A magnetic stimulation system for heart failure therapy

Abstract

The application discloses a magnetic stimulation system for heart failure treatment, comprising: a trans-cervical magnetic stimulation component and a control circuit; the trans-cervical magnetic stimulation component comprises a non-closed magnetic core and one or more induction coils, which are used to generate an alternating pulse magnetic field in connection with the control circuit; and the control circuit is used to provide electric energy for the whole system and generate an alternating pulse magnetic field in combination with the trans-cervical magnetic stimulation component. The application optimizes the design of the existing short board of the cervical nerve magnetic stimulation device, adds a magnetic core to reduce the magnetic resistance of the non-treatment area, improves the magnetic field stimulation intensity under the same energy consumption, further optimizes the magnetic circuit by matching multiple coils, enhances the penetration depth and uniformity of the magnetic field, and relaxes the positioning accuracy requirement of the lesion. The overall energy utilization rate is higher, the production threshold of the equipment is lower, the operation is more simple, the treatment magnetic field effect is more stable, different nerve stimulation treatments of the neck are adapted, and the applicability is significantly improved.

Description

Technical Field

[0001] This invention belongs to the field of medical devices and electromagnetic therapy technology, and specifically relates to a magnetic stimulation system for the treatment of heart failure. Background Technology

[0002] Heart failure is a common end-stage outcome of various cardiovascular diseases. Current treatment options include medication, implantable cardiac pacing and resynchronization therapy, left ventricular assist devices, and heart transplantation. However, these methods have drawbacks such as high invasiveness, high cost, poor long-term adherence, and limited indications.

[0003] In recent years, electromagnetic field therapy and neuromodulation technology have developed rapidly. Techniques such as transcranial magnetic stimulation (TMS) have been applied in psychiatry and neurology to induce currents in tissues through pulsed magnetic fields, thereby achieving functional regulation of nerves, muscles or other tissues.

[0004] Drawing on the therapeutic mechanism of transcranial magnetic stimulation (TMS), cervical vagus nerve magnetic stimulation (mVNS) also shows good therapeutic effects in treating heart failure. Sympathetic overactivity and significantly decreased vagal tone (autonomic imbalance) drive myocardial remodeling, increased myocardial oxygen consumption, inflammation activation, and malignant arrhythmias through continuous neuroendocrine activation. Magnetic stimulation, through non-invasive targeted regulation of these two types of nerves, reverses the imbalance and achieves heart failure protection. Magnetic stimulation is divided into two main directions: vagal nerve excitation magnetic stimulation and sympathetic nerve inhibition magnetic stimulation. Targeting these two types of nerves can effectively treat heart failure symptoms.

[0005] However, magnetic stimulation devices for the treatment of heart failure are still in the exploratory stage, and existing coil and magnetic circuit structures for medical magnetic stimulation mainly have the following problems:

[0006] Low magnetic circuit utilization: Traditional "hollow coils" or simple magnetic conductive structures suffer from severe magnetic field dissipation in non-therapeutic pathways (i.e., spatial regions where no induced electric field needs to be applied to the target tissue), resulting in high magnetic circuit resistance. Consequently, the effective magnetic field strength that can act on the heart or related neural structures per unit input energy is insufficient, and the penetration depth is limited.

[0007] High coil voltage stress and high insulation requirements: In order to obtain sufficient magnetic field strength, the driving circuit usually needs to apply a high pulse voltage across the two ends of a single coil, and there may be a large potential difference between different coils; at the same time, the compact spatial arrangement between coils leads to strict requirements on the insulation distance and insulation material between coils, which increases the system size, cost and breakdown risk.

[0008] Insufficient granularity of system control: Some devices use simple fixed-parameter stimulation modes and lack stimulation parameter optimization and safety monitoring software systems tailored to individual differences in heart failure patients, making it difficult to achieve precise, traceable, and multimodal treatment.

[0009] Therefore, it is necessary to provide a magnetic stimulation device and its control system with higher magnetic circuit utilization, lower voltage difference between coils, and easy fine control for the treatment of heart failure.

[0010] Currently, research on this technology is in its early stages, and there are many problems that need to be solved, mainly the following:

[0011] 1. The magnetic field of a conventional circular / figure-eight coil diffuses in an umbrella-like pattern, penetrating longitudinally and diverging laterally uncontrollably.

[0012] 2. If deep vagal stimulation is required, excessive magnetic stimulation is needed for the superficial skin and muscles, which carries risks such as soreness and headache.

[0013] 3. It is impossible to achieve synchronous and differentiated stimulation of vagal excitation and sympathetic inhibition at two targets: vagal frequency is preferred at 6-10 Hz and sympathetic frequency is preferred at 1-5 Hz. A single coil can only output one set of frequencies at the same time, and existing equipment cannot perform zone frequency conversion.

[0014] 4. If a strong magnetic field is required for deep stimulation, a larger inductance is needed, which in turn generates a stronger induced voltage. Insulation issues with the equipment may pose treatment risks. Summary of the Invention

[0015] The purpose of this invention is to address the deficiencies of the prior art by providing a magnetic stimulation device for the modulation of myocardium or cardiac-related nerves in patients with heart failure, particularly relating to the magnetic circuit structure, circuit system, software system, and corresponding control and operation methods of the device.

[0016] To achieve the above objectives, the present invention adopts the following technical solution: a magnetic stimulation system for the treatment of heart failure, comprising: a transcervical magnetic stimulation component and a control circuit;

[0017] The transcervical magnetic stimulation component includes a non-closed-loop magnetic core and one or more induction coils for connection with a control circuit to generate an alternating pulsed magnetic field.

[0018] The control circuit is used to provide electrical power to the entire system and, in conjunction with the transcervical magnetic stimulation component, generate an alternating pulsed magnetic field.

[0019] Furthermore, the induction coil uses flat wires, which are wound in layers, with each coil having 3 to 100 turns.

[0020] Furthermore, when there are more than two induction coils, the terminals of the induction coils with the same name are connected in parallel.

[0021] Furthermore, the control circuit includes:

[0022] The isolated power frequency conversion module is used to achieve electrical isolation between strong and weak currents. It converts the 220V AC power frequency into isolated AC power, which is then output in two ways. One way is rectified to output DC voltage, which is then fed into a high-voltage power supply for secondary voltage boosting. The other way is sent to the AC-DC auxiliary power supply module, where it is isolated and converted into low-voltage DC for power supply.

[0023] The ACDC auxiliary power supply module is used to provide working power to the control system of the control circuit.

[0024] The high-voltage power supply, including a high-voltage step-up transformer and a rectifier circuit, is used to receive drive commands from the control system to achieve PWM frequency modulation / amplitude modulation boost, and then the subsequent stage rectifies it into a smooth high-voltage DC to charge the capacitor energy storage array.

[0025] A control system is used to collect information in real time and output control signals based on the signals.

[0026] The capacitor energy storage array includes several parallel capacitors, which are used to change the total capacitance C by switching different capacitors according to the control signal, thereby generating different resonant frequencies. It forms an LC series resonant circuit with the induction coil of the neck magnetic stimulation component, generating a magnetic field of approximately uniform intensity at the opening of the magnetic core.

[0027] Furthermore, the capacitor energy storage array includes 2 to 200 parallel capacitors.

[0028] Furthermore, the control system includes an MCU main control system, high-voltage control, and resonance monitoring;

[0029] The MCU main control system is used to send control signals to the high-voltage power supply through high-voltage control based on the monitoring information collected in real time by the resonance monitoring.

[0030] Furthermore, the monitoring information includes temperature, number of pulses, voltage, and base frequency.

[0031] Furthermore, the control signals include the high-voltage output amplitude and the fundamental frequency selection.

[0032] Furthermore, non-closed-loop magnetic cores are rectangular, circular, or racetrack-shaped magnetic cores with a certain opening.

[0033] Advantages of this invention:

[0034] 1. Use a non-closed magnetic core to guide the magnetic field and increase the magnetic induction intensity of the treatment area (mandatory feature): The magnetic core relies on high relative permeability to gather magnetic flux and reduce magnetic circuit resistance, while increasing coil inductance and optimizing LC resonant discharge current, thus doubly improving the effective magnetic induction intensity of the working surface.

[0035] 2. Using multiple coil terminals connected in parallel reduces the voltage across the coil, increases the magnetic flux density, and lowers the insulation requirements (mandatory feature): Connecting coil terminals in parallel does not change the inductance, and the voltage across the parallel section is consistent. The risk of insulation breakdown between coils is relatively small, and the inductance is not changed and the resonant frequency is not affected.

[0036] 3. By switching the resonant capacitor, the magnetic field output frequency can be changed and frequency compensation can be performed (mandatory feature): Most devices on the market can only output one type of magnetic pulse. By switching the capacitor, different nerves can be stimulated, achieving the purpose of one machine serving multiple purposes.

[0037] 4. Features magnetic pulse output monitoring function, forming a closed loop between control and output (mandatory feature): Frequency deviation can affect treatment effect. Compared with other products, the control circuit can accurately feed back the signal frequency, automatically adjust the output frequency, ensure frequency stability, and achieve better treatment effect.

[0038] 5. Wide range of adjustable output parameters (optional feature): such as Figure 6 The magnetic pulse frequency is ≤500µs and the number of repetitions is ≤100Hz.

[0039] 6. By increasing the magnetic core, the magnetic resistance of non-treatment areas is reduced, thereby achieving a higher magnetic field stimulation intensity with the same energy.

[0040] 7. Connecting multiple coil terminals in parallel reduces the induced voltage in the coils, thereby lowering the insulation requirements of the equipment;

[0041] 8. By using parallel coils at both ends and a magnetic core to reduce magnetic resistance, the penetration and uniformity of the magnetic field are increased, thereby reducing the therapeutic impact on the target area.

[0042] Precision requirements;

[0043] 9. The output frequency of the magnetic pulse is stabilized through a pulse monitoring circuit;

[0044] 10. The fundamental frequency pulse of the magnetic stimulation can be automatically adjusted by switching the switch. Attached Figure Description

[0045] Figure 1 This is a schematic diagram of the structure of the transcervical magnetic stimulation system in an embodiment.

[0046] Figure 2 This is a system framework diagram of the control circuit in an embodiment.

[0047] Figure 3 This is a schematic diagram of the magnetic field distribution of the neck magnetic stimulation component in the embodiment.

[0048] Figure 4 This is a schematic diagram of a magnetic stimulation system treatment embodiment.

[0049] Figure 5 This is a schematic diagram of the coil connection of the neck magnetic stimulation component in the embodiment.

[0050] Figure 6 This is a schematic diagram of the magnetic pulse output control in an embodiment.

[0051] Figure 7 This is the magnetic pulse output sequence of the embodiment.

[0052] Figure 8 This is a software flowchart of an example implementation. Detailed Implementation

[0053] To enable those skilled in the art to better understand the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present application, and not all embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative effort should fall within the scope of protection of the present application.

[0054] It should be noted that the terms "comprising" and "having" and any variations thereof in the specification, claims and accompanying drawings of this application are intended to cover non-exclusive inclusion. For example, a process, method, system, product or device that includes a series of steps or units is not necessarily limited to those steps or units that are explicitly listed, but may include other steps or units that are not explicitly listed or that are inherent to such process, method, product or device.

[0055] like Figure 1 The transcervical magnetic stimulation system shown includes: a transcervical magnetic stimulation component and control circuitry in the device.

[0056] The entire control circuit is divided into 5 major functional sub-modules: a mains frequency input AC-AC isolation converter and AC-CDC auxiliary power supply module, a boost high-voltage power supply module, an LC resonant pulse output module, a multi-parameter sampling and monitoring module, and an MCU main control closed-loop control system (such as...). Figure 2 (As shown).

[0057] (1) ACAC isolated power frequency conversion

[0058] Input: AC220V L / N mains power. The power frequency isolation transformer completes the electrical isolation between strong and weak currents. Isolation is a mandatory safety requirement for medical equipment to prevent leakage current from the stimulation coil from endangering the human body.

[0059] ① Isolate the high-voltage power grid from the downstream stimulation load to meet the insulation requirements of Class II medical devices;

[0060] ② Convert the 220V AC power frequency to a suitable amplitude low-voltage AC, and output it in two ways: one way goes to the rectifier bridge, and the output DC voltage is sent to the subsequent "high voltage power supply module" for secondary boosting; the other way goes to the "ACDC" power supply module, which isolates and converts it into the whole machine's low-voltage DC (±5V / ±12V / 24V) to power the MCU main control, sampling circuit, high voltage drive chip and resonance monitoring circuit.

[0061] (2) ACDC auxiliary power supply module (weak current energy source for the whole machine)

[0062] Derived from the ACAC isolated secondary winding, this independently isolated AC-DC switching power supply outputs multiple regulated DC power supplies: providing operating power to the MCU main control chip, resonant monitoring circuit, various sampling operational amplifiers, and high-voltage control drive circuits; and electrically isolating from the main power link to avoid interference from main power high-voltage pulses to the main control digital circuit, and to prevent EMI interference from magnetic field pulses that cause main control sampling distortion, which is the foundation of overall system stability.

[0063] (3) High voltage power supply and subsequent rectifier module (core of power boosting of the whole machine)

[0064] The high-voltage power supply includes a high-frequency inverter and a step-up transformer. It receives MCU drive commands from the "high-voltage control module" below to achieve PWM frequency modulation / amplitude modulation boost. The subsequent rectification stage rectifies the high-voltage AC into smooth high-voltage DC to charge the selected C01 / C02 / C03 capacitor energy storage array on the right. The output voltage of the high-voltage power supply is regulated by the MCU through a high-voltage control closed loop. The MCU collects voltage sampling data from the load end, fine-tunes the high-voltage output amplitude in real time, accurately controls the energy stored in the capacitors, and ultimately controls the coil magnetic field strength (corresponding to the nerve stimulation dose, a key parameter in heart failure treatment).

[0065] (4) Capacitor array of C01 / C02 / C03 and L0 stimulation coil (LC resonant output stage, magnetic field generation terminal)

[0066] This is the magnetic stimulation output load, which is directly applied to the skin of the neck to generate an alternating pulsed magnetic field, targeting the vagus / sympathetic nerves. Capacitor groups C01 / C02 / C03 consist of multiple capacitors connected in parallel or selectively switched, forming an energy storage capacitor array. A high-voltage rectified output charges the capacitors, storing electric field energy. At the moment the controlled switch (the controllable thyristor in the diagram) is turned on, the capacitor array and the stimulation coil L0 form an LC series resonant circuit. Switching the number of capacitors in operation changes the total capacitance C, and in conjunction with the L0 inductor, fine-tunes the inherent resonant frequency of the LC circuit, adapting it to the therapeutic fundamental frequency required for heart failure.

[0067] Stimulation coil L0: Neck surface magnetic stimulation coil. At the moment of LC resonant discharge, a transient pulsed large current flows through the coil → According to the law of electromagnetic induction, an alternating pulsed magnetic field is generated in the coil space, which penetrates the skin and subcutaneous tissue to non-invasively excite / inhibit the vagus and sympathetic nerves in the neck (autonomic nerve regulation target point for heart failure).

[0068] Circuit switch: The controllable power device (SCR / IGBT) is turned on and off by the MCU timing control. The switching frequency is equal to the treatment base frequency. The MCU "base frequency selection" port sends frequency instructions to determine the number of resonant discharges per second, which is the magnetic stimulation pulse frequency.

[0069] (5) Multi-channel monitoring and sampling + MCU main control system (the closed-loop control center of the whole machine, the "brain" of the whole machine)

[0070] The MCU receives four key sampling signals and simultaneously outputs two control signals (high voltage control and base frequency selection), forming a fully closed-loop adaptive control system that perfectly matches the individualized frequency conversion treatment needs of heart failure.

[0071] Pulse count sampling (output of the resonance monitoring module) counts the actual number of LC resonant discharge pulses, compares them with the set base frequency issued by the MCU, corrects the switching timing, and avoids frequency drift; Temperature monitoring (coil / power device temperature measurement) collects the temperature of the stimulation coil L0 and the high-voltage power device. Heart failure treatment involves long-term periodic stimulation. When the coil continues to overheat, the MCU reduces the high-voltage output, reduces the stimulation frequency, or even shuts down for protection to avoid scalding the patient and overheating damage to the equipment.

[0072] like Figure 3 The diagram showing the magnetic field distribution, combined with... Figure 1 The treatment site is at the gap between the magnetic cores. Ordinary magnetic field stimulation coils use air as the medium, resulting in a very long magnetic circuit and high magnetic resistance, so the effective treatment energy is not concentrated in the treatment area.

[0073] According to the total current law:

[0074] Formula (1)

[0075] Formula (2)

[0076] The magnetic core (μe = 500~5000) has a relatively high permeability, while the permeability of air is very small, approximately equal to the permeability of vacuum, which is 4π × 10⁻⁻. 7 According to formula (2), it can be seen that the overall magnetic circuit length and the magnetic circuit length in the air can be effectively reduced, which can greatly improve the magnetic induction intensity of the treatment area.

[0077] Under the conditions of fixed coil turns and discharge voltage, the magnetic core relies on high relative permeability to gather magnetic flux and reduce magnetic circuit reluctance. According to B=μe*μc*H, the magnetic induction intensity increases proportionally with μe. At the same time, the coil inductance is increased and the LC resonant discharge current is optimized, thus doubly improving the effective magnetic induction intensity of the working surface.

[0078] Increase the magnetic field strength by connecting the same-named terminals of the coil in parallel.

[0079] (1) Working process (in conjunction with the whole machine LC resonant magnetic stimulation circuit)

[0080] Capacitor pre-charge stage: The MCU controls the high-voltage power supply to charge the selected energy storage capacitors C01 / C02 / C03 with high voltage through the AB parallel coil;

[0081] Resonant discharge stage: The MCU turns on the power switch according to the set treatment frequency, A1 and B1 are shorted, A2 and B2 are shorted (the same terminals are connected in parallel), the capacitor, the double coil and the magnetic core form an LC resonant circuit, and the capacitor releases a pulsed large current to the parallel coil instantaneously;

[0082] Magnetic field output: The current in the two coils generates magnetic flux in the same direction on the same magnetic core. The magnetic flux is superimposed, the magnetic core gathers the magnetic lines of force, and a high-intensity pulsed alternating magnetic field is generated on the end face of the coil, which penetrates the skin of the neck to stimulate the vagus / sympathetic nerves.

[0083] Intermittent cycle: After a single resonant discharge, the system enters an intermittent rest period, during which the capacitor is recharged, and the next round of stimulation is repeated.

[0084] (2) Main working principle

[0085] ① Electrical principle: Parallel connection of terminals with the same name to share the voltage reduces the insulation withstand voltage of the coil.

[0086] like Figure 5 The two coils have the same number of turns and winding direction. The outer terminals of A1 and B1 are at the same potential, and the inner terminals of A2 and B2 are at the same potential. The total capacitor voltage is shared by the two coils A and B. The voltage borne by a single coil is only 1 / 2 of the total voltage. The insulation withstand voltage requirements between turns and between layers are directly halved. The planar wound coil does not need to be thickened with insulation layer, which reduces the coil volume and reduces the difficulty of winding process. The potential at the same end is equal, and there is no high voltage potential difference between windings, eliminating the risk of interlayer breakdown and short circuit.

[0087] ② Magnetic circuit principle: Superposition of magnetic flux in the same direction increases the magnetic induction intensity.

[0088] After parallel connection, the current flows in the same direction in the two coils, generating alternating magnetic flux in the same direction in the shared magnetic core, with a total magnetic flux Φ=ΦA+ΦB; since B=SΦ, and the cross-sectional area S of the magnetic core is fixed, the superposition of the total magnetic flux significantly increases the magnetic induction intensity B on the working surface; the magnetic field is stronger under the same energy storage voltage, and deep nerve stimulation can be satisfied without increasing the high voltage of the equipment, thus optimizing the overall power supply design.

[0089] ③ Resonant inductor principle: Tightly coupled parallel connection, total inductance ≈ single coil inductance:

[0090] like Figure 4 and 5 With the magnetic core tightly coupled, the single coil inductance is L0, the mutual inductance is M≈L0, and the equivalent inductance of the same terminals in parallel is: Leq=2L0+M=L0. From formula (3), we know that after parallel connection, the equivalent inductance and the single coil inductance remain basically unchanged, and the LC resonant frequency is f= The resonant frequency can be finely adjusted simply by switching C01 / C02 / C03 capacitors, making it suitable for precise frequency conversion in heart failure. At the same time, the cross-sectional area of ​​the dual-line parallel conductor is doubled, and the coil can withstand a larger peak current, further improving the upper limit of the magnetic field strength.

[0091] Formula (3)

[0092] Through pulse monitoring circuitry, base frequency control, and output;

[0093] like Figure 6 This circuit is the main LC pulse power circuit for a cervical magnetic stimulation device for heart failure. It utilizes a unidirectional silicon controlled rectifier (SCR) and the LC resonance principle to achieve programmable pulse magnetic field output. The circuit consists of four main operating stages: pre-charging, resonant discharge, device shutdown, and sampling feedback. On the left side, a rectifier bridge BD1 performs power frequency rectification and filtering. A resistor divider network and an LM393 voltage comparator form a high-voltage sampling unit, which collects the bus voltage in real time and compares it with a reference voltage to provide voltage monitoring signals for the control system. The middle T4 is a common-mode inductor that pre-charges the CO1, CO2, and CO3 multi-channel energy storage capacitor arrays through a current-limiting resistor, completing the electric field energy storage. These multiple capacitors can be switched on and off as needed, adjusting the LC resonant frequency in conjunction with coil L1 to adapt to and switch the clinical treatment frequency band.

[0094] When the main control system sends a trigger signal according to the set stimulation frequency, the SCR (Silicon Controlled Rectifier) ​​turns on. The energy storage capacitor and the magnetic core coil L1 form an LC resonant circuit. A large pulse current flows through the coil instantaneously. Relying on the magnetic core's focusing magnetism and the superposition effect of the magnetic flux of the two coils, an alternating pulse magnetic field is generated, which is applied to the vagus and sympathetic nerves in the neck. After half a cycle of LC resonance, the circuit current reverses. Due to the unidirectional conduction characteristic of the SCR, the reverse current cannot flow, the SCR turns off automatically, and the single resonant discharge terminates.

[0095] The end of resonance triggers a sudden change in bus voltage, causing the voltage divider signal to trigger a level flip of the LM393, feeding back a single pulse completion signal to the main controller. The control system completes pulse counting, verifies the actual output frequency, and then enters an intermittent waiting phase, during which the capacitor is recharged. Figure 7 It continuously outputs standardized treatment pulses in a cyclical manner.

[0096] Implementation using process management software

[0097] like Figure 8 After the device is powered on, the MCU completes hardware initialization, reads the stored historical treatment parameters and performs a full-circuit hardware self-test. If the self-test fails, the high voltage is cut off and the alarm is triggered to stop the machine. If the self-test is successful, the human-machine interface is entered, where the vagal, sympathetic or combined alternating treatment modes can be selected as needed for stimulation. The system automatically loads the corresponding frequency and energy storage voltage parameters.

[0098] After parameter configuration, the high-voltage pre-charge closed loop is initiated. The MCU, relying on voltage sampling, adjusts the high-voltage output in real time to stabilize the energy storage capacitor voltage at the set value. Once the voltage reaches the target, the matching capacitor array is switched based on resonance sampling to calibrate the LC resonance parameters. The main controller triggers the thyristor to conduct at a set frequency, causing the LC circuit to resonate and discharge, and the coil outputs a pulsed magnetic field. Simultaneously, four data points are collected: temperature, resonance waveform, and pulse count. In case of over-temperature or coil malfunction, the high-voltage protection is immediately shut off. If no malfunction occurs, the measured frequency is compared with the set value, and the resonance parameters are corrected as needed. After a single stimulation, an intermittent delay occurs. If the treatment course is not yet finished, cyclic stimulation continues. After treatment, the residual voltage of the capacitor is discharged, and the entire machine enters standby mode.

[0099] In summary, the above description is merely a preferred embodiment of the present invention and is not intended to limit the invention. Various modifications and variations can be made to the present invention by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

Claims

1. A magnetic stimulation system for the treatment of heart failure, characterized in that... include: Neck magnetic stimulation component and control circuit; The transcervical magnetic stimulation component includes a non-closed-loop magnetic core and one or more induction coils for connection with a control circuit to generate an alternating pulsed magnetic field. The control circuit is used to provide electrical power to the entire system and, in conjunction with the transcervical magnetic stimulation component, generate an alternating pulsed magnetic field.

2. The magnetic stimulation system for treating heart failure according to claim 1, characterized in that: The induction coil is made of flat wire, which is wound in layers, with each coil having 3 to 100 turns.

3. The magnetic stimulation system for treating heart failure according to claim 1, characterized in that: When there are two or more induction coils, the terminals of the induction coils with the same name are connected in parallel.

4. The magnetic stimulation system for treating heart failure according to claim 1, characterized in that: The control circuit includes: The isolated power frequency conversion module is used to achieve electrical isolation between strong and weak currents. It converts the 220V AC power frequency into isolated AC power, which is then output in two ways. One way is rectified to output DC voltage, which is then fed into a high-voltage power supply for secondary voltage boosting. The other way is sent to the AC-DC auxiliary power supply module, where it is isolated and converted into low-voltage DC for power supply. The ACDC auxiliary power supply module is used to provide working power to the control system of the control circuit. The high-voltage power supply, including a high-voltage step-up transformer and a rectifier circuit, is used to receive drive commands from the control system to achieve PWM frequency modulation / amplitude modulation boost, and then the subsequent stage rectifies it into a smooth high-voltage DC to charge the capacitor energy storage array. A control system is used to collect information in real time and output control signals based on the signals. The capacitor energy storage array includes several parallel capacitors, which are used to change the total capacitance C by switching different capacitors according to the control signal, thereby generating different resonant frequencies. It forms an LC series resonant circuit with the induction coil of the neck magnetic stimulation component, generating a magnetic field of approximately uniform intensity at the opening of the magnetic core.

5. The magnetic stimulation system for treating heart failure according to claim 4, characterized in that: The capacitor energy storage array includes 2 to 200 parallel capacitors.

6. The magnetic stimulation system for treating heart failure according to claim 4, characterized in that: The control system includes an MCU main control system, high voltage control, and resonance monitoring; The MCU main control system is used to send control signals to the high-voltage power supply through high-voltage control based on the monitoring information collected in real time by the resonance monitoring.

7. The magnetic stimulation system for treating heart failure according to claim 6, characterized in that: The monitoring information includes temperature, number of pulses, voltage, and base frequency.

8. The magnetic stimulation system for treating heart failure according to claim 6, characterized in that: The control signals include high voltage output amplitude and base frequency selection.

9. The magnetic stimulation system for treating heart failure according to claim 1, characterized in that: The non-closed-loop magnetic core is a rectangular, circular, or racetrack-shaped magnetic core with a certain opening.

Images