Wireless power supply calibration device and method for medical electronic equipment

Abstract

The invention provides a wireless power supply calibration device and method for medical electronic equipment, and belongs to the technical field of medical electronic equipment, and the device comprises an in-vitro transmitting module which comprises a motor unit, a transmitting coil and a resonance circuit; the in-vivo receiving module comprises a receiving coil, a magnetic field detection unit and a microcontroller; the magnetic field detection unit is used for collecting magnetic field data of the transmitting coil; the microcontroller is used for determining the position offset of the transmitting coil and the receiving coil based on the magnetic field data; and the control module is used for receiving the position offset and controlling the motor unit to rotate based on the position offset so as to drive the transmitting coil to move through the rotation of the motor unit until the transmitting coil is aligned with the receiving coil, and is also used for controlling the resonant circuit to adjust the resonant frequency of the transmitting coil so as to enable the transmitting coil to be matched with the receiving coil. According to the invention, the problems of low energy transmission efficiency and large energy loss of the existing wireless power supply technology of the medical electronic equipment can be solved.

Description

Technical Field

[0001] This invention relates to the field of medical electronic equipment technology, and specifically to a wireless power supply calibration device and method for medical electronic equipment. Background Technology

[0002] In the field of medical electronic devices, wireless power supply technology, with its advantages of being non-invasive and convenient, has become a key supporting technology for implantable medical electronic devices, and is widely used in devices such as pacemakers, neurostimulators, and brain-computer interfaces. However, existing wireless power supply technology still faces the following technical bottlenecks that urgently need to be addressed in practical applications: Wireless power supply relies on precise coupling between the transmitting and receiving coils. Patient activities or changes in body posture can easily cause misalignment between the transmitting and receiving coils in the planar direction (X / Y axis). When the misalignment exceeds 5mm, energy transmission efficiency decreases by more than 30%. Simultaneously, changes in the vertical direction (Z axis) (such as differences in implantation depth or device displacement) can cause resonant frequency shifts, further exacerbating energy loss. This efficiency loss not only limits the device's battery life and charging time but may also affect the normal functioning of medical electronic devices.

[0003] In summary, existing wireless power supply technologies for medical electronic devices suffer from low energy transmission efficiency and significant energy loss. Summary of the Invention

[0004] In view of this, it is necessary to provide a wireless power supply calibration device and method for medical electronic devices to solve the technical problems of low energy transmission efficiency and large energy loss in the existing wireless power supply technology for medical electronic devices.

[0005] To address the aforementioned problems, in a first aspect, the present invention provides a wireless power supply calibration device for medical electronic devices, comprising: An external emission module includes: a motor unit, a transmitting coil drivenly connected to the motor unit, and a resonant circuit electrically connected to the transmitting coil; An in-body receiving module includes: a receiving coil, a magnetic field detection unit, and a microcontroller; the magnetic field detection unit is used to collect magnetic field data of the transmitting coil and send the magnetic field data to the microcontroller; the microcontroller is used to determine the positional offset between the transmitting coil and the receiving coil based on the magnetic field data; The control module is used to receive the position offset and control the motor unit to rotate based on the position offset, so as to drive the transmitting coil to move through the rotation of the motor unit until the transmitting coil is aligned with the receiving coil. It is also used to control the resonant circuit to adjust the resonant frequency of the transmitting coil so that the transmitting coil is matched with the receiving coil.

[0006] In one possible implementation, the magnetic field detection unit includes a plurality of magnetic sensors disposed around a receiving coil.

[0007] In one possible implementation, the plurality of magnetic sensors are orthogonally distributed around the receiving coil to form a three-dimensional magnetic field gradient detection array.

[0008] In one possible implementation, determining the positional offset between the transmitting coil and the receiving coil based on the magnetic field data includes: The positional offset between the transmitting coil and the receiving coil is determined based on the differences between the magnetic field data collected by magnetic sensors at different locations.

[0009] In one possible implementation, the formula for calculating the position offset is: ,

[0010] in, It is the position offset along the X-axis. This is the position offset along the Y-axis. The X-axis and Y-axis form a horizontal plane. These represent the magnetic field strength values ​​detected by different magnetic sensors. This is the correction coefficient for the position change of the magnetic sensor along the X-axis. This is the correction coefficient for the position change of the magnetic sensor along the Y-axis.

[0011] In one possible implementation, the X-axis position change correction coefficient and the Y-axis position change correction coefficient are obtained based on the following steps: The magnetic field data collected by the magnetic sensors at different locations are fitted to obtain a fitting curve that characterizes the relationship between the magnetic sensor position and the magnetic field data. Based on the fitting curve, the position change correction coefficient of the X-axis and the position change correction coefficient of the Y-axis are calculated.

[0012] In one possible implementation, the control module is further configured to determine the magnetic field strength in the Z-axis direction based on the magnetic field data, and determine the Z-axis distance of the transmitting coil based on the magnetic field strength in the Z-axis direction, and adjust the power or frequency of the transmitting coil to maintain the energy transmission efficiency of the transmitting coil if the Z-axis distance exceeds a preset distance threshold range. The plane formed by the Z-axis, X-axis, and Y-axis is perpendicular to each other, and the Z-axis distance is the distance between the transmitting coil and the receiving coil in the Z-axis direction.

[0013] In one possible implementation, the in vivo receiving module further includes: a rectifier and filter circuit, and an electrical signal and temperature detection unit; The rectifier and filter circuit is electrically connected to the receiving coil and is used to receive the electrical signal collected by the receiving coil and to rectify and filter the electrical signal to obtain a rectified and filtered electrical signal. The electrical signal and temperature detection unit is electrically connected to the rectifier and filter circuit and the microcontroller, respectively. It is used to calculate the voltage and current values ​​of the receiving coil after rectification and filtering based on the rectified and filtered electrical signal, and to collect the temperature value of the receiving coil. The voltage, current and temperature values ​​are then forwarded to the control module through the microcontroller. The control module is further configured to determine the resonant frequency of the resonant circuit based on the current value, adjust the voltage of the resonant circuit when the voltage value exceeds a preset voltage threshold range, and adjust the voltage and resonant frequency of the resonant circuit when the temperature value exceeds a preset temperature threshold range.

[0014] In one possible implementation, the control module is used to input the position offset into a PID control algorithm model to adjust the speed, direction of rotation, and number of rotations of the motor unit.

[0015] In a second aspect, the present invention also provides a wireless power supply calibration method for a medical electronic device, the method being applied to the device described in any of the preceding claims, the method comprising: The magnetic field data of the transmitting coil is collected by the magnetic field detection unit and sent to the microcontroller. Based on the magnetic field data, the microcontroller determines the positional offset between the transmitting coil and the receiving coil. The control module receives the position offset and controls the motor unit to rotate based on the position offset. The rotation of the motor unit drives the transmitting coil to move until the transmitting coil is aligned with the receiving coil. The control module also controls the resonant circuit to adjust the resonant frequency of the transmitting coil so that the transmitting coil matches the receiving coil.

[0016] The beneficial effects of the above implementation method are as follows: The wireless power supply calibration device and method for medical electronic devices provided by the present invention collects the magnetic field data of the transmitting coil through a magnetic field detection unit, and determines the positional offset between the transmitting coil and the receiving coil by a microcontroller in combination with the magnetic field data. The positional offset can be calculated and updated in real time based on the magnetic field data. When the body posture of a person changes, the magnetic field data will also change, and thus the positional offset will also be updated. The present invention controls the rotation of the motor unit according to the positional offset, so as to drive the transmitting coil to move through the rotation of the motor unit until the transmitting coil and the receiving coil are aligned. After alignment, the resonant circuit is controlled to adjust the resonant frequency of the transmitting coil, so that the transmitting coil and the receiving coil are matched. This avoids the misalignment distance between the transmitting coil and the receiving coil being too large, which would lead to a sharp drop in energy transmission efficiency and excessive energy loss. Thus, it solves the technical problems of low energy transmission efficiency and large energy loss in the existing wireless power supply technology for medical electronic devices. Attached Figure Description

[0017] To more clearly illustrate the technical solutions in the embodiments of the present invention, 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 the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0018] Figure 1 A structural diagram of an embodiment of the wireless power supply calibration device for medical electronic devices provided by the present invention; Figure 2 A flowchart of an embodiment of the wireless power supply calibration method for medical electronic devices provided by the present invention; Figure 3 A flowchart of another embodiment of the wireless power supply calibration method for medical electronic devices provided by the present invention. Detailed Implementation

[0019] The technical solutions of the embodiments of the present invention 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 the present invention, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without creative effort are within the scope of protection of the present invention.

[0020] In the description of the embodiments of this application, unless otherwise stated, "a plurality of" means two or more.

[0021] In this embodiment of the invention, the terms "comprising" and "having" and any variations thereof are intended to cover non-exclusive inclusion, for example, a process, method, apparatus, product or device that includes a series of steps or modules is not necessarily limited to those steps or modules that are explicitly listed, but may include other steps or modules that are not explicitly listed or that are inherent to such process, method, product or device.

[0022] The naming or numbering of steps in the embodiments of the present invention does not mean that the steps in the method flow must be executed in the time / logical order indicated by the naming or numbering. The execution order of the named or numbered process steps can be changed according to the technical purpose to be achieved, as long as the same or similar technical effect can be achieved.

[0023] 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 the invention. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a mutually exclusive, independent, or alternative embodiment. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0024] Existing wireless power supply relies on precise coupling between the transmitting and receiving coils. Patient activities or changes in body posture can easily cause misalignment of the coils in the planar direction (X / Y axis). When the misalignment distance exceeds 5mm, the energy transmission efficiency decreases by more than 30%. Simultaneously, changes in the vertical direction (Z axis) (such as differences in implantation depth or wearable device displacement) can cause resonant frequency shifts, further exacerbating energy loss. This efficiency loss not only limits the device's battery life and charging time but may also affect the normal functioning of medical electronic devices. Therefore, this invention provides a wireless power supply calibration device and method for medical electronic devices to solve this problem.

[0025] This invention provides a wireless power supply calibration device and method for medical electronic devices, which will be described below.

[0026] like Figure 1 As shown, the present invention provides a wireless power supply calibration device for medical electronic devices, comprising: The external emission module 101 includes: a motor unit 1011, an emission coil 1012 that is drivenly connected to the motor unit 1011, and a resonant circuit 1013 that is electrically connected to the emission coil 1012; The in-body receiving module 102 includes: a receiving coil 1022, a magnetic field detection unit 1021, and a microcontroller 1024; the magnetic field detection unit 1021 is used to collect magnetic field data of the transmitting coil 1012 and send the magnetic field data to the microcontroller 1024; the microcontroller 1024 is used to determine the positional offset between the transmitting coil 1012 and the receiving coil 1022 based on the magnetic field data; The control module 103 is used to receive the position offset and control the motor unit 1011 to rotate based on the position offset, so as to drive the transmitting coil 1012 to move through the rotation of the motor unit 1011 until the transmitting coil 1012 is aligned with the receiving coil 1022. It is also used to control the resonant circuit 1013 to adjust the resonant frequency of the transmitting coil 1012 so that the transmitting coil 1012 matches the receiving coil 1022.

[0027] It is understood that the medical electronic device in this invention refers to an implantable medical electronic device, such as a brain-computer interface device. The external transmitting module 101 is a device disposed outside the human body, and the internal receiving module 102 is a device disposed inside the human body.

[0028] refer to Figure 1 As shown, the control module 103 includes a microcontroller and a wireless communication module, and the in-body receiving module 102 also includes a wireless communication module. The two wireless communication modules are interconnected.

[0029] The diameter and number of turns of the transmitting coil 1012: A 42mm diameter Litz wire with 9 to 105 turns (0.08mm wire diameter) was selected as the transmitting coil 1012. This size satisfies wearability on the human body while generating a sufficiently strong magnetic field. According to electromagnetic induction theory, more turns result in a stronger magnetic field, but also increase coil resistance and power consumption. Experimental tests showed that, at this size, the 9-turn, 105-strand Litz wire achieves a good balance between energy transfer efficiency and power consumption, with the no-load current controlled below 50mA at a 170kHz operating frequency.

[0030] The core material for the 1012 transmitting coil is a nanocrystalline material with high permeability (μi>80000) and low loss (loss <100mW / cm³). The narrow hysteresis loop of the nanocrystalline material effectively reduces hysteresis loss, improving energy transfer efficiency by 15%-20% compared to traditional ferrite materials. The core is designed in a toroidal shape to reduce magnetic leakage and enhance magnetic field coupling.

[0031] The motor unit 1011 in this invention may include a stepper motor and a drive circuit, wherein: Motor Selection: OT-SM05P-001 miniature stepper motor, with a compact size (5.1mm in diameter), suitable for integration into portable external launch devices. This motor has a step angle of 18° / step and is driven by a TMC2209 driver, achieving a platform displacement accuracy of 0.1mm, meeting the system's high-precision positioning requirements for the 1012 launch coil.

[0032] Drive circuit: The TMC2209 driver connects to the 1024 microcontroller via UART / I2C communication protocol, allowing for flexible software settings of the stepper motor's microstepping mode, running direction, and speed. Utilizing StealthChop2 technology, it reduces motor noise by 80%.

[0033] The diameter and number of turns of the receiving coil 1022: The receiving coil 1022 has a diameter of 20mm and 18 turns, and is wound with multi-strand (24) wire. This miniaturized design is easy to implant in the human body. Due to the small size of the receiving coil 1022, the number of turns is appropriately increased to improve the magnetic induction intensity in order to ensure sufficient induced electromotive force. Simulation verification shows that the receiving coil 1022 with these parameters can stably output an induced voltage of 4~6V within a distance of 5-25mm from the transmitting coil 1012.

[0034] The receiving coil 1022 is packaged with Parylene-C, which has excellent biocompatibility and has passed ISO10993 biocompatibility certification, allowing for long-term implantation in the human body without triggering an immune response. Parylene-C also has good insulation properties (breakdown voltage > 100kV / mm) and moisture resistance, effectively protecting the coil and ensuring stable operation in the complex environment inside the body.

[0035] In some embodiments, the magnetic field detection unit 1021 includes a plurality of magnetic sensors disposed around the receiving coil 1022.

[0036] It is understood that in this embodiment, multiple magnetic sensors use non-contact three-dimensional positioning technology to replace traditional magnet alignment. This eliminates the need for magnet-assisted alignment, avoids the risk of eddy current heating, and enables real-time position detection in dynamic environments.

[0037] In some embodiments, the plurality of magnetic sensors are orthogonally distributed around the receiving coil 1022 to form a three-dimensional magnetic field gradient detection array.

[0038] Understandably, the sensor selection involves four MMC5633NJL 3-axis AMR magnetic sensors. These sensors utilize AMR technology, offering a high-precision magnetic field measurement capability of 0.0625 mG and a measurement range of ±30 G. The sensors incorporate a 20-bit ADC, converting the magnetic field signal into a digital output, which communicates with the 1024 microcontroller via an SPI interface.

[0039] Layout and Compensation: Four sensors are orthogonally distributed around the receiving coil 1022, forming a three-dimensional magnetic field gradient detection array. To eliminate mutual interference between sensors and the influence of ambient magnetic fields, each sensor is individually calibrated during system initialization to establish a mapping relationship between magnetic field strength and output data. Temperature compensation and zero-point drift correction are then performed in subsequent calculations.

[0040] In some embodiments, determining the positional offset between the transmitting coil 1012 and the receiving coil 1022 based on the magnetic field data includes: Based on the differences between the magnetic field data collected by magnetic sensors at different locations, the positional offset between the transmitting coil 1012 and the receiving coil 1022 is determined.

[0041] It is understandable that magnetic field energy is transferred from the transmitting coil 1012 to the receiving coil 1022. When there is a positional offset between the transmitting coil 1012 and the receiving coil 1022, the magnetic field data collected by the magnetic sensors at different positions will be different. Therefore, the positional offset between the transmitting coil 1012 and the receiving coil 1022 can be determined based on the difference between the magnetic field data collected by the magnetic sensors at different positions.

[0042] In some embodiments, the formula for calculating the position offset is: ,

[0043] in, It is the position offset along the X-axis. This is the position offset along the Y-axis. The X-axis and Y-axis form a horizontal plane. These represent the magnetic field strength values ​​detected by different magnetic sensors. This is the correction coefficient for the position change of the magnetic sensor along the X-axis. This is the correction coefficient for the position change of the magnetic sensor along the Y-axis.

[0044] It is understandable that, based on the above calculation formula for position offset, this invention can achieve dynamic calibration and energy transmission optimization. Combining the above calculation formula, the stepper motor achieves a displacement accuracy of 0.1mm through micro-step driving, adjusting the position of the transmitting coil 1012 in real time to compensate for X / Y axis offset.

[0045] In some embodiments, the X-axis position change correction factor and the Y-axis position change correction factor are obtained based on the following steps: The magnetic field data collected by the magnetic sensors at different locations are fitted to obtain a fitting curve that characterizes the relationship between the magnetic sensor position and the magnetic field data. Based on the fitting curve, the position change correction coefficient of the X-axis and the position change correction coefficient of the Y-axis are calculated.

[0046] Understandably, the position of the magnetic sensor and the magnetic field data can be determined based on the fitted curve, and then the theoretical magnetic field data corresponding to different positions can be determined. By comparing the theoretical magnetic field data at the corresponding position with the actual detected magnetic field data, the position of the magnetic sensor can be corrected based on the difference, thus obtaining the corresponding position change correction coefficient.

[0047] In some embodiments, the control module 103 is further configured to determine the magnetic field strength in the Z-axis direction based on the magnetic field data, and determine the Z-axis distance of the transmitting coil 1012 based on the magnetic field strength in the Z-axis direction, and adjust the power or frequency of the transmitting coil 1012 when the Z-axis distance exceeds a preset distance threshold range, so as to maintain the energy transmission efficiency of the transmitting coil 1012. The plane formed by the Z-axis, X-axis, and Y-axis is perpendicular to each other, and the Z-axis distance is the distance between the transmitting coil 1012 and the receiving coil 1022 in the Z-axis direction.

[0048] Understandably, the Z-axis distance is derived by inverting the relationship between magnetic field strength and distance, as shown in the formula:

[0049] In the formula, Where is the vacuum permeability, a constant; N is the number of turns of the transmitting coil 1012, which is 9 in the transmitting end design of this system; I is the excitation current, which can be obtained in real time through the current detection circuit during system operation; r is the radius of the transmitting coil 1012, which has a diameter of 42mm in this system, i.e., r = 21mm; Bz is the magnetic field strength in the Z-axis direction detected by the magnetic sensor. This formula is based on the theory of electromagnetic induction. When an excitation current is applied to the transmitting coil 1012, a magnetic field is generated in the surrounding space, and the magnetic field strength has a specific relationship with the distance. By combining the magnetic field strength Bz detected by the magnetic sensor with the known parameters of the transmitting coil 1012, the Z-axis distance can be calculated using the above formula. For example, when a change in Bz is detected, the system can quickly calculate the current Z-axis distance. If the distance exceeds the set range, energy transmission efficiency can be ensured by adjusting the power or frequency of the transmitting coil 1012.

[0050] Through the algorithm described above, the system can quickly and accurately obtain the positional relationship between the transmitting coil 1012 and the receiving coil 1022 in three-dimensional space, laying a solid foundation for subsequent dynamic calibration and efficient energy transmission.

[0051] In some embodiments, the in vivo receiving module 102 further includes: a rectifier and filter circuit 1023, and an electrical signal and temperature detection unit 1025; The rectifier and filter circuit 1023 is electrically connected to the receiving coil 1022 and is used to receive the electrical signal collected by the receiving coil 1022 and rectify and filter the electrical signal to obtain the rectified and filtered electrical signal. The electrical signal and temperature detection unit 1025 is electrically connected to the rectifier and filter circuit 1023 and the microcontroller 1024, respectively. It is used to calculate the voltage and current values ​​of the receiving coil 1022 after rectification and filtering based on the rectified and filtered electrical signal, and to collect the temperature value of the receiving coil 1022. The voltage value, the current value and the temperature value are then forwarded to the control module 103 through the microcontroller 1024. The control module 103 is further configured to determine the resonant frequency of the resonant circuit 1013 based on the current value, adjust the voltage of the resonant circuit 1013 when the voltage value exceeds a preset voltage threshold range, and adjust the voltage and resonant frequency of the resonant circuit 1013 when the temperature value exceeds a preset temperature threshold range.

[0052] It is understood that the detection unit includes an electrical signal calculation unit and a temperature sensor. The electrical signal calculation unit is used to calculate the voltage and current values ​​of the receiving coil 1022 after rectification and filtering, and the temperature sensor is used to collect the temperature value of the receiving coil 1022.

[0053] Temperature sensor: Integrated TMP117AIDRVR digital temperature sensor, which has a high-precision temperature measurement capability of ±0.1℃ (-20°C to 50°C). The sensor communicates with the 1024 microcontroller via a single-bus protocol, acquiring system temperature data once per second.

[0054] Thermal design: A large copper-clad design is used on the PCB of the transmitting coil 1012 and LLC resonant circuit 1013, and heat dissipation vias are added to improve heat conduction efficiency. At the same time, heat sinks are designed on the device casing to utilize natural convection for heat dissipation, ensuring that the temperature of critical components does not exceed 50°C during long-term system operation.

[0055] In some embodiments, the control module 103 is used to input the position offset into a PID control algorithm model to adjust the speed, direction of rotation and number of rotations of the motor unit 1011.

[0056] Understandably, existing wireless power supply products often employ magnet-assisted alignment technology to improve coil alignment accuracy. However, in an alternating magnetic field environment, eddy currents can occur inside the magnet, causing a rapid increase in localized temperature within the device. Clinical studies have shown that when the surface temperature of the device exceeds 2°C for an extended period, it can cause irreversible thermal damage to human tissue. Furthermore, high temperatures accelerate the aging of internal components, reducing the device's lifespan and reliability.

[0057] To address this issue, the position offset in this embodiment is not obtained through manual calibration using traditional magnet-assisted alignment techniques. Instead, the position offset can be determined in real-time based on the magnetic field data of the transmitting coil 1012, thus adapting to dynamic changes in the position of the transmitting coil 1012 and environmental variations. The PID control algorithm combines proportional, integral, and derivative control elements, employing a closed-loop control strategy. Closed-loop control is a control method that corrects based on feedback from the controlled object's output. It corrects deviations from the planned output according to quotas or standards. The input parameters of the PID control algorithm can be dynamically adjusted based on actual conditions. Combined with the inherent properties of the PID control algorithm, this easily ensures stable energy transmission, meeting the requirements for long-term, reliable operation of medical electronic equipment.

[0058] This invention also provides a wireless power supply calibration method for medical electronic devices, wherein the method is applied to any of the devices described above, such as... Figure 2 As shown, the method includes: S201. The magnetic field data of the transmitting coil 1012 is collected by the magnetic field detection unit 1021 and sent to the microcontroller 1024. S202. Based on the magnetic field data, the microcontroller 1024 determines the positional offset between the transmitting coil 1012 and the receiving coil 1022. S203. Based on the position offset received by the control module 103, the motor unit 1011 is controlled to rotate to drive the transmitting coil 1012 to move until the transmitting coil 1012 is aligned with the receiving coil 1022. Based on the position offset received by the control module 103, the resonant circuit 1013 is controlled to adjust the resonant frequency of the transmitting coil 1012 so that the transmitting coil 1012 matches the receiving coil 1022.

[0059] In some embodiments, the present invention uses the above-described apparatus to perform position calibration experiments, specifically including: Experimental setup: A human movement scenario was simulated on the experimental platform. The transmitting coil 1012 was fixed on a two-dimensional moving platform, and its displacement could be adjusted by ±10mm in the X / Y axis directions. The receiving coil 1022 was placed at a fixed position 15mm away from the transmitting coil 1012 to simulate the implantation state in the human body.

[0060] Data Acquisition and Processing: For specific procedures, please refer to... Figure 3 As shown, the offset of the transmitting coil 1012 in the X / Y axis direction is set in increments of 1 mm, gradually increasing from -5 mm to 5 mm. At each offset position, the magnetic sensor array collects magnetic field data. Based on the principle of spatial magnetic field gradient, the X / Y axis offset is calculated by analyzing the difference in magnetic field strength detected by the magnetic sensors at different positions. The formula is: ,

[0061] in, These are the magnetic field strength values ​​detected by the magnetic sensor at a specific location along the X or Y axis. For example, in a practical layout, It is the magnetic field strength collected by this sensor, which is distributed on both sides of the X-axis direction of the receiving coil 1022. The sensor position change correction coefficient is determined through pre-calibration. During calibration, the sensor is placed at different positions in a known magnetic field environment, and the magnetic field strength values ​​output by the sensor at different positions are recorded. The accurate position correction coefficient is obtained through methods such as curve fitting. In actual operation, the microcontroller 1024 acquires the magnetic field strength data collected by the sensor in real time. Substituting this data into the above formula, the offset in the X / Y axis directions can be quickly calculated, providing data support for subsequent adjustment of the transmitter coil 1012 position by the stepper motor. The Z-axis distance is obtained by inverse calculation based on the relationship between magnetic field strength and distance.

[0062] Through the algorithm described above, the system can quickly and accurately obtain the positional relationship between the transmitting coil 1012 and the receiving coil 1022 in three-dimensional space, laying a solid foundation for subsequent dynamic calibration and efficient energy transmission.

[0063] Experimental results: The average calibration time of the system is 1.5s, and the maximum residual error is <0.15mm. The experimental data show that the position detection and adjustment module can quickly and accurately calibrate the transmitting coil 1012, meeting the usage requirements of brain-computer interface devices in dynamic environments.

[0064] Frequency tracking experiment Experimental setup: Keep the transmitting coil 1012 and the receiving coil 1022 aligned in the X / Y axis directions, and change the distance in the Z axis direction, gradually increasing it from 5mm to 25mm in increments of 2mm. The initial operating frequency of the system is set to 150kHz.

[0065] Data Acquisition and Processing: At each distance, the receiver detects the peak current of the coil and feeds the current data back to the transmitter via BLE or other wireless communication technologies. The transmitter uses the golden ratio method to perform frequency sweeping, recording the frequency value and corresponding current value in each sweep until the resonant frequency corresponding to the maximum current is found. Simultaneously, the time required for frequency locking is recorded.

[0066] Specifically, a frequency tracking algorithm can be used, which employs the golden section method to sweep the frequency (range 100-300kHz, step size 10kHz). The resonant frequency is locked based on the current peak fed back by the receiver, with a locking time of <200ms. This adapts to the frequency shift caused by changes in Z-axis distance (5-25mm), and the energy transmission efficiency is improved to over 55% (compared to about 40% for traditional solutions).

[0067] Experimental results: When the Z-axis distance increased from 5mm to 25mm, the system automatically adjusted the frequency from 120kHz to 270kHz, with current fluctuation <5% and frequency lock-in time <200ms. These results verify that the frequency tracking module can quickly and accurately adapt to changes in coil distance, ensuring stable energy transfer efficiency.

[0068] Eddy current suppression and thermal management experiment Experimental setup: The receiving coil 1022 was continuously powered for 1 hour to simulate a long-term working scenario. The system did not use magnets for alignment; instead, it maintained coil alignment through three-dimensional position detection and a dynamic adjustment module for the transmitting coil 1012.

[0069] Data Acquisition and Processing: The TMP117AIDRVR temperature sensor monitors the surface temperature of the receiving coil 1022 in real time, recording temperature data every 10 seconds. Simultaneously, it acquires parameters such as the input voltage and current at the transmitting end and the output voltage and current at the receiving end to calculate the system's energy transfer efficiency.

[0070] Experimental results: After one hour of continuous power supply, the receiver temperature rose from 37℃ to 38.5℃, with the temperature rise controlled within 1.5℃. This experiment demonstrates that the eddy current suppression and thermal management module can effectively control heat generation and ensure safe system operation.

[0071] The present invention has the following beneficial effects: Position calibration accuracy: Tested, the X / Y axis positioning error is <0.2mm, the Z axis distance detection error is <0.5mm, and the energy transmission efficiency is improved to over 55%, which is a significant improvement compared to the traditional solution (about 40%).

[0072] Eddy current suppression and thermal management: After the magnet is completely removed, the system does not exhibit significant eddy current heating, and the temperature rise is controlled within 1.5℃, which greatly improves the safety of wireless power supply and the service life of the equipment.

[0073] Frequency tracking speed: resonant frequency lock time < 200ms, which can quickly adapt to the frequency offset problem caused by the relative position change of the transmitting coil 1012 and the receiving coil 1022 when the patient moves.

[0074] Long-term stability: Through multi-module collaborative work and dynamic calibration, the system can adapt to various patient movement scenarios, ensuring the long-term stable operation of the brain-computer interface.

[0075] Those skilled in the art will understand that all or part of the processes of the methods described in the above embodiments can be implemented by a computer program instructing related hardware, and the program can be stored in a computer-readable storage medium. The computer-readable storage medium may be a disk, optical disk, read-only memory, or random access memory, etc.

[0076] The wireless power supply calibration device and method for medical electronic devices provided by the present invention have been described in detail above. Specific examples have been used to illustrate the principle and implementation of the present invention. The description of the above embodiments is only for the purpose of helping to understand the method and core idea of ​​the present invention. At the same time, for those skilled in the art, there will be changes in the specific implementation and application scope based on the idea of ​​the present invention. Therefore, the content of this specification should not be construed as a limitation of the present invention.

Claims

1. A wireless power supply calibration device for medical electronic equipment, characterized in that, include: An external emission module includes: a motor unit, a transmitting coil drivenly connected to the motor unit, and a resonant circuit electrically connected to the transmitting coil; An in-body receiving module includes: a receiving coil, a magnetic field detection unit, and a microcontroller; the magnetic field detection unit is used to collect magnetic field data of the transmitting coil and send the magnetic field data to the microcontroller; the microcontroller is used to determine the positional offset between the transmitting coil and the receiving coil based on the magnetic field data; The control module is used to receive the position offset and control the motor unit to rotate based on the position offset, so as to drive the transmitting coil to move through the rotation of the motor unit until the transmitting coil is aligned with the receiving coil. It is also used to control the resonant circuit to adjust the resonant frequency of the transmitting coil so that the transmitting coil is matched with the receiving coil.

2. The wireless power supply calibration device for medical electronic equipment according to claim 1, characterized in that, The magnetic field detection unit includes multiple magnetic sensors, which are arranged around the receiving coil.

3. The wireless power supply calibration device for medical electronic equipment according to claim 2, characterized in that, The multiple magnetic sensors are orthogonally distributed around the receiving coil to form a three-dimensional magnetic field gradient detection array.

4. The wireless power supply calibration device for medical electronic equipment according to claim 3, characterized in that, Based on the magnetic field data, the positional offset between the transmitting coil and the receiving coil is determined, including: The positional offset between the transmitting coil and the receiving coil is determined based on the differences between the magnetic field data collected by magnetic sensors at different locations.

5. The wireless power supply calibration device for medical electronic equipment according to claim 4, characterized in that, The formula for calculating the position offset is: , in, It is the position offset along the X-axis. This is the position offset along the Y-axis. The X-axis and Y-axis form a horizontal plane. These represent the magnetic field strength values ​​detected by different magnetic sensors. This is the correction coefficient for the position change of the magnetic sensor along the X-axis. This is the correction coefficient for the position change of the magnetic sensor along the Y-axis.

6. The wireless power supply calibration device for medical electronic equipment according to claim 5, characterized in that, The X-axis and Y-axis position change correction factors are obtained based on the following steps: The magnetic field data collected by the magnetic sensors at different locations are fitted to obtain a fitting curve that characterizes the relationship between the magnetic sensor position and the magnetic field data. Based on the fitting curve, the position change correction coefficient of the X-axis and the position change correction coefficient of the Y-axis are calculated.

7. The wireless power supply calibration device for medical electronic equipment according to claim 5, characterized in that, The control module is also used to determine the magnetic field strength in the Z-axis direction based on the magnetic field data, and to determine the Z-axis distance of the transmitting coil based on the magnetic field strength in the Z-axis direction. If the Z-axis distance exceeds a preset distance threshold range, the power or frequency of the transmitting coil is adjusted to maintain the energy transmission efficiency of the transmitting coil. The plane formed by the Z-axis, X-axis, and Y-axis is perpendicular to each other, and the Z-axis distance is the distance between the transmitting coil and the receiving coil in the Z-axis direction.

8. The wireless power supply calibration device for medical electronic equipment according to claim 1, characterized in that, The in-body receiving module further includes: a rectifier and filter circuit, and an electrical signal and temperature detection unit; The rectifier and filter circuit is electrically connected to the receiving coil and is used to receive the electrical signal collected by the receiving coil and to rectify and filter the electrical signal to obtain a rectified and filtered electrical signal. The electrical signal and temperature detection unit is electrically connected to the rectifier and filter circuit and the microcontroller, respectively. It is used to calculate the voltage and current values ​​of the receiving coil after rectification and filtering based on the rectified and filtered electrical signal, and to collect the temperature value of the receiving coil. The voltage, current and temperature values ​​are then forwarded to the control module through the microcontroller. The control module is further configured to determine the resonant frequency of the resonant circuit based on the current value, adjust the voltage of the resonant circuit when the voltage value exceeds a preset voltage threshold range, and adjust the voltage and resonant frequency of the resonant circuit when the temperature value exceeds a preset temperature threshold range.

9. The wireless power supply calibration device for medical electronic equipment according to any one of claims 1-8, characterized in that, The control module is used to input the position offset into the PID control algorithm model to adjust the speed, direction of rotation and number of rotations of the motor unit.

10. A wireless power supply calibration method for medical electronic devices, characterized in that, The method is applied to the apparatus according to any one of claims 1-9, and the method comprises: The magnetic field data of the transmitting coil is collected by the magnetic field detection unit and sent to the microcontroller. Based on the magnetic field data, the microcontroller determines the positional offset between the transmitting coil and the receiving coil. The control module receives the position offset and controls the motor unit to rotate based on the position offset. The rotation of the motor unit drives the transmitting coil to move until the transmitting coil is aligned with the receiving coil. The control module also controls the resonant circuit to adjust the resonant frequency of the transmitting coil so that the transmitting coil matches the receiving coil.

Images