed wireless time synchronization module. The TMS also adopts a wireless precision time synchronization unit, whose error can be controlled at the microsecond level, so that the MEP waveform acquisition time error can be almost ignored.

[0183] While some embodiments of the present general inventive concept have been shown and described, those skilled in the art will understand that changes may be made to these embodiments without departing from the principles and spirit of the present general inventive concept, the scope of which is defined by the claims and their equivalents.

Claims

1. A magnetic stimulation unit, characterized in that, The magnetic stimulation unit includes: The magnetic stimulation coil is made of a hollow conductor wound into a predetermined pattern, the tube wall of the hollow conductor is configured as an energized circuit, and the hollow cavity of the hollow conductor is filled with insulating refrigerant. An insulating shell is formed by vacuum-filling high-voltage resistant material between adjacent portions of the hollow conductor, and the shape of the insulating shell is consistent with the shape of the magnetic stimulation coil. The magnetic stimulation coil is a four-layer structure formed by repeatedly winding a hollow conductor in a predetermined pattern from the outside to the inside, and then winding it in the predetermined pattern from the inside to the center.

2. The magnetic stimulation unit according to claim 1, characterized in that, The insulating coolant includes silicone oil; the insulating shell is 1-5 mm above the upper or lower surface of the magnetic stimulation coil.

3. The magnetic stimulation unit according to claim 1, characterized in that, The hollow conductor of the magnetic stimulation coil has two ends. After passing through the extension joint, refrigerant interface and parallel connection block, the refrigerant inlet pipe and refrigerant outlet pipe are respectively connected to the two ends to form a refrigerant circuit; The two power lines pass through an extension connector, an electrical interface, and a parallel connector before being electrically connected to their respective ends to form an electrical circuit. The extended connector leads the two power lines, the refrigerant inlet pipe, and the refrigerant outlet pipe out of the insulating shell.

4. The magnetic stimulation unit according to claim 1, characterized in that, The magnetic stimulation coil is a figure-eight shaped coil divided into a left and a right section, each of which has two ends. The refrigerant inlet pipe and refrigerant outlet pipe, after passing through an extension connector and a tee connector, become two refrigerant inlet branch pipes and two refrigerant outlet branch pipes. The two refrigerant inlet branch pipes, after passing through a refrigerant interface and a parallel connecting block, are respectively connected to one end of the magnetic stimulation coil in the left and right sections. Correspondingly, the two refrigerant outlet branch pipes, after passing through a refrigerant interface and a parallel connecting block, are respectively connected to the other end of the magnetic stimulation coil in the left and right sections to form a refrigerant circuit. Two power lines, after passing through an extension connector, insulating conduit, electrical interface, and electrical connection block, connect one power line to one end of the magnetic stimulation coil in the left and right sections respectively. Correspondingly, the other power line connects to the other end of the magnetic stimulation coil in the left and right sections respectively to form an electrical circuit. The extended connector leads the two power lines, the refrigerant inlet pipe, and the refrigerant outlet pipe out of the insulating shell.

5. The magnetic stimulation unit according to claim 4, characterized in that, The left and right parts of the figure-eight coil are circular coils. The circular coil is a four-layer structure formed by repeatedly winding a copper tube in a circular pattern from the outside to the inside, and then winding it in a circular pattern from the inside to the outside at the center. The circular coils in the left and right parts are mirror-symmetrical and connected in series. Positioning protrusions are provided on the insulating shell.

6. The magnetic stimulation unit according to claim 1 or 5, characterized in that, The four-layer structure, from bottom to top, includes a first regulating inductor layer, a second regulating inductor layer, a third magnetic field layer, and a fourth magnetic field layer. The number of turns of the first and second regulating inductor layers is set to 2 to 3, and the number of turns of the third and fourth magnetic field layers is set to 3 to 4.

7. The magnetic stimulation unit according to claim 6, characterized in that, The diameter range of the circular coils in the left and right portions of the figure-eight coils is set to 3.8–7.2 cm.

8. The magnetic stimulation unit according to claim 3 or 4, characterized in that, The refrigerant inlet pipe, refrigerant outlet pipe, and power cord are encased in an insulated conduit that extends from the parallel connector block to the extension joint.

9. A magnetic stimulation component, characterized in that, The magnetic stimulation component includes: A magnetic stimulation unit, wherein the magnetic stimulation unit is the magnetic stimulation unit according to any one of claims 1-8; A driving unit configured to drive the magnetic stimulation unit to generate an alternating magnetic field; A charging unit, configured as a magnetic stimulation unit for charging.

10. The magnetic stimulation assembly according to claim 9, characterized in that, The magnetic stimulation component is also provided with a control unit for controlling the magnetic stimulation component; The drive unit includes a DC power supply, a first switch, a second switch, a high-voltage energy storage charging and discharging capacitor, and a controller. The DC power supply, the first switch, the second switch, and the magnetic stimulation unit are connected in sequence by wires. The high-voltage energy storage charging and discharging capacitor is connected between the first switch and the second switch. The control timing of the controller to open and close the first switch and the second switch is a pulse waveform.

11. The magnetic stimulation assembly according to claim 10, characterized in that, The charging unit also includes a half-bridge quasi-resonant topology circuit for charging the high-voltage energy storage charging and discharging capacitor. The control unit also includes a wireless precision time synchronization unit that uses wireless transmission technology for muscle data acquisition.

12. The magnetic stimulation assembly according to claim 11, characterized in that, The drive unit and the charging unit are connected by a wiring harness, and the drive unit and the control unit are connected by a ribbon cable. The control unit is fixed to one end of the charging unit and is electrically connected to the charging unit.

13. The magnetic stimulation assembly according to any one of claims 9-12, characterized in that, The magnetic stimulation component further includes a cooling unit for actively cooling the magnetic stimulation unit, wherein the cooling unit is a semiconductor cooling system employing semiconductor refrigeration technology.

14. The magnetic stimulation assembly according to claim 13, characterized in that, The cooling unit includes: A storage tank containing refrigerant; A cooling module that uses semiconductor refrigeration technology for refrigerant heat exchange; A pumping device, wherein the pumping device draws refrigerant into the pumping device through a refrigerant pipeline and pumps the refrigerant to the cooling module; The refrigerant cooled by the cooling module enters the magnetic stimulation coil through the refrigerant pipe, cools the magnetic stimulation coil, and then flows back to the storage tank.

15. The magnetic stimulation assembly according to claim 14, characterized in that, The cooling unit also includes: A control board for controlling the cooling module, wherein the control board reads the temperature of the refrigerant in real time through a sensor installed on the refrigerant pipe at the outlet of the cooling module; The power supply is electrically connected in sequence to the controller of the pumping device, the pumping device, and the control board; At least two quick-connect connectors connect the magnetic stimulation coil to the cooling unit.

16. The magnetic stimulation assembly according to claim 15, characterized in that, The cooling unit includes an electromagnetic shielding box shell. The cooling module is located at one end inside the electromagnetic shielding box shell. The refrigerant pipe connected to the cooling module is connected to a corresponding interface on the electromagnetic shielding box shell through at least two quick-connect interfaces. The pumping device, power supply, and storage tank are placed inside the electromagnetic shielding box shell. The refrigerant pipe connected to the storage tank is connected to another corresponding interface on the electromagnetic shielding box shell through at least two quick-connect interfaces.

17. The magnetic stimulation assembly according to claim 16, characterized in that, The cooling module includes a radiator, a thermoelectric cooler, and a heat sink. The cold side of the thermoelectric cooler is attached to the radiator, and the hot side of the thermoelectric cooler is attached to the heat sink. The cooling module also includes Thermal interface material located between the cold side and the radiator and between the hot side and the heat sink; The fan is located near the heatsink on the cooling module.

18. A magnetic stimulation device, characterized in that, The magnetic stimulation device includes: A magnetic stimulation unit, wherein the magnetic stimulation unit is the magnetic stimulation unit according to any one of claims 1-8; Acquisition module, configured to acquire electromyographic signals of the human body in real time; and The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

19. A magnetic stimulation device, characterized in that, The magnetic stimulation device includes: A magnetic stimulation assembly, wherein the magnetic stimulation assembly is the magnetic stimulation assembly according to any one of claims 9-17; The acquisition module is configured to acquire electromyographic signals from the human body in real time; and The wireless time synchronization module is used to acquire the first time of the magnetic field output by the magnetic stimulation unit in the magnetic stimulation component, add the first time to the electromyographic signal to be transmitted, and then transmit the electromyographic signal with the first time to the terminal for processing.

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