Wireless transcutaneous transmission system

Abstract

The application provides a wireless transcutaneous transmission system, comprising a transmitting unit and a receiving unit, the transmitting unit comprising a control unit and a primary transmitting coil, a magnetic field sensor is arranged at the center position of the primary transmitting coil, the magnetic field sensor is configured to detect the magnetic field strength generated by a magnet and output a voltage detection signal; the control unit is configured to determine a current frequency parameter based on the voltage detection signal and output a first control signal to control the primary transmitting coil based on the current frequency parameter; the receiving unit comprises a secondary receiving coil and a load, the secondary receiving coil comprises a magnet, and the secondary receiving coil is configured to generate a power supply signal based on the magnetic field strength to supply power to the load. The wireless transcutaneous transmission system of the application does not need to set a feedback circuit on the implantation side, avoids additional power consumption, reduces the power consumption of the system, and can dynamically adjust the frequency according to the voltage, so that the system is automatically maintained in an optimal or nearly optimal resonant transmission state.

Description

Technical Field

[0001] This application relates to the field of wireless power transfer technology, and more particularly to a wireless transdermal power transfer system. Background Technology

[0002] Patients with end-stage heart failure typically require ventricular assist devices or total artificial hearts to sustain life. Currently, most of these devices connect to an external power source via percutaneous leads that pass through the skin. Because the leads need to pass through the skin, they are prone to infection, blood clots, and device malfunction.

[0003] An existing wireless transdermal power transfer system can solve this problem. The wireless transdermal power transfer system is achieved through coil coupling and does not require transdermal wires to pass through the skin.

[0004] However, existing wireless transcutaneous power transfer technologies face significant challenges. The human body is a dynamic environment; changes in patient respiration, posture, physical activity, and differences in skin thickness between or within individuals can all alter the axial gap, lateral offset, and orientation angle between the internal and external coils. This directly changes the coupling coefficient between the coils, causing the system to deviate from its optimal resonant point, resulting in decreased transmission efficiency, unstable output power, and the risk of tissue overheating.

[0005] One existing solution involves sampling voltage / current signals at the implantation site and feeding them back to the operating side for control via wireless communication (such as radio frequency or infrared). This method requires a feedback circuit, which itself consumes valuable battery power at the implantation site, increasing energy consumption. Summary of the Invention

[0006] This application provides a wireless transcutaneous transmission system, the main technical problem of which is to reduce the power consumption of the system.

[0007] To solve the above-mentioned technical problems, one technical solution adopted in this application is: to provide a wireless transcutaneous transmission system, including: a transmitting unit, the transmitting unit including a control unit and a primary transmitting coil, a magnetic field sensor is disposed at the center of the primary transmitting coil, the magnetic field sensor is configured to detect the magnetic field strength generated by a magnet and output a voltage detection signal; the control unit is configured to determine the current frequency parameters based on the voltage detection signal, and output a first control signal to control the primary transmitting coil based on the current frequency parameters; The receiving unit includes a secondary receiving coil and a load. A magnet is disposed at the center of the secondary receiving coil, and the secondary receiving coil is configured to generate a power supply signal based on the magnetic field strength to supply power to the load.

[0008] In one embodiment, the control unit is configured to determine the current frequency parameter based on a voltage detection signal and a first preset curve, wherein the first preset curve characterizes the mapping relationship between the voltage value corresponding to the voltage detection signal and the frequency.

[0009] In one embodiment, the control unit is further configured to determine the coil axial gap based on a voltage detection signal and a second preset curve, the second preset curve representing the mapping relationship between the voltage value corresponding to the voltage detection signal and the coil axial gap.

[0010] In one embodiment, the control unit includes: The controller, connected to the magnetic field sensor, is configured to determine the current frequency parameter based on the voltage detection signal and a first preset curve, and output a first control signal based on the current frequency parameter; The resonant unit, connected to the controller, is configured to convert a first control signal into a second control signal to control the primary transmitting coil.

[0011] In one embodiment, the transmitting unit further includes: The resonant full-bridge unit is connected to the primary transmitting coil; The conversion unit is connected between the resonant unit and the resonant full-bridge unit.

[0012] In one embodiment, the resonant full-bridge unit includes an inductor and a first resonant capacitor, a first end of the first resonant capacitor being connected to a primary transmitting coil, a second end of the first resonant capacitor being connected to a first end of the inductor, and a second end of the inductor being connected to a switching unit.

[0013] In one embodiment, the receiving unit further includes a rectification unit connected between the secondary receiving coil and the load.

[0014] In one embodiment, the receiving unit further includes a second resonant capacitor, the first end of which is connected to the secondary receiving coil, and the second end of which is connected to the rectifier unit.

[0015] In one embodiment, the receiving unit further includes a filter capacitor, the first end of which is connected to the rectifier unit, and the second end of which is connected to the load.

[0016] In one embodiment, the magnetic field sensor includes a Hall sensor, and the magnet includes a neodymium iron boron magnet.

[0017] Unlike existing technologies, the wireless transdermal transmission system of this application includes: a transmitting unit, which includes a control unit and a primary transmitting coil. A magnetic field sensor is disposed at the center of the primary transmitting coil. The magnetic field sensor is configured to detect the magnetic field strength generated by a magnet and output a voltage detection signal. The control unit is configured to determine the current frequency parameters based on the voltage detection signal and output a first control signal to control the primary transmitting coil based on the current frequency parameters. A receiving unit includes a secondary receiving coil and a load. The secondary receiving coil includes a magnet and is configured to generate a power supply signal based on the magnetic field strength to power the load. The wireless transdermal transmission system of this application forms a non-contact structure through the magnetic field sensor and magnet, which can dynamically adjust the frequency according to the voltage feedback, overcoming the detuning problem caused by changes in the coupling coefficient. This allows the system to automatically maintain an optimal or near-optimal resonant transmission state under various dynamic environments. This process does not require a feedback circuit on the implantation side, avoiding additional power consumption and reducing the system's power consumption. Attached Figure Description

[0018] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a schematic diagram of the structure of the first embodiment of the wireless transcutaneous transmission system of this application; Figure 2 This is a schematic diagram of the structure of the second embodiment of the wireless transcutaneous transmission system of this application; Figure 3 This is a schematic diagram of the first preset curve in this application; Figure 4 This is a schematic diagram of the second preset curve in this application; Figure 5 This is a schematic diagram of the third embodiment of the wireless transcutaneous transmission system of this application. Detailed Implementation

[0020] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of the embodiments. Based on the embodiments of this application, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the scope of protection of this application.

[0021] The terms "first," "second," and "third" in this application are for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined as "first," "second," or "third" may explicitly or implicitly include at least one of that feature. In the description of this application, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified. All directional indications (such as up, down, left, right, front, back, etc.) in the embodiments of this application are only used to explain the relative positional relationships and movements between components in a specific orientation (as shown in the figures). If the specific orientation changes, the directional indications also change accordingly. Furthermore, the terms "comprising" and "having," and any variations thereof, 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 limited to the listed steps or units, but may optionally include steps or units not listed, or may optionally include other steps or units inherent to these processes, methods, products, or devices.

[0022] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0023] The present application will now be described in detail with reference to the accompanying drawings and embodiments.

[0024] Please see Figure 1 , Figure 1 This is a schematic diagram of the structure of a first embodiment of the wireless transcutaneous transmission system of this application, specifically including: a transmitting unit 10 and a receiving unit 20. The transmitting unit 10 includes a control unit 11 and a primary transmitting coil 12. A magnetic field sensor 13 is disposed at the center of the primary transmitting coil 12. The magnetic field sensor 13 is configured to detect the magnetic field strength generated by the magnet 22 and output a voltage detection signal. The control unit 11 is configured to determine the current frequency parameters based on the voltage detection signal and output a first control signal to control the primary transmitting coil 12 based on the current frequency parameters. The receiving unit 20 includes a secondary receiving coil 21 and a load 24. A magnet 22 is disposed at the center of the secondary receiving coil 21. The secondary receiving coil 21 is configured to generate a power supply signal based on the magnetic field strength to power the load 24.

[0025] The primary transmitting coil 12 and the secondary receiving coil 21 are helically wound flat coils. The operating voltage of the load 24 is, for example, 15V, and the rated power is 10W.

[0026] In one embodiment, the magnetic field sensor 13 includes a Hall sensor, and the magnet 22 includes a neodymium iron boron magnet. The magnetic field sensor 13 is fixedly mounted at the center of the primary transmitting coil 12, and the magnet 22 is fixedly mounted at the center of the secondary receiving coil 21.

[0027] The wireless transcutaneous transmission system of this application includes a magnetic field sensor 13 and a magnet 22, forming a non-contact structure capable of providing feedback on physical location. Specifically, the magnetic field sensor 13 senses the magnetic field generated by the magnet 22 and obtains a voltage detection signal based on the detected magnetic field strength. This allows the control unit 11 to determine the current frequency based on the voltage detection signal, thereby outputting a first control signal to control the primary transmitting coil 12. Understandably, the current frequency follows the change in the voltage detection signal. Dynamically adjusting the frequency based on the voltage overcomes the detuning problem caused by changes in the coupling coefficient, enabling the system to automatically maintain an optimal or near-optimal resonant transmission state under various dynamic environments.

[0028] The wireless transdermal transmission system of this application does not require an additional feedback circuit to feed back electrical signals from the implantation side (i.e., the load side), does not consume energy from the implantation side, reduces the system's energy consumption, and can quickly and automatically adapt to dynamic changes in voltage, always ensuring that the system maintains or operates at the transmission point close to the maximum power, so that it is in the best working state under dynamic conditions such as skin thickness, posture changes, breathing, and body activity.

[0029] It should be noted that the voltage detection signal changes with the axial spacing of the coils. The axial spacing of the coils refers to the distance between the primary transmitting coil 12 and the secondary receiving coil 21. That is, when the distance between the primary transmitting coil 12 and the secondary receiving coil 21 changes, the voltage value of the voltage detection signal will also change. In order to maintain the optimal resonant transmission state, the current frequency parameters need to be adjusted synchronously.

[0030] In one embodiment, the control unit 11 is configured to determine the current frequency parameters based on a voltage detection signal and a first preset curve, whereby the first preset curve represents the mapping relationship between the voltage value corresponding to the voltage detection signal and the frequency. Determining the current frequency parameters based on the voltage detection signal and the first preset curve enables automatic, rapid, and precise adjustment of the system's operating frequency, allowing the wirelessly powered transdermal power transmission system to maintain efficient and stable power transmission in various dynamic environments.

[0031] In another embodiment, the control unit 11 is further configured to determine the coil axial gap based on a voltage detection signal and a second preset curve, wherein the second preset curve characterizes the mapping relationship between the voltage value corresponding to the voltage detection signal and the coil axial gap.

[0032] Specifically, it is necessary to establish a first preset curve representing the mapping relationship between the voltage value corresponding to the voltage detection signal and the frequency, and to establish a second preset curve representing the mapping relationship between the voltage value corresponding to the voltage detection signal and the axial gap of the coil, so as to associate the axial gap of the coil with the frequency.

[0033] First, the transmitting unit 10 is fixed, ensuring the relative position of the magnetic field sensor 13 and the primary transmitting coil 12 remains unchanged. A high-precision rangefinder is used to accurately measure and control the axial distance d between the primary transmitting coil 12 and the secondary receiving coil 21, using this as a reference value. A load parameter is set for the load 24, for example, a fixed resistance value of 20Ω is set for simulation. The axial distance d between the primary transmitting coil 12 and the secondary receiving coil 21 is controlled, increasing from a minimum of 0mm in fixed steps of 1mm to a maximum of 25mm. The i-th given axial distance is denoted as d_i. At the i-th given axial distance d_i, the control unit 11 outputs control signals at multiple operating frequencies to control the primary transmitting coil. The range of these multiple operating frequencies is 100kHz-200kHz. Simultaneously, the output voltage V_out or output power P_out of the secondary receiving coil 21 is detected and recorded. Find the optimal frequency f_opt_i that maximizes either the output voltage V_out or the output power P_out (f_opt_i corresponds to the optimal frequency for the i-th given axial gap d_i). Simultaneously, record the voltage value V_hall_i corresponding to the voltage detection signal output by the magnetic field sensor 13 at this time (V_hall_i corresponds to the voltage value for the i-th given axial gap d_i). This will yield the calibration data (d_i, V_hall_i, f_opt_i) for the i-th given axial gap d_i. Using the above method, a set of calibration data can be obtained for each given axial gap. By fitting these multiple sets of calibration data, a first preset curve and a second preset curve can be established.

[0034] In one embodiment, the formula for the second preset curve is V_hall=A d²+B d+C (Formula 1), where A, B, and C are fitting coefficients. Substituting the obtained sets of calibration data into Formula (1), A, B, and C are calculated, thus yielding the second preset curve. The second preset curve is as follows: Figure 4 As shown, it can be seen that the voltage value of the voltage detection signal (i.e., the output voltage) is positively correlated with the axial spacing of the coil.

[0035] In one embodiment, the formula for the first preset curve is f_opt=P V_hall³+Q V_hall²+R V_hall+S (Formula 2), where P, Q, R, and S are fitting coefficients. Substituting the obtained multiple sets of calibration data into Formula (2), P, Q, R, and S are calculated, thus allowing the calculation of the first preset curve, as shown in the figure. Figure 3 As shown.

[0036] Specifically, the fitting coefficients A, B, C and P, Q, R, S are stored in the control unit 11. When the voltage value V_hall corresponding to the known voltage detection signal is known, the current frequency can be calculated according to the fitting coefficients P, Q, R, S combined with formula (2). The axial gap of the coil can also be calculated according to the fitting coefficients A, B, C combined with formula (1).

[0037] The first and second preset curves mentioned above are obtained under a fixed load. In another embodiment, to improve the system's adaptability under different load conditions, multiple load conditions can be set (e.g., loads of 10Ω, 20Ω, and 40Ω), and multiple different first and second preset curves can be established and stored for each load condition. During system operation, the correct calibration curve can be automatically selected based on the estimated load conditions.

[0038] See Figure 2 , Figure 2 This is a schematic diagram of the structure of a second embodiment of the wireless transcutaneous transmission system of this application. In this embodiment, the control unit 11 includes a controller 112 and a resonant unit 111. The controller 112 is connected to a magnetic field sensor 13 and is configured to determine the current frequency parameters based on a voltage detection signal and a first preset curve, and output a first control signal based on the current frequency parameters. The resonant unit 111 is connected to the controller 112 and is configured to convert the first control signal into a second control signal to control the primary transmitting coil. The controller 112 is isolated from the primary transmitting coil 12 by an isolation component. In one embodiment, the controller 112 is isolated from the primary transmitting coil 12 by a ferrite sheet.

[0039] Specifically, the controller 112 is equipped with an analog-to-digital converter (ADC). The ADC is used to acquire the voltage detection signal output by the magnetic field sensor 13 in real time at a certain sampling rate, such as 1 kHz. The sampled voltage detection signal is digitally filtered, for example, by using a moving average filter or a low-pass filter algorithm to eliminate noise interference and obtain a stable voltage value (i.e., V_hall). The fitting coefficients P, Q, R, and S are read and combined with the formula (2) f_opt=P V_hall³+Q V_hall²+R V_hall+S (i.e., the first preset curve) can be used to calculate the corresponding current frequency parameters. Based on the calculated current frequency parameters, the controller 112 adjusts the reload value of its internal timer, thereby outputting a first control signal, i.e., a PWM signal, to the resonant unit 111. The resonant unit 111 converts the first control signal into a second control signal to control the primary transmitting coil.

[0040] In one embodiment, the resonant unit 111 is a high-frequency resonant converter. The resonant unit 111 converts the first control signal, i.e., the PWM signal, into a high-frequency square wave pulse signal, i.e., the second control signal, and outputs it to control the primary transmitting coil.

[0041] In one embodiment, combined with Figure 5 , Figure 5 This is a schematic diagram of the structure of the third embodiment of the wireless transcutaneous transmission system of this application. The transmitting unit 10 further includes a resonant full-bridge unit 15 and a conversion unit 14. The resonant full-bridge unit 15 is connected to the primary transmitting coil 12; the conversion unit 14 is connected between the resonant unit 111 and the resonant full-bridge unit 15. Specifically, the resonant full-bridge unit 15 includes an inductor L and a first resonant capacitor C1. The first end of the first resonant capacitor C1 is connected to the primary transmitting coil 12, the second end of the first resonant capacitor C1 is connected to the first end of the inductor L, and the second end of the inductor L is connected to the conversion unit 14.

[0042] In one embodiment, the capacitance of the first resonant capacitor C1 is 20-40 nF (nanofarad), for example, 27 nF (nanofarad). The inductance of the inductor L is, for example, 30-60 μH (microhenry), for example, 40 μH (microhenry). This enables the resonant frequency of the resonant full-bridge unit to reach a predetermined frequency, for example, 150 kHz.

[0043] In one embodiment, the conversion unit 14 is a full-bridge inverter. The second control signal output by the resonant unit 111 drives the MOSFET switching transistor of the full-bridge inverter, thereby applying the second control signal to both ends of the resonant full-bridge unit 15. The resonant full-bridge unit 15 can select the frequency of the second control signal, thereby generating a high-frequency sinusoidal AC voltage across the inductor L. The amplitude of this high-frequency sinusoidal AC voltage varies with the current frequency parameters, so that the waveform frequency applied to the resonant full-bridge unit 15 matches the current frequency parameters. The wireless transcutaneous transmission system operates at the current frequency parameters, thereby adapting to changes in the coil axial gap caused by body movement, so that the system always maintains or approaches maximum transmission efficiency.

[0044] It should be noted that the actual optimal resonant frequency of the wireless transcutaneous transmission system depends on the inductance value of inductor L, the capacitance value of the first resonant capacitor C1, and the coupling coefficient between the primary transmitting coil 12 and the secondary receiving coil 21. The current in inductor L generates an alternating electromagnetic field around it, and according to the principle of electromagnetic induction, this alternating electromagnetic field will induce an alternating voltage in the secondary receiving coil 21.

[0045] In one embodiment, the wireless transcutaneous transmission system further includes a power supply 30, which is a DC power supply used to power the transmitting unit 10.

[0046] In one embodiment, the receiving unit 20 further includes a rectifier unit 23 connected between the secondary receiving coil 21 and the load 24. The rectifier unit 23 converts the AC voltage induced in the secondary receiving coil 21 into a pulsed DC voltage.

[0047] In one embodiment, the receiving unit 20 further includes a second resonant capacitor C2, the first end of which is connected to the secondary receiving coil 21, and the second end of which is connected to the rectifier unit 23.

[0048] In one embodiment, the receiving unit 20 further includes a filter capacitor C3, with its first terminal connected to the rectifier unit 23 and its second terminal connected to the load 24. The rectifier unit 23 converts the AC voltage induced by the secondary receiving coil 21 into a pulsed DC voltage, which, after passing through the filter capacitor C3, outputs a stable DC voltage for powering the load 24 or charging the battery within the load 24.

[0049] In one embodiment, the secondary receiving coil 21 and the second resonant capacitor C2 form a series resonant circuit, and the resonant frequency on the receiving unit 20 side is tuned to the same resonant frequency as the transmitting unit 10. When the system operates in the resonant state, the energy transmission efficiency from the transmitting unit 10 side to the receiving unit 20 side reaches its maximum.

[0050] In use, the wireless transdermal transmission system of this application involves implanting a portion of the receiving unit 20, such as the load 24, into the body, and placing the primary transmitting coil 12 at the corresponding location on the skin. After the system is powered on, the controller continuously samples the voltage detection signal output by the magnetic field sensor 13. The sampled voltage detection signal is filtered and then input into the pre-stored formula (2): f_opt=P V_hall³+Q V_hall²+R V_hall+S (i.e., the first preset curve) can be used to calculate the corresponding current frequency parameters. The controller adjusts the output of the first control signal according to the current frequency parameters. This process is repeated cyclically to achieve dynamic automatic optimization control. The wireless transcutaneous transmission system of this application can form a closed-loop feedback, continuously executing hundreds of times per second, forming a highly dynamic response closed-loop control system that can track rapid changes caused by breathing, movement, etc. in real time.

[0051] The wireless transdermal transmission system of this application features a non-contact structure formed by a magnetic field sensor 13 and a magnet 22. This structure is characterized by low cost, small size, high reliability, simple structure, and ease of implementation, and it is easily integrated into existing wireless transdermal energy transmission systems. The non-contact structure formed by the magnetic field sensor 13 and magnet 22 allows for real-time acquisition of voltage detection signals based on magnetic field strength, eliminating the need for feedback signals such as voltage / current signals on the implantation side (i.e., the load side). This eliminates implantation-side energy consumption and complexity, avoids additional power consumption and circuitry, reduces system energy consumption, and improves the reliability and safety of the implant. Furthermore, the wireless transdermal transmission system of this application, based on direct measurement of physical location, offers fast control response and can adapt to rapid changes caused by breathing, movement, etc. By combining the voltage detection signal with a pre-calibrated first preset curve to determine the current frequency parameters, the system can automatically, quickly, and accurately adjust the operating frequency, ensuring that the system operates at the optimal frequency under various conditions, resulting in high transmission efficiency and stable output.

[0052] In the several embodiments provided in this application, it should be understood that the disclosed systems, apparatuses, and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative; for instance, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be through some interfaces, or indirect coupling or communication connection between apparatuses or units, and may be electrical, mechanical, or other forms.

[0053] Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0054] The above are merely embodiments of this application and do not limit the scope of this patent application. Any equivalent structural or procedural changes made using the content of this application's specification and drawings, or direct or indirect applications in other related technical fields, are similarly included within the scope of patent protection of this application.

Claims

1. A wireless transcutaneous transmission system, characterized in that, include: The transmitting unit includes a control unit and a primary transmitting coil. A magnetic field sensor is disposed at the center of the primary transmitting coil. The magnetic field sensor is configured to detect the magnetic field strength generated by a magnet and output a voltage detection signal. The control unit is configured to determine the current frequency parameter based on the voltage detection signal and output a first control signal to control the primary transmitting coil based on the current frequency parameter. The receiving unit includes a secondary receiving coil and a load. The magnet is disposed at the center of the secondary receiving coil, and the secondary receiving coil is configured to generate a power supply signal based on the magnetic field strength to supply power to the load.

2. The wireless transcutaneous transmission system according to claim 1, characterized in that, The control unit is configured to determine the current frequency parameter based on the voltage detection signal and a first preset curve, wherein the first preset curve represents the mapping relationship between the voltage value and the frequency corresponding to the voltage detection signal.

3. The wireless transcutaneous transmission system according to claim 2, characterized in that, The control unit is also configured to determine the coil axial gap based on the voltage detection signal and a second preset curve, wherein the second preset curve characterizes the mapping relationship between the voltage value corresponding to the voltage detection signal and the coil axial gap.

4. The wireless transcutaneous transmission system according to claim 2, characterized in that, The control unit includes: A controller, connected to the magnetic field sensor, is configured to determine the current frequency parameter based on the voltage detection signal and a first preset curve, and output a first control signal based on the current frequency parameter; A resonant unit, connected to the controller, is configured to convert the first control signal into a second control signal to control the primary transmitting coil.

5. The wireless transcutaneous transmission system according to claim 4, characterized in that, The transmitting unit also includes: A resonant full-bridge unit is connected to the primary transmitting coil; A conversion unit is connected between the resonant unit and the resonant full-bridge unit.

6. The wireless transcutaneous transmission system according to claim 5, characterized in that, The resonant full-bridge unit includes an inductor and a first resonant capacitor. The first end of the first resonant capacitor is connected to the primary transmitting coil, the second end of the first resonant capacitor is connected to the first end of the inductor, and the second end of the inductor is connected to the conversion unit.

7. The wireless transcutaneous transmission system according to claim 1, characterized in that, The receiving unit further includes a rectification unit connected between the secondary receiving coil and the load.

8. The wireless transcutaneous transmission system according to claim 7, characterized in that, The receiving unit further includes a second resonant capacitor, the first end of which is connected to the secondary receiving coil, and the second end of which is connected to the rectifier unit.

9. The wireless transcutaneous transmission system according to claim 7, characterized in that, The receiving unit further includes a filter capacitor, the first end of which is connected to the rectifier unit, and the second end of which is connected to the load.

10. The wireless transcutaneous transmission system according to claim 1, characterized in that, The magnetic field sensor includes a Hall sensor, and the magnet includes a neodymium iron boron magnet.

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