Method and apparatus for determining electromagnetic influence of cochlear implant, and non-transitory storage medium

Abstract

The application discloses a kind of electromagnetic influence determination method, device and nonvolatile storage medium of cochlear implant, wherein the method includes: obtaining brain tissue electromagnetic parameters and electric vehicle wireless charging frequency information, based on frequency information, brain tissue electromagnetic parameters calibration is carried out, and coupling model is constructed;Interference source parameters and human posture boundary are set, according to the coupling model, magnetic induction intensity is simulated and calculated, and interference signal is extracted;Circuit model is constructed;Interference signal is injected into circuit model and simulated, and the current of receiving coil and load voltage are determined;Current amplitude, audible sound frequency band corresponding current amplitude and the offset caused by interference signal to circuit static working point are determined, and then the influence result of electric vehicle wireless charging on cochlear implant is determined.The application solves the technical problem that the subsequent cochlear implant is difficult to adjust to resist electromagnetic disturbance due to the lack of cochlear implant electromagnetic disturbance influence determination method under the current electric vehicle wireless charging scene.

Description

Technical Field

[0001] This invention relates to the field of electromagnetic influence technology, and more specifically, to a method, apparatus, and non-volatile storage medium for determining the electromagnetic influence of a cochlear implant. Background Technology

[0002] The auditory system, an important sensory system in the human body, consists of the outer ear, middle ear, and inner ear. Normal hearing requires multiple steps, including sound wave collection, vibration transmission, neural signal conversion, and transmission. When the hair cells in the inner ear are damaged or die due to congenital factors or acquired injuries, it can lead to severe or profound hearing loss. In such cases, hearing aids cannot meet the needs of hearing recovery, and cochlear implants become the main solution.

[0003] An implantable cochlear implant consists of an external device (including a microphone, a speech processor, and an encoder transmitter) and an internal device (including a receiver stimulator and an electrode array). Its working principle is as follows: the microphone collects external sound signals and transmits them to the speech processor. The speech processor extracts the signal features and converts them into electrical signals, which are then transmitted to the encoder transmitter. The encoder transmitter transmits the electrical signals through the skin in the form of radio waves to the internal receiver stimulator. The receiver stimulator decodes the signals and transmits them to the electrode array, which ultimately stimulates the auditory nerve fibers to produce hearing.

[0004] However, unlike other implantable medical devices such as pacemakers, cochlear implants are external devices exposed to the environment and are susceptible to factors such as ambient temperature and humidity, electromagnetic interference, and external forces. With the widespread adoption of wireless charging technology for electric vehicles, the electromagnetic fields generated during charging may interfere with the propagation of electrical signals in the cochlear implant, potentially causing noise, functional abnormalities, and threatening the auditory safety of hearing-impaired patients. Currently, there is a lack of systematic evaluation methods for the impact of electromagnetic interference on cochlear implants in the context of wireless charging for electric vehicles, which cannot provide effective support for the safe use and design optimization of cochlear implants.

[0005] There is currently no effective solution to the above problems. Summary of the Invention

[0006] This invention provides a method, apparatus, and non-volatile storage medium for determining the electromagnetic interference of cochlear implants, at least to solve the technical problem that the lack of a method for determining the electromagnetic interference of cochlear implants in the context of wireless charging of electric vehicles makes it difficult to subsequently adjust the cochlear implant to resist electromagnetic interference.

[0007] According to one aspect of the present invention, a method for determining the electromagnetic influence of a cochlear implant is provided, comprising: acquiring electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles; calibrating the electromagnetic parameters of brain tissue and constructing a coupling model based on the frequency information, wherein the coupling model includes a cochlear implant and a human head structure; setting parameters of the interference source of the wireless charging for electric vehicles and human posture boundaries; based on the parameters of the interference source of the wireless charging for electric vehicles and the human posture boundaries, and according to the coupling model, simulating and calculating the magnetic induction intensity on the surface of the cochlear implant magnet using a time-domain solver, and extracting the interference signal; constructing a transcutaneous energy transfer circuit model of the cochlear implant based on the coupling model; injecting the interference signal into the transcutaneous energy transfer circuit model of the cochlear implant and performing simulation to determine the receiving coil current and load voltage; determining the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset caused by the interference signal to the static operating point of the circuit based on the receiving coil current and load voltage; and determining the impact of wireless charging for electric vehicles on the cochlear implant based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset.

[0008] Optionally, based on frequency information, the electromagnetic parameters of brain tissue are calibrated and a coupled model is constructed, including: determining the operating frequency band for wireless charging of electric vehicles based on frequency information; selecting a target frequency within the operating frequency band as the core analysis frequency; obtaining electromagnetic parameter verification data at the core analysis frequency according to a preset standard; comparing the electromagnetic parameters of brain tissue with the electromagnetic parameter verification data to determine the deviation value; calibrating the electromagnetic parameters of brain tissue using interpolation if the deviation value exceeds a preset error range to obtain calibrated electromagnetic parameters of brain tissue; and constructing a coupled model based on the calibrated electromagnetic parameters of brain tissue and the preset structural parameters of the cochlear implant.

[0009] Optionally, setting human posture boundaries includes: determining the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple preset human posture scenarios, wherein the human posture scenarios include at least standing, squatting and leaning postures; and determining the human posture boundaries according to the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple human posture scenarios.

[0010] Optionally, based on the parameters of the interference source in the wireless charging of electric vehicles and the human posture boundary, the magnetic flux density on the surface of the cochlear implant magnet is simulated and calculated using a time-domain solver according to the coupled model, and the interference signal is extracted. This includes: setting multiple monitoring points on the surface of the cochlear implant magnetic component in the coupled model; simulating the model using a time-domain solver and recording the instantaneous values ​​of the magnetic flux density corresponding to each of the multiple monitoring points during the simulation process, determining the maximum value of the magnetic flux density corresponding to each of the multiple monitoring points and obtaining the output data of the time-domain solver; determining the magnetic flux density on the surface of the cochlear implant magnet based on the maximum value of the magnetic flux density corresponding to each of the multiple monitoring points; and extracting the voltage waveform induced in the cochlear implant coil based on the output data of the time-domain solver to determine the interference signal.

[0011] Optionally, the impact of wireless charging of electric vehicles on cochlear implants is determined based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset, including: comparing the current amplitude with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing hearing abnormalities, and obtaining a first judgment result; comparing the current amplitude corresponding to the audible frequency band with a preset hearing perception threshold to determine whether there is a risk of noise interference, and obtaining a second judgment result; comparing the offset with a preset allowable offset range to determine whether there is a risk of damage to signal processing accuracy, and obtaining a third judgment result; and generating an impact result based on the first judgment result, the second judgment result, and the third judgment result.

[0012] Optionally, if the result results in impaired signal processing accuracy, an anti-interference filtering scheme is set up, wherein the anti-interference filtering scheme includes setting a bandpass filter and a high-pass filter at the front end of the signal processing unit of the cochlear implant.

[0013] According to another aspect of the present invention, an electromagnetic influence determination device for a cochlear implant is also provided, comprising: an acquisition module for acquiring electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles; a first construction module for calibrating the electromagnetic parameters of brain tissue and constructing a coupling model based on the frequency information, wherein the coupling model includes a cochlear implant and a human head structure; a setting module for setting parameters of the interference source of the wireless charging for electric vehicles and human posture boundaries; and a calculation module for simulating and calculating the cochlear implant magnet surface using a time-domain solver based on the parameters of the interference source of the wireless charging for electric vehicles and the human posture boundaries, according to the coupling model. The system comprises the following modules: a first module for determining the magnetic field strength of the surface and extracting interference signals; a second module for constructing a transcutaneous energy transfer circuit model of the cochlear implant based on a coupling model; a simulation module for injecting interference signals into the transcutaneous energy transfer circuit model of the cochlear implant and performing simulation to determine the receiving coil current and load voltage; a first determination module for determining the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by the interference signal to the static operating point of the circuit based on the receiving coil current and load voltage; and a second determination module for determining the impact of wireless charging of electric vehicles on the cochlear implant based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset.

[0014] According to another aspect of the present invention, a non-volatile storage medium is also provided, the non-volatile storage medium including a stored program, wherein, when the program is running, the device where the non-volatile storage medium is located is controlled to execute any of the above-described methods for determining the electromagnetic influence of a cochlear implant.

[0015] According to another aspect of the present invention, a computer device is also provided, the computer device including a processor, the processor being configured to run a program, wherein the program, when running, executes any of the above-described methods for determining the electromagnetic influence of a cochlear implant.

[0016] According to another aspect of the present invention, a computer program product is also provided, including a computer program that, when executed by a processor, implements any of the above-described methods for determining the electromagnetic influence of a cochlear implant.

[0017] In this embodiment of the invention, a method for determining the electromagnetic influence of a cochlear implant is employed. This involves acquiring electromagnetic parameters of brain tissue and frequency information from wireless charging of an electric vehicle. Based on the frequency information, the electromagnetic parameters of the brain tissue are calibrated, and a coupling model is constructed. This coupling model includes the cochlear implant and the human head structure. Interference source parameters for the wireless charging of the electric vehicle and human posture boundaries are defined. Based on these parameters and the coupling model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated using a time-domain solver, and the interference signal is extracted. A transcutaneous energy transfer circuit model of the cochlear implant is constructed based on the coupling model. The interference signal is then injected into the transcutaneous energy transfer circuit model of the cochlear implant and simulated. The method involves determining the receiving coil current and load voltage; based on the receiving coil current and load voltage, determining the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by interference signals to the circuit's static operating point; and determining the impact of electric vehicle wireless charging on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset. This achieves the goal of scientifically and comprehensively evaluating the electromagnetic interference impact on cochlear implants in electric vehicle wireless charging scenarios, thus providing a quantitative basis for the design of cochlear implants to resist electromagnetic interference. Furthermore, it solves the technical problem of the current lack of a method to determine the impact of electromagnetic interference on cochlear implants in electric vehicle wireless charging scenarios, which makes it difficult to subsequently adjust cochlear implants to resist electromagnetic interference. Attached Figure Description

[0018] The accompanying drawings, which are included to provide a further understanding of the invention and form part of this application, illustrate exemplary embodiments of the invention and, together with their description, serve to explain the invention and do not constitute an undue limitation thereof. In the drawings:

[0019] Figure 1 A hardware block diagram of a computer terminal for implementing a method for determining the electromagnetic effects of a cochlear implant is shown.

[0020] Figure 2 This is a flowchart illustrating the method for determining the electromagnetic influence of a cochlear implant according to an embodiment of the present invention.

[0021] Figure 3 This is a structural block diagram of the electromagnetic influence determination device for cochlear implants provided in an embodiment of the present invention. Detailed Implementation

[0022] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0023] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this invention are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of the invention described herein can be implemented in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0024] According to an embodiment of the present invention, a method embodiment for determining the electromagnetic influence of a cochlear implant is provided. It should be noted that the steps shown in the flowchart in the accompanying drawings can be executed in a computer system such as a set of computer-executable instructions. Furthermore, although a logical order is shown in the flowchart, in some cases, the steps shown or described may be executed in a different order than that shown here.

[0025] The methods and embodiments provided in this application can be executed on mobile terminals, computer terminals, or similar computing devices. Figure 1 A hardware block diagram of a computer terminal for implementing a method to determine the electromagnetic effects of a cochlear implant is shown. Figure 1 As shown, the computer terminal 10 may include one or more processors (shown as 102a, 102b, ..., 102n in the figure) (the processor may include, but is not limited to, a microprocessor MCU or a programmable logic device FPGA, etc.) and a memory 104 for storing data. In addition, it may also include: a display, an input / output interface (I / O interface), a universal serial bus (USB) port (which may be included as one of the ports of a BUS bus), a network interface, a power supply, and / or a camera. Those skilled in the art will understand that... Figure 1 The structure shown is for illustrative purposes only and does not limit the structure of the aforementioned electronic device. For example, computer terminal 10 may also include... Figure 1 The more or fewer components shown, or having the same Figure 1 The different configurations shown.

[0026] It should be noted that the aforementioned one or more processors and / or other data processing circuits are generally referred to herein as "data processing circuits". These data processing circuits may be embodied, in whole or in part, in software, hardware, firmware, or any other combination thereof. Furthermore, the data processing circuits may be a single, independent processing module, or may be integrated, in whole or in part, into any other element within the computer terminal 10. As involved in the embodiments of this application, the data processing circuits serve as a processor control mechanism (e.g., selection of a variable resistor termination path connected to an interface).

[0027] The memory 104 can be used to store software programs and modules of application software, such as the program instructions / data storage device corresponding to the method for determining the electromagnetic influence of a cochlear implant in this embodiment of the invention. The processor executes various functional applications and data processing by running the software programs and modules stored in the memory 104, thereby implementing the aforementioned application method for determining the electromagnetic influence of a cochlear implant. The memory 104 may include high-speed random access memory and may also include non-volatile memory, such as one or more magnetic storage devices, flash memory, or other non-volatile solid-state memory. In some instances, the memory 104 may further include memory remotely located relative to the processor, and these remote memories can be connected to the computer terminal 10 via a network. Examples of such networks include, but are not limited to, the Internet, corporate intranets, local area networks, mobile communication networks, and combinations thereof.

[0028] The display can be, for example, a touchscreen liquid crystal display (LCD) that allows the user to interact with the user interface of the computer terminal 10.

[0029] Figure 2 This is a flowchart illustrating a method for determining the electromagnetic influence of a cochlear implant according to an embodiment of the present invention, as shown below. Figure 2 As shown, the method includes the following steps:

[0030] Step S202: Obtain electromagnetic parameters of brain tissue and frequency information for wireless charging of electric vehicles.

[0031] In this step, we acquire electromagnetic parameters of brain tissue and frequency information for wireless charging of electric vehicles to provide fundamental data support for subsequent electromagnetic interference impact assessment. By considering the mainstream frequency band for wireless charging of electric vehicles (80kHz-90kHz), 85kHz is selected as the core analysis frequency, covering most commercial equipment scenarios. Then, based on IEEE StdC95.3-2002 and the IT'IS Database, we determine the electromagnetic parameters of brain tissue at 85kHz, including relative permittivity, conductivity, and density, while controlling the parameter error within 5%. Acquiring the electromagnetic parameters of brain tissue ensures that the electromagnetic characteristics of the human head tissue in the simulation model are consistent with the actual physiological structure, while clarifying the frequency information of wireless charging of electric vehicles identifies the operating frequency band of the interference source. The combination of these two provides accurate parameter basis for constructing the "human-cochlear implant" coupling model and subsequent magnetic induction intensity simulation, thereby ensuring the scientific validity and reliability of the evaluation results.

[0032] Step S204: Based on frequency information, the electromagnetic parameters of brain tissue are calibrated and a coupling model is constructed, wherein the coupling model includes the cochlear implant and the human head structure.

[0033] In this step, the electromagnetic parameters of brain tissue are calibrated based on pre-determined core analysis frequency information, and a coupled model including the cochlear implant structure and the human head structure is constructed on this basis. 85kHz is selected as the core analysis frequency by referencing the mainstream frequency band for wireless charging of electric vehicles. The relative permittivity, conductivity, and other electromagnetic parameters of brain tissue at this frequency are determined according to relevant standards and databases, with parameter errors controlled within 5% to ensure the reliability of simulation accuracy. Subsequently, a three-dimensional solid model of the cochlear implant is drawn based on measured data from commercial products, clarifying key dimensions such as its shell and coil, as well as material parameters such as TC4 titanium alloy and medical PDMS. This cochlear implant model is then assembled into the human head anatomical model according to the clinical implantation location, forming a complete human-cochlear implant coupled model.

[0034] Specifically, referring to the measured data of a commercial cochlear implant product, the key dimensions of the model were determined. For example, the overall shell dimensions are: length 40mm ± 0.5mm, width 22mm ± 0.3mm, and height 6.5mm ± 0.2mm; the wireless transmission coil uses enameled copper wire with a diameter of 0.2mm ± 0.01mm, 10 turns, an inner diameter of 8mm ± 0.1mm, and an outer diameter of 12mm ± 0.1mm; the shell and magnet are made of TC4 titanium alloy, with the following electromagnetic parameters: relative permittivity 1, conductivity 1.7 × 10⁻⁶. 6 S / m, permeability 1.0003; the filled silicone rubber uses medical-grade PDMS, with a relative permittivity of 3.2±0.1 and conductivity of 1×10. - ¹ 4S / m, density 970kg / m³; construct a three-dimensional solid model of the cochlear implant, first draw sketches of the shell, magnet and coil respectively, and perform Boolean operations according to the actual assembly relationship (the coil is embedded in the groove of the magnet and the gap is filled with silicone rubber).

[0035] The CST-provided "Adult Head Anatomy Model" was used. This model includes 12 layers of anatomical structures, such as skin, skull, brain tissue, and cerebrospinal fluid. The electromagnetic parameters of each layer were preset and conformed to international standards. Referring to the conventional location for cochlear implantation surgery in clinical practice (below the mastoid region behind the ear, approximately 30mm from the external auditory canal opening and approximately 5mm from the skull surface), the cochlear implant model was assembled into the corresponding position on the human head model using coordinate positioning, with the assembly error controlled within ±1mm. By comparing the distance between the center of the cochlear implant coil and the brain tissue in the model (measured value 5mm±0.5mm) and the fit between the outer shell and the skin surface (gap ≤0.3mm), the consistency between the model and the actual implantation scenario was ensured. At the same time, the percutaneous energy transfer efficiency of the model under interference-free conditions was calculated (should be ≥75%, consistent with the actual product specifications) to verify the functionality of the model.

[0036] The construction of this coupling model realizes the precise spatial correlation between the cochlear implant and the human head structure, providing accurate basic model support for subsequent quantitative assessment of the interference effects on the cochlear implant under specific electromagnetic environments.

[0037] Step S206: Set the parameters of the wireless charging interference source for electric vehicles and the human posture boundary.

[0038] In this step, key electrical parameters of the charging system are determined according to standard specifications. These include setting the charging power to 11kW, constructing a circular planar coil model with a diameter of 300mm ± 5mm, 15 turns, and a wire diameter of 2mm, and setting the coil center height above the ground to 150mm ± 5mm. Based on near-field radiation characteristics, the electromagnetic field within a 1m radius of the coil center is determined to be predominantly magnetic, thus quantifying the physical properties and radiation patterns of interference sources. Subsequently, by dividing the simulation into three specific scenarios—standing, squatting, and leaning-out inspection postures—the horizontal and vertical distances of the human head center relative to the charging coil center, as well as the angle between the body and the charging coil plane, are defined to quantify the spatial positional relationships under different usage postures. Furthermore, by setting a 5m cube simulation space and applying absorbing boundary conditions, the ambient temperature is controlled at 25℃ and the humidity at 50% to eliminate environmental interference with electromagnetic field propagation and the simulation of human tissue parameters. By comprehensively setting the electrical parameters, geometric structure, radiation mode, human posture and spatial position, and simulation environment boundary conditions of the interference source, an electromagnetic simulation environment with clear boundary conditions that conforms to actual use scenarios is constructed, providing a standardized input benchmark for subsequent monitoring of magnetic induction intensity and interference analysis of energy transmission circuits.

[0039] Step S208: Based on the parameters of the interference source of the electric vehicle wireless charging and the human body posture boundary, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated by a time-domain solver according to the coupled model, and the interference signal is extracted.

[0040] In this step, based on the parameters of the interference source in the electric vehicle wireless charging system and the human posture boundary, and combined with the previously constructed human-cochlear implant coupling model, a time-domain solver is used for simulation calculations. Specifically, the electromagnetic field characteristics of the electric vehicle wireless charging system (such as power, coil size, and current excitation) and the spatial positional relationships of different human postures (such as standing, squatting, and leaning-out examination postures) are used as input conditions to drive the coupling model in the simulation environment, focusing on monitoring and calculating the magnetic induction intensity distribution on the surface of the cochlear implant magnet. Through this time-domain simulation process, the instantaneous and maximum values ​​of the magnetic induction intensity at each monitoring point on the surface of the magnet outside and inside the cochlear implant can be obtained under specific electromagnetic interference scenarios, thereby quantitatively assessing the degree of influence of the electromagnetic environment on the implanted device. Based on this, the interference signal induced in the cochlear implant coil by the interference source is extracted from the simulation results, providing data support for subsequent analysis of the specific impact of the interference signal on the energy transmission circuit and signal processing system.

[0041] Step S210: Based on the coupling model, construct the transcutaneous power transmission circuit model of the cochlear implant.

[0042] In this step, a transcutaneous cochlear implant power transfer circuit model is first constructed based on the previously established human-cochlear implant coupling model. This coupling model includes the spatial geometric relationship and electromagnetic characteristics of human tissue, the cochlear implant, and its external components. Circuit modeling is then performed based on this model, aiming to transform the electromagnetic coupling relationship in physical space into electrical parameters (such as mutual inductance and parasitic capacitance) and transmission characteristics at the circuit level, thereby achieving quantitative evaluation and simulation verification of the electrical behavior of the transcutaneous power transfer system.

[0043] Specifically, the string-compensated magnetic coupling resonant topology has the characteristics of "strong resistance to load changes and high transmission efficiency", which is suitable for transcutaneous energy transmission in cochlear implants (which requires stable power supply). Therefore, this topology was selected as the core solution. Referring to the commonly used transcutaneous transmission frequency (4MHz-6MHz) of cochlear implants, 5MHz was selected as the resonant frequency. At this frequency, the electromagnetic loss of human tissue is relatively small (attenuation rate ≤10%). Through CST simulation, in the coupling model, a sinusoidal voltage (amplitude 5V) of 5MHz was applied to the transmitting coil, and the induced voltage of the receiving coil was measured. According to the formula M=U2 / (2πfI1) (U2 is the induced voltage of the receiving coil, f is the frequency, and I1 is the current of the transmitting coil), the mutual inductance M=1.63μH±0.02μH was calculated. According to the resonance condition ωL=1 / (ωC), where ω=2πf, L is the coil inductance, and the coil inductance L1=L2=10μH±0.5μH (measured value), substituting f=5MHz, the compensation capacitor C1=C2=3nF±0.05nF was calculated. Construct a series-compensated magnetically coupled resonant circuit, including a transmitter (signal source, compensation capacitor C1, transmitting coil L1) and a receiver (receiving coil L2, compensation capacitor C2, load resistor R_L), with the load resistor R_L=1kΩ (simulating the input impedance of the stimulator in the cochlear implant).

[0044] Step S212: Inject the interference signal into the transcutaneous energy transfer circuit model of the cochlear implant and perform simulation to determine the receiving coil current and load voltage.

[0045] In this step, the interference signal is injected into the transcutaneous power transfer circuit model of the cochlear implant and simulated to determine the receiving coil current and load voltage. A series-compensated magnetically coupled resonant circuit model is constructed, including a transmitter (signal source, compensation capacitor, transmitting coil) and a receiver (receiving coil, compensation capacitor, load resistor). Simulating a real-world working scenario, the extracted interference signal source is injected in parallel next to the transmitter signal source to simulate the interference signal superimposed on the normal power supply signal. Time-domain simulation calculations are then performed to obtain the current waveform of the receiving coil and the voltage waveform across the load resistor, thereby quantitatively evaluating the specific impact of the interference signal on the power transfer circuit.

[0046] Step S214: Based on the receiving coil current and load voltage, determine the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by the interference signal to the static operating point of the circuit.

[0047] In this step, based on the receiving coil current and load voltage, the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by the interference signal to the circuit's static operating point are determined. Specifically, the maximum current amplitude is extracted by acquiring the current waveform data of the receiving coil; simultaneously, a frequency domain analysis of the receiving coil's current waveform is performed using a Fast Fourier Transform to calculate and determine the corresponding current amplitude within the audible frequency band; furthermore, the offset caused by the interference signal to the circuit's static operating point is determined by comparing the operating point of the amplifier circuit under interference conditions with its operating point under normal conditions.

[0048] Step S216: Determine the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset.

[0049] In this step, based on the key data obtained from the aforementioned simulation analysis, a comprehensive assessment is made of the specific impact of electromagnetic interference generated by wireless charging of electric vehicles on cochlear implants. Specifically, by extracting the peak value of the interference current in the receiving coil and comparing it with the current pulse range (10μA-2mA) required for normal operation of the cochlear implant, it is confirmed that the peak value of the interference current (2.1μA±0.1μA) is much lower than the minimum value of the normal operating current (10μA), thus determining that the interference current will not directly trigger the stimulation response of the auditory nerve fibers, i.e., it will not cause hearing abnormalities. At the same time, combined with the frequency domain analysis results obtained by Fast Fourier Transform (FFT), it is analyzed whether the current amplitude in the audible sound band of 20Hz-20kHz is within the safe threshold. In addition, the static operating point offset (0.02V, offset rate 4%) caused by the 85kHz interference signal coupling to the amplifier circuit is evaluated to determine its potential impact on the signal amplification accuracy. Finally, the above current amplitude comparison results, the current amplitude characteristics in the audible sound band, and the operating point offset are used as the judgment criteria to draw the final conclusion on the impact of wireless charging of electric vehicles on cochlear implants in this scenario.

[0050] As an optional embodiment, the electromagnetic parameters of brain tissue are calibrated and a coupled model is constructed based on frequency information, including: determining the operating frequency band for wireless charging of electric vehicles based on frequency information; selecting a target frequency within the operating frequency band as the core analysis frequency; obtaining electromagnetic parameter verification data at the core analysis frequency according to a preset standard; comparing the electromagnetic parameters of brain tissue with the electromagnetic parameter verification data to determine the deviation value; calibrating the electromagnetic parameters of brain tissue using interpolation if the deviation value exceeds a preset error range to obtain calibrated electromagnetic parameters of brain tissue; and constructing a coupled model based on the calibrated electromagnetic parameters of brain tissue and the preset structural parameters of the cochlear implant.

[0051] Optionally, technical standards or measured data of electric vehicle wireless charging systems can be obtained to determine their mainstream operating frequency band. For example, referring to the GB / T38775 series standards, electric vehicle wireless charging systems typically operate in the 80kHz-90kHz frequency band. This band covers the operating frequencies of most commercial wireless charging devices currently on the market and has broad representativeness. After determining the operating frequency band, the center frequency or the most representative frequency within this band is selected as the core analysis frequency. For example, the center frequency of the 80kHz-90kHz band, 85kHz, is selected as the core analysis frequency. The reason for choosing this frequency as the core analysis frequency is that, on the one hand, 85kHz is in the middle of the wireless charging frequency band, which can better cover the electromagnetic field distribution characteristics within this band; on the other hand, at this frequency, the electromagnetic characteristics of human tissue are relatively stable, which facilitates parametric analysis.

[0052] To assess the accuracy of the electromagnetic parameters of brain tissue, reference baseline data is required. Based on pre-defined standards, such as other published literature, reference values ​​for the electromagnetic parameters of the target brain tissue at the core analysis frequency (85 kHz) are searched or retrieved. These reference values ​​include relative permittivity, conductivity, and density, determining the electromagnetic parameter validation data. The brain tissue electromagnetic parameters are compared with the validation data; if the deviation exceeds 5%, interpolation is used for correction to obtain calibrated brain tissue electromagnetic parameters. Based on the calibrated brain tissue electromagnetic parameters and the pre-defined structural parameters of the cochlear implant, a coupled model is constructed. A human head anatomical model (such as the adult head model included with CST) containing multiple layers of anatomical structures including skin, skull, brain tissue, and cerebrospinal fluid can be used. The calibrated brain tissue electromagnetic parameters are assigned to the corresponding brain tissue layers in the model, replacing the original default parameters, thus obtaining a high-fidelity human head electromagnetic model. Then, based on the pre-defined structural parameters of the cochlear implant (including shell size, material, number of coil turns, wire diameter, magnet position, etc.), a three-dimensional solid model of the cochlear implant is created using 3D modeling software. The 3D model of the cochlear implant was assembled into the human head anatomical model according to the clinical implantation site. During assembly, it was ensured that the cochlear implant shell fit tightly against the skin surface, with the gap error controlled within ±1mm. Under interference-free conditions, the transcutaneous energy transmission efficiency of the cochlear implant was simulated and calculated. If the efficiency was ≥75% (meeting the specifications of commercial products), the coupling model was confirmed to be successfully constructed and could be used for subsequent electromagnetic interference simulation analysis.

[0053] Through the above steps, this embodiment achieves scientific calibration of electromagnetic parameters of brain tissue and constructs a high-precision human-artificial cochlear coupling model, laying a model foundation for subsequent accurate assessment of the electromagnetic interference effects generated by wireless charging of electric vehicles.

[0054] As an optional embodiment, setting human posture boundaries includes: determining the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple preset human posture scenarios, wherein the human posture scenarios include at least standing, squatting, and leaning postures; and determining the human posture boundaries according to the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple human posture scenarios.

[0055] Optionally, based on the typical usage environment and user behavior habits of electric vehicle wireless charging systems, at least three representative human posture scenarios are preset: standing, squatting, and leaning forward. For each posture scenario, the spatial coordinates and angular relationship of the human head relative to the charging coil are defined, with specific quantitative definitions as follows:

[0056] Standing posture scenario: This simulates a user standing next to a vehicle preparing for or waiting to charge. In this scenario, the horizontal distance (i.e., the projected distance on a horizontal plane) between the center of the human head and the center of the charging coil is defined as the first preset distance range, and the vertical distance (i.e., the height difference) is defined as the second preset distance range. Simultaneously, the angle between the human torso axis and the charging coil plane is defined as the third preset angle range. For example, in practical applications, the standing posture scenario can be set as follows: the horizontal distance between the center of the human head and the center of the charging coil is 1500mm ± 50mm, the vertical distance is 1600mm ± 50mm (based on average adult height), and the body is approximately perpendicular to the charging coil plane with an angle of 90° ± 5°.

[0057] Squatting Scenario: This simulates a user squatting down to check the charging port or place a charging device. In this scenario, both the horizontal and vertical distances between the center of the user's head and the center of the charging coil are significantly reduced. The horizontal distance between the center of the user's head and the center of the charging coil is defined as the fourth preset distance range, and the vertical distance as the fifth preset distance range. Simultaneously, the angle between the user's torso axis and the charging coil plane is defined as the sixth preset angle range. For example, in practical applications, the squatting scenario can be set as follows: the horizontal distance between the center of the user's head and the center of the charging coil is 800mm ± 30mm, the vertical distance is 800mm ± 30mm, the body is leaning forward or bent, and the angle between the body and the charging coil plane is 60° ± 5°.

[0058] Leaning Forward Posture Scenario: This simulates a user leaning forward to observe or operate the charging port at a closer distance. This scenario is generally considered a critical scenario with a high risk of electromagnetic interference. In this scenario, the horizontal and vertical distances between the center of the user's head and the center of the charging coil are further reduced, and the head is tilted towards the charging coil plane. The horizontal distance between the center of the user's head and the center of the charging coil is defined as the seventh preset distance range, and the vertical distance as the eighth preset distance range. Simultaneously, the angle between the head axis or the direction of the body's forward tilt and the charging coil plane is defined as the ninth preset angle range. For example, in practical applications, the leaning forward posture scenario can be set as follows: the horizontal distance between the center of the user's head and the center of the charging coil is 300mm ± 20mm, the vertical distance is 500mm ± 20mm, the body is tilted forward significantly, and the angle between the head and the charging coil plane is 30° ± 5°.

[0059] Based on the spatial coordinates and angular relationships of the human head relative to the charging coil in multiple defined human posture scenarios, the human posture boundaries in the simulation space are determined. Specifically, the human posture boundaries refer to the transformation of the spatial position and angular relationships of the human head in each posture into geometric constraints in the simulation model. In electromagnetic simulation software, abstract distance and angle parameters can be mapped to three-dimensional coordinate points in the simulation space, determining the unique position of the human head model in the simulation space. By using rotation matrices or Euler angles, the human head model is adjusted to the corresponding angular relationships, ensuring that the orientation of the head relative to the charging coil plane conforms to the actual posture. For each posture scenario, a virtual bounding box or mesh region surrounding the human body and cochlear implant model is defined as the boundary of the simulation computation domain for that specific posture. These boundaries ensure that the relative positions of the human body model and the charging coil model are fixed during the simulation, thereby enabling accurate calculation of the near-field electromagnetic coupling effect in specific postures.

[0060] In addition to defining the human body posture boundaries, environmental boundary conditions for the entire simulation scene must be set to eliminate interference from the external environment on the electromagnetic field distribution. The simulation space is defined as a closed cubic region (e.g., with a side length of 5m), and the surface of this cube is set as an absorbing boundary condition to simulate infinite free space, preventing electromagnetic waves from reflecting at the boundaries and interfering with the simulation results. Simultaneously, the ambient temperature is set to 25℃ and the relative humidity to 50% to eliminate the minor effects of temperature and humidity changes on the electromagnetic parameters of air and tissues.

[0061] Through the above steps, this embodiment establishes human posture boundaries for multiple scenarios, including standing, squatting, and leaning postures, providing a standardized geometric model basis for accurately calculating the magnetic induction intensity and induced interference signals at the cochlea in different spatial locations.

[0062] As an optional embodiment, based on the interference source parameters of electric vehicle wireless charging and the human body posture boundary, according to the coupled model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated using a time-domain solver, and the interference signal is extracted. This includes: setting multiple monitoring points on the surface of the cochlear implant magnetic component in the coupled model; simulating using a time-domain solver and recording the instantaneous values ​​of the magnetic induction intensity corresponding to each of the multiple monitoring points during the simulation process, determining the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points and obtaining the output data of the time-domain solver; determining the magnetic induction intensity on the surface of the cochlear implant magnet based on the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points; and extracting the voltage waveform induced in the cochlear implant coil based on the output data of the time-domain solver to determine the interference signal.

[0063] Optionally, to comprehensively evaluate the magnetic field distribution on the surface of the cochlear implant magnet, multiple monitoring points need to be precisely set on the surface of the magnetic component of the cochlear implant in the coupled model. The monitoring points should cover key areas of the magnet, typically including points evenly distributed at the geometric center and edges. For example, three monitoring points (one center point and two edge points) can be set on the surface of the external magnet, and three corresponding monitoring points can be set on the surface of the internal magnet. The spatial coordinates of each monitoring point are precisely located using the local coordinate system of the coupled model, ensuring that the monitoring point is always attached to the magnet surface and moves with the model. For example, the coordinates of the external center monitoring point can be defined as specific X, Y, and Z values ​​in the model coordinate system. The monitoring type is set as "FieldMonitor" in the simulation software, and it is configured to record the vector magnetic flux density that changes over time. Simulation is performed using a time-domain solver, and during the simulation, the instantaneous values ​​of the magnetic flux density corresponding to each of the multiple monitoring points are recorded. The maximum value of the magnetic flux density corresponding to each of the multiple monitoring points is determined, and the output data of the time-domain solver is obtained. The simulation frequency is set to the center analysis frequency (e.g., 85kHz), the simulation time is set long enough to ensure the electromagnetic field reaches a steady state (e.g., 10ms), and the sampling interval is set small enough to capture high-frequency details (e.g., 0.1ms). During the simulation, the time-domain solver calculates the electromagnetic field distribution at each point in space step by step according to Maxwell's equations. For multiple monitoring points, the solver records the instantaneous magnetic flux density (MFD) at each monitoring point at each time step in real time. After the simulation, the processor performs statistical analysis on the instantaneous value sequence recorded for each monitoring point and calculates the maximum MFD at that monitoring point within the simulation time window. The time-domain solver summarizes the instantaneous MFD value sequences, maximum values, and other field distribution data (such as electric field distribution, S-parameters, etc.) of all monitoring points into a simulation output data file (e.g., .CSV or binary data file) for subsequent analysis.

[0064] Then, based on the maximum magnetic flux density obtained at each monitoring point, the overall magnetic flux density level on the surface of the cochlear implant magnet is determined. The maximum magnetic flux density at all monitoring points (external and internal) is compared, and the highest value is selected as the highest magnetic flux density on the surface of the cochlear implant magnet in that posture. The highest magnetic flux density is compared with the magnetic flux density limit for implantable medical devices specified in relevant standards (e.g., ≤1 μT) in GB / T 38775.4-2020. If the highest magnetic flux density exceeds the limit, a biosafety risk is identified for that posture. By comparing the highest magnetic flux density under different human postures (standing, squatting, and leaning posture), the key posture scenario with the highest magnetic flux density (usually the leaning posture) can be identified as the focus scenario for subsequent interference signal extraction.

[0065] To assess the impact of electromagnetic interference on the function of the cochlear implant circuitry, it is necessary to extract the interference signal from the simulation output data. In the coupled model, the cochlear implant's receiving coil is typically defined as an electromagnetic port or connected as a lumped element. In the simulation of step S302, the solver not only records the magnetic field but also calculates the voltage and current at the port. From the output data of the time-domain solver, waveform data of the induced voltage at the cochlear implant's receiving coil port changing over time is extracted. This waveform reflects the induced electromotive force generated in the coil by the external wireless charging magnetic field. The extracted waveform is considered as the interference signal generated by the wireless charging of electric vehicles. This interference signal contains amplitude, frequency (mainly the center frequency of 85kHz and its harmonics), and phase information.

[0066] Through the above steps, this embodiment utilizes a time-domain solver to achieve a complete conversion from spatial magnetic field distribution to circuit interference signals. This not only assesses the safety of the electromagnetic field but also quantifies the potential interference to the circuit, providing accurate data support for subsequent filtering optimization.

[0067] As an optional embodiment, the impact of wireless charging of electric vehicles on cochlear implants is determined based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset. This includes: comparing the current amplitude with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing hearing abnormalities, thus obtaining a first judgment result; comparing the current amplitude corresponding to the audible sound frequency band with a preset auditory perception threshold to determine whether there is a risk of noise interference, thus obtaining a second judgment result; comparing the offset with a preset allowable offset range to determine whether there is a risk of damage to signal processing accuracy, thus obtaining a third judgment result; and generating an impact result based on the first, second, and third judgment results.

[0068] Optionally, the current amplitude is compared with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing auditory abnormalities, thus obtaining a first judgment result. First, the amplitude of the interference current (i.e., the peak or effective value of the interference current) generated in the receiving coil after the interference signal is injected into the cochlear implant's energy transmission circuit is acquired. Based on the clinical stimulation parameter standards for cochlear implants, a minimum stimulation current threshold is set. This threshold is lower than the minimum pulse current corresponding to a normal speech signal (for example, if the current range of a normal speech signal is 10μA-2mA, then the minimum stimulation current threshold can be set slightly lower than 10μA, such as 5μA), representing the minimum current threshold that can directly activate auditory nerve fibers to generate auditory perception. The simulated interference current amplitude is compared with the minimum stimulation current threshold. If the interference current amplitude is not lower than the minimum stimulation current threshold, it is determined that the interference current is sufficient to directly stimulate the auditory nerve, posing a risk of directly causing auditory abnormalities (such as auditory hallucinations or false triggering), and the first judgment result is "high risk." Conversely, it is determined that the interference current is insufficient to directly activate the auditory nerve, and there is no risk of directly causing auditory abnormalities, and the first judgment result is "low risk" or "safe."

[0069] The current amplitude corresponding to the audible frequency band is compared with a preset auditory perception threshold to determine if there is a risk of noise interference, resulting in a second judgment result. To assess whether the interference will be perceived as noise by the patient, frequency domain analysis of the interference signal is required to extract its energy within the human audible frequency band. A Fast Fourier Transform (FFT) is performed on the total current waveform in the receiving coil to obtain the current spectrum. The current amplitude within the preset audible frequency band (e.g., 20Hz-20kHz) is extracted. A preset auditory perception threshold is set. This threshold represents the minimum background noise current level that the patient can subjectively perceive, typically much lower than normal speech signals but higher than the noise floor. The current amplitude corresponding to the audible frequency band is compared with the preset auditory perception threshold. If the current amplitude corresponding to the audible frequency band is not lower than the preset auditory perception threshold, the interference signal is determined to have high energy within the audible frequency band and may be perceived as a "buzzing" sound or other noise by the patient; the second judgment result is "there is a risk of noise interference." If the current amplitude corresponding to the audible frequency band is lower than the preset auditory perception threshold, it is determined that the interference signal has extremely low energy within the audible frequency band and cannot be perceived by the patient. The second judgment result is "no risk of noise interference".

[0070] Obtain the offset: From the circuit simulation results, obtain the voltage offset of the amplifier circuit's static operating point caused by interference signal injection. For example, if the normal operating point is 0.5V and becomes 0.52V after interference, the offset is 0.02V. Set a preset allowable offset range. This range is determined based on the linear operating range and signal-to-noise ratio requirements of the cochlear implant signal processing chip. For example, the allowable offset range is ±0.01V. Compare the absolute offset with the upper limit of the preset allowable offset range. If the absolute offset exceeds the preset allowable offset range, it is determined that the amplifier circuit may have entered the nonlinear region or saturation region, leading to signal distortion, gain changes, and a risk of impaired signal processing accuracy. The third judgment result is "risk of impaired signal processing accuracy". If the absolute offset is within the preset allowable offset range, it is determined that the circuit operating point remains stable and the signal processing accuracy is not significantly affected. The third judgment result is "no risk of impaired signal processing accuracy".

[0071] Based on the first, second, and third judgment results, an impact result is generated. If the first judgment result is "high risk," the overall impact result is "serious safety risk," and it is recommended to immediately stop charging or take emergency shielding measures. If the first judgment result is "safe," but the second judgment result is "risk of noise interference," the overall impact result is "impaired auditory experience," and it is recommended to optimize the filtering circuit to reduce noise in the audible frequency band. If the first judgment result is "safe," the second judgment result is "no risk of noise interference," but the third judgment result is "risk of impaired signal processing accuracy," the overall impact result is "potential risk to circuit performance," and it is recommended to optimize the analog front-end circuit or add decoupling capacitors to improve anti-interference capability. If all three results are "safe / no risk," the overall impact result is "safe and usable."

[0072] Through the above steps, this embodiment achieves a refined and multi-dimensional assessment of the impact of wireless charging interference on electric vehicles. It not only focuses on biosafety but also takes into account auditory experience and device functional stability, providing a scientific basis for the anti-interference design of cochlear implants.

[0073] As an optional embodiment, when the result results in impaired signal processing accuracy, an anti-interference filtering scheme is set up, wherein the anti-interference filtering scheme includes setting a bandpass filter and a high-pass filter at the front end of the signal processing unit of the cochlear implant.

[0074] Optionally, when the results indicate that the cochlear implant poses a risk of "damaged signal processing accuracy" (i.e., the static operating point of the amplifier circuit deviates beyond the allowable range, or high-frequency interference signals are coupled to the signal processing link), a combination of "bandpass filtering + high-pass filtering" can be used. This scheme aims to preserve the effective cochlear implant speech / energy transmission signal while significantly attenuating the 85kHz interference signal generated by wireless charging of electric vehicles.

[0075] Based on the characteristics of cochlear implant signal processing and the features of interference signals (85kHz high-frequency sinusoidal interference), a cascaded topology of "bandpass filter + high-pass filter" is designed:

[0076] A band-pass filter (BPF) primarily filters out low-frequency noise (such as power line interference and baseband drift) and extremely high-frequency broadband noise, allowing only the main frequency bands of the cochlear implant's speech signal to pass through. An active RC band-pass filter can be used. An active structure is chosen because it features high input impedance, low output impedance, and controllable gain, making it suitable for the low power consumption and high linearity requirements of implantable or miniaturized medical devices. Based on the range of human hearing and the cochlear implant coding strategy, the passband frequency range is set to 1kHz-20kHz. This range covers the vast majority of the effective frequency components of the speech signal.

[0077] A high-pass filter (HPF) is specifically designed to attenuate wireless charging interference signals at 85kHz. Since the interference frequency (85kHz) is much higher than the highest frequency of the voice signal (20kHz), setting a high-pass filter with a cutoff frequency below 85kHz but above 20kHz creates a deep attenuation band for the interference signal. A passive LC high-pass filter or a passive RC high-pass filter can be used. Considering the high frequency of 85kHz, LC filters have advantages in achieving a high Q value (selectivity) and a steeper roll-off characteristic, therefore an LC structure is preferred. The cutoff frequency is set to 25kHz. This frequency is slightly higher than the highest frequency of the voice signal (20kHz) to ensure that the voice signal passes through without phase distortion, while also providing a transition area for the stopband, ensuring efficient filtering of the 85kHz interference signal.

[0078] The designed filter module is integrated into the hardware circuitry of the cochlear implant. Specifically, the filter circuit can be placed at the front end of the cochlear implant signal processing unit, between the receiving coil (which receives transcutaneous energy and signals) and the main amplifier circuit (or the analog input of the decoding chip). Because interference signals first enter through coil induction, filtering them here can prevent interference signals from entering the subsequent high-gain amplification stage, avoiding amplifier saturation or operating point drift.

[0079] The above steps effectively solve the problem of impaired signal processing accuracy and ensure the stable operation of cochlear implants in environments with wireless charging interference and other interference.

[0080] It should be noted that, for the sake of simplicity, the foregoing method embodiments are all described as a series of actions. However, those skilled in the art should understand that the present invention is not limited to the described order of actions, because according to the present invention, some steps can be performed in other orders or simultaneously. Furthermore, those skilled in the art should also understand that the embodiments described in the specification are preferred embodiments, and the actions and modules involved are not necessarily essential to the present invention.

[0081] Through the above description of the embodiments, those skilled in the art can clearly understand that the method for determining the electromagnetic influence of cochlear implants according to the above embodiments can be implemented by means of software plus necessary general-purpose hardware platforms. Of course, it can also be implemented by hardware, but in many cases the former is a better implementation method. Based on this understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art, can be embodied in the form of a software product. This computer software product is stored in a storage medium (such as ROM / RAM, magnetic disk, optical disk) and includes several instructions to cause a terminal device (which may be a mobile phone, computer, server, or network device, etc.) to execute the methods described in the various embodiments of the present invention.

[0082] According to embodiments of the present invention, an electromagnetic influence determination device for cochlear implants is also provided for implementing the above-described method for determining the electromagnetic influence of cochlear implants. Figure 3 This is a structural block diagram of the electromagnetic influence determination device for cochlear implants provided in an embodiment of the present invention, as shown below. Figure 3 As shown, the electromagnetic influence determination device for the cochlear implant includes: an acquisition module 302, a first construction module 304, a setting module 306, a calculation module 308, a second construction module 310, a simulation module 312, a first determination module 314, and a second determination module 316. The electromagnetic influence determination device for the cochlear implant will be described below.

[0083] The acquisition module 302 is used to acquire electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles.

[0084] The first building module 304 is used to calibrate the electromagnetic parameters of brain tissue and build a coupling model based on frequency information, wherein the coupling model includes a cochlear implant and the human head structure.

[0085] The setting module 306 is used to set the parameters of the wireless charging interference source for electric vehicles and the human posture boundary.

[0086] The calculation module 308 is used to simulate and calculate the magnetic induction intensity on the surface of the cochlear implant magnet based on the parameters of the interference source of the electric vehicle wireless charging and the human body posture boundary, according to the coupled model, and extract the interference signal.

[0087] The second building module 310 is used to build a transcutaneous energy transfer circuit model for the cochlea based on the coupling model.

[0088] Simulation module 312 is used to inject interference signals into the transcutaneous energy transfer circuit model of the cochlear implant and perform simulation to determine the receiving coil current and load voltage.

[0089] The first determining module 314 is used to determine the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset of the circuit's static operating point caused by the interference signal based on the receiving coil current and the load voltage.

[0090] The second determining module 316 is used to determine the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset.

[0091] It should be noted that the aforementioned acquisition module 302, first construction module 304, setting module 306, calculation module 308, second construction module 310, simulation module 312, first determination module 314, and second determination module 316 correspond to steps S202 to S216 in the embodiments. Multiple modules and their corresponding steps implement the same instances and application scenarios, but are not limited to the content disclosed in the above embodiments. It should also be noted that the aforementioned modules, as part of the device, can run on the computer terminal 10 provided in the embodiments.

[0092] Embodiments of the present invention may provide a computer device. Optionally, in this embodiment, the computer device may be located in at least one of a plurality of network devices in a computer network. The computer device includes a memory and a processor.

[0093] The memory can be used to store software programs and modules, such as the program instructions / modules corresponding to the method and apparatus for determining the electromagnetic influence of a cochlear implant in this embodiment of the invention. The processor executes various functional applications and data processing by running the software programs and modules stored in the memory, thereby realizing the aforementioned method for determining the electromagnetic influence of a cochlear implant. The memory may include high-speed random access memory, and may also include non-volatile memory, such as one or more magnetic storage devices, flash memory, or other non-volatile solid-state memory. In some instances, the memory may further include memory remotely located relative to the processor, and these remote memories can be connected to a computer terminal via a network. Examples of such networks include, but are not limited to, the Internet, corporate intranets, local area networks, mobile communication networks, and combinations thereof.

[0094] The processor can access information and applications stored in memory via a transmission device to perform the following steps: acquiring electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles; calibrating the electromagnetic parameters of brain tissue and constructing a coupled model based on the frequency information, wherein the coupled model includes the cochlear implant and the human head structure; setting parameters of the interference source for wireless charging for electric vehicles and human posture boundaries; based on the parameters of the interference source for wireless charging for electric vehicles and human posture boundaries, and according to the coupled model, simulating and calculating the magnetic induction intensity on the surface of the cochlear implant magnet using a time-domain solver, and extracting the interference signal; constructing a transcutaneous energy transfer circuit model for the cochlear implant based on the coupled model; injecting the interference signal into the transcutaneous energy transfer circuit model for the cochlear implant and performing simulation to determine the receiving coil current and load voltage; based on the receiving coil current and load voltage, determining the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset caused by the interference signal to the static operating point of the circuit; and determining the impact of wireless charging for electric vehicles on the cochlear implant based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset.

[0095] Optionally, the processor may also execute program code for the following steps: calibrating the electromagnetic parameters of brain tissue and constructing a coupling model based on frequency information, including: determining the operating frequency band for wireless charging of electric vehicles based on frequency information; selecting a target frequency within the operating frequency band as the core analysis frequency; obtaining electromagnetic parameter verification data at the core analysis frequency according to a preset standard; comparing the electromagnetic parameters of brain tissue with the electromagnetic parameter verification data to determine the deviation value; calibrating the electromagnetic parameters of brain tissue using interpolation if the deviation value exceeds a preset error range to obtain calibrated electromagnetic parameters of brain tissue; and constructing a coupling model based on the calibrated electromagnetic parameters of brain tissue and the preset structural parameters of the cochlear implant.

[0096] Optionally, the processor may also execute program code for the following steps: setting human posture boundaries, including: determining the spatial position coordinates and angular relationships of the human head relative to the charging coil in each of the multiple preset human posture scenarios, wherein the human posture scenarios include at least standing, squatting and leaning postures; and determining the human posture boundaries according to the spatial position coordinates and angular relationships of the human head relative to the charging coil in each of the multiple human posture scenarios.

[0097] Optionally, the processor may also execute program code for the following steps: based on the parameters of the interference source of the electric vehicle wireless charging and the human posture boundary, according to the coupled model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated by a time-domain solver, and the interference signal is extracted, including: setting multiple monitoring points on the surface of the cochlear implant magnetic component in the coupled model; simulating the process by a time-domain solver and recording the instantaneous values ​​of the magnetic induction intensity corresponding to each of the multiple monitoring points during the simulation, determining the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points and obtaining the output data of the time-domain solver; determining the magnetic induction intensity on the surface of the cochlear implant magnet based on the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points; and extracting the voltage waveform induced in the cochlear implant coil based on the output data of the time-domain solver to determine the interference signal.

[0098] Optionally, the processor may also execute program code for the following steps: determining the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset, including: comparing the current amplitude with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing hearing abnormalities, and obtaining a first judgment result; comparing the current amplitude corresponding to the audible frequency band with a preset hearing perception threshold to determine whether there is a risk of noise interference, and obtaining a second judgment result; comparing the offset with a preset allowable offset range to determine whether there is a risk of damage to signal processing accuracy, and obtaining a third judgment result; and generating an impact result based on the first judgment result, the second judgment result, and the third judgment result.

[0099] Optionally, the processor may also execute program code that performs the following steps: when the result results in impaired signal processing accuracy, an anti-interference filtering scheme is set, wherein the anti-interference filtering scheme includes setting a bandpass filter and a high-pass filter at the front end of the signal processing unit of the cochlear implant.

[0100] This invention provides a method for determining the electromagnetic interference of a cochlear implant. The method involves acquiring electromagnetic parameters of brain tissue and frequency information from wireless charging of an electric vehicle. Based on the frequency information, the electromagnetic parameters of the brain tissue are calibrated, and a coupled model is constructed, which includes the cochlear implant and the human head structure. Interference source parameters for the wireless charging of the electric vehicle and human posture boundaries are defined. Based on the interference source parameters and human posture boundaries, and according to the coupled model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated using a time-domain solver, and the interference signal is extracted. Based on the coupled model, a transcutaneous energy transfer circuit model of the cochlear implant is constructed. The interference signal is then injected into the transcutaneous energy transfer circuit model of the cochlear implant and processed. Simulations were used to determine the receiving coil current and load voltage. Based on the receiving coil current and load voltage, the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by interference signals to the circuit's static operating point were determined. According to the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset, the impact of electric vehicle wireless charging on cochlear implants was determined. This achieved the goal of scientifically and comprehensively evaluating the impact of electromagnetic interference on cochlear implants in the scenario of electric vehicle wireless charging, thus providing a quantitative basis for the design of cochlear implants to resist electromagnetic interference. This solved the technical problem that the lack of a method to determine the impact of electromagnetic interference on cochlear implants in the scenario of electric vehicle wireless charging makes it difficult to adjust cochlear implants to resist electromagnetic interference.

[0101] Those skilled in the art will understand that all or part of the steps in the various methods of the above embodiments can be implemented by a program instructing the hardware related to the terminal device. The program can be stored in a non-volatile storage medium, which may include: flash drive, read-only memory (ROM), random access memory (RAM), disk or optical disk, etc.

[0102] Embodiments of the present invention also provide a non-volatile storage medium. Optionally, in this embodiment, the aforementioned non-volatile storage medium can be used to store the program code executed by the method for determining the electromagnetic influence of a cochlear implant provided in the above embodiments.

[0103] Optionally, in this embodiment, the non-volatile storage medium may be located in any computer terminal in a group of computer terminals in a computer network, or in any mobile terminal in a group of mobile terminals.

[0104] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: acquiring electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles; calibrating the electromagnetic parameters of brain tissue and constructing a coupling model based on the frequency information, wherein the coupling model includes the cochlear implant and the human head structure; setting parameters of the interference source for wireless charging for electric vehicles and human posture boundaries; based on the parameters of the interference source for wireless charging for electric vehicles and human posture boundaries, and according to the coupling model, simulating and calculating the magnetic induction intensity on the surface of the cochlear implant magnet using a time-domain solver, and extracting the interference signal; constructing a transcutaneous energy transfer circuit model for the cochlear implant based on the coupling model; injecting the interference signal into the transcutaneous energy transfer circuit model for the cochlear implant and performing simulation to determine the receiving coil current and load voltage; determining the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset caused by the interference signal to the static operating point of the circuit based on the receiving coil current and load voltage; and determining the impact of wireless charging for electric vehicles on the cochlear implant based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset.

[0105] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: calibrating the electromagnetic parameters of brain tissue and constructing a coupling model based on frequency information, including: determining the operating frequency band for wireless charging of electric vehicles based on frequency information; selecting a target frequency within the operating frequency band as the core analysis frequency; obtaining electromagnetic parameter verification data at the core analysis frequency according to a preset standard; comparing the electromagnetic parameters of brain tissue with the electromagnetic parameter verification data to determine the deviation value; calibrating the electromagnetic parameters of brain tissue using interpolation if the deviation value exceeds a preset error range to obtain calibrated electromagnetic parameters of brain tissue; and constructing a coupling model based on the calibrated electromagnetic parameters of brain tissue and the preset structural parameters of the cochlear implant.

[0106] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: setting human posture boundaries, including: determining the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple preset human posture scenarios, wherein the human posture scenarios include at least standing, squatting and leaning postures; determining the human posture boundaries according to the spatial position coordinates and angular relationships of the human head relative to the charging coil under each of the multiple human posture scenarios.

[0107] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: based on the parameters of the interference source of the electric vehicle wireless charging and the human body posture boundary, according to the coupling model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated by a time-domain solver, and the interference signal is extracted, including: setting multiple monitoring points on the surface of the cochlear implant magnetic component in the coupling model; simulating with a time-domain solver and recording the instantaneous values ​​of the magnetic induction intensity corresponding to each of the multiple monitoring points during the simulation process, determining the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points and obtaining the output data of the time-domain solver; determining the magnetic induction intensity on the surface of the cochlear implant magnet according to the maximum value of the magnetic induction intensity corresponding to each of the multiple monitoring points; and extracting the voltage waveform induced in the cochlear implant coil based on the output data of the time-domain solver to determine the interference signal.

[0108] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: determining the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset, including: comparing the current amplitude with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing hearing abnormalities, and obtaining a first judgment result; comparing the current amplitude corresponding to the audible sound frequency band with a preset hearing perception threshold to determine whether there is a risk of noise interference, and obtaining a second judgment result; comparing the offset with a preset allowable offset range to determine whether there is a risk of damage to signal processing accuracy, and obtaining a third judgment result; and generating an impact result based on the first judgment result, the second judgment result, and the third judgment result.

[0109] Optionally, in this embodiment, the non-volatile storage medium is configured to store program code for performing the following steps: when the result is that the signal processing accuracy is impaired, an anti-interference filtering scheme is set, wherein the anti-interference filtering scheme includes setting a bandpass filter and a high-pass filter at the front end of the signal processing unit of the cochlear implant.

[0110] Embodiments of the present invention also provide a computer program product, including a computer program. Optionally, in this embodiment, when the computer program is executed by a processor, it can: acquire electromagnetic parameters of brain tissue and frequency information of wireless charging for electric vehicles; calibrate the electromagnetic parameters of brain tissue and construct a coupling model based on the frequency information, wherein the coupling model includes a cochlear implant and the human head structure; set parameters of the interference source for wireless charging for electric vehicles and human posture boundaries; based on the parameters of the interference source for wireless charging for electric vehicles and human posture boundaries, calculate the magnetic induction intensity on the surface of the cochlear implant magnet using a time-domain solver according to the coupling model, and extract the interference signal; construct a transcutaneous energy transfer circuit model for the cochlear implant based on the coupling model; inject the interference signal into the transcutaneous energy transfer circuit model for the cochlear implant and perform simulation to determine the receiving coil current and load voltage; based on the receiving coil current and load voltage, determine the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset caused by the interference signal to the static operating point of the circuit; and determine the impact of wireless charging for electric vehicles on the cochlear implant based on the current amplitude, the current amplitude corresponding to the audible sound frequency band, and the offset.

[0111] The sequence numbers of the above embodiments of the present invention are for descriptive purposes only and do not represent the superiority or inferiority of the embodiments.

[0112] In the above embodiments of the present invention, the descriptions of each embodiment have different focuses. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0113] In the several embodiments provided in this application, it should be understood that the disclosed technical content can be implemented in other ways. The device embodiments described above are merely illustrative; for example, the division of units can be a logical functional division, and in actual implementation, there may be other division methods. For instance, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the displayed or discussed mutual coupling, direct coupling, or communication connection may be through some interfaces; the indirect coupling or communication connection between units or modules may be electrical or other forms.

[0114] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0115] Furthermore, the functional units in the various embodiments of the present invention 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.

[0116] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a non-volatile storage medium. Based on this understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of the present invention. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, read-only memory (ROM), random access memory (RAM), portable hard drives, magnetic disks, or optical disks.

[0117] The above description is only a preferred embodiment of the present invention. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of the present invention, and these improvements and modifications should also be considered within the scope of protection of the present invention.

Claims

1. A method for determining the electromagnetic influence of a cochlear implant, characterized in that, include: To obtain electromagnetic parameters of brain tissue and frequency information for wireless charging of electric vehicles; Based on the frequency information, the electromagnetic parameters of the brain tissue are calibrated and a coupling model is constructed, wherein the coupling model includes a cochlear implant and the human head structure. Set the parameters of the interference source for wireless charging of electric vehicles and the boundaries of human posture. Based on the parameters of the wireless charging interference source of the electric vehicle and the human posture boundary, according to the coupling model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated by a time-domain solver, and the interference signal is extracted. Based on the aforementioned coupling model, a transcutaneous energy transfer circuit model for cochlear implants is constructed. The interference signal was injected into the transcutaneous energy transfer circuit model of the artificial cochlea and simulated to determine the receiving coil current and load voltage. Based on the receiving coil current and the load voltage, determine the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by the interference signal to the static operating point of the circuit. The impact of wireless charging of electric vehicles on cochlear implants is determined based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset.

2. The method according to claim 1, characterized in that, The step of calibrating the electromagnetic parameters of the brain tissue and constructing a coupling model based on the frequency information includes: Based on the frequency information, the operating frequency band for wireless charging of electric vehicles is determined; The target frequency within the operating frequency band is selected as the core analysis frequency. Based on preset standards, obtain electromagnetic parameter verification data at the core analysis frequency; The electromagnetic parameters of the brain tissue were compared with electromagnetic parameter verification data to determine the deviation value; If the deviation value exceeds the preset error range, the electromagnetic parameters of the brain tissue are calibrated by interpolation to obtain the calibrated electromagnetic parameters of the brain tissue. The coupling model is constructed based on the calibrated electromagnetic parameters of brain tissue and the preset structural parameters of the cochlear implant.

3. The method according to claim 1, characterized in that, Define the boundaries of human pose, including: Based on multiple preset human posture scenarios, the spatial position coordinates and angle relationships of the human head relative to the charging coil are determined for each of the multiple human posture scenarios. The human posture scenarios include at least standing, squatting and leaning postures. The human posture boundary is determined based on the spatial position coordinates and angle relationship of the human head relative to the charging coil in each of the multiple human posture scenarios.

4. The method according to claim 1, characterized in that, Based on the parameters of the wireless charging interference source of the electric vehicle and the human posture boundary, and according to the coupling model, the magnetic induction intensity on the surface of the cochlear implant magnet is simulated and calculated using a time-domain solver, and the interference signal is extracted, including: Multiple monitoring points are set on the surface of the magnetic component of the cochlear implant in the coupling model; Simulation is performed using the time-domain solver, and during the simulation process, the instantaneous values ​​of magnetic flux density corresponding to each of the multiple monitoring points are recorded. The maximum value of magnetic flux density corresponding to each of the multiple monitoring points is determined, and the output data of the time-domain solver is obtained. The magnetic induction intensity on the surface of the cochlear implant magnet is determined based on the maximum magnetic induction intensity corresponding to each of the multiple monitoring points. Based on the output data of the time-domain solver, the voltage waveform induced in the cochlear implant coil is extracted to determine the interference signal.

5. The method according to any one of claims 1 to 4, characterized in that, The determination of the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset includes: The current amplitude is compared with a preset minimum stimulation current threshold to determine whether there is a risk of directly causing hearing abnormalities, and a first judgment result is obtained. The current amplitude corresponding to the audible frequency band is compared with a preset auditory perception threshold to determine whether there is a risk of noise interference, and a second judgment result is obtained. The offset is compared with a preset allowable offset range to determine whether there is a risk of damage to signal processing accuracy, and a third judgment result is obtained. The impact result is generated based on the first judgment result, the second judgment result, and the third judgment result.

6. The method according to claim 5, characterized in that, Also includes: When the impact result is that the signal processing accuracy is impaired, an anti-interference filtering scheme is set up, wherein the anti-interference filtering scheme includes setting a bandpass filter and a high-pass filter at the front end of the signal processing unit of the cochlear implant.

7. A device for determining the electromagnetic influence of a cochlear implant, characterized in that, include: The acquisition module is used to acquire electromagnetic parameters of brain tissue and frequency information for wireless charging of electric vehicles; The first construction module is used to calibrate the electromagnetic parameters of the brain tissue and construct a coupling model based on the frequency information, wherein the coupling model includes a cochlear implant and the human head structure. The setting module is used to set the parameters of the interference source for wireless charging of electric vehicles and the human posture boundary; The calculation module is used to simulate and calculate the magnetic induction intensity on the surface of the cochlear implant magnet based on the parameters of the electric vehicle wireless charging interference source and the human body posture boundary, according to the coupling model, and extract the interference signal. The second construction module is used to construct a transcutaneous energy transfer circuit model for the cochlea based on the coupling model. The simulation module is used to inject the interference signal into the transcutaneous energy transfer circuit model of the artificial cochlea and perform simulation to determine the receiving coil current and load voltage. The first determining module is used to determine the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset caused by the interference signal to the static operating point of the circuit based on the receiving coil current and the load voltage. The second determining module is used to determine the impact of wireless charging of electric vehicles on cochlear implants based on the current amplitude, the current amplitude corresponding to the audible frequency band, and the offset.

8. A non-volatile storage medium, characterized in that, The non-volatile storage medium includes a stored program, wherein, when the program is executed, it controls the device containing the non-volatile storage medium to perform the electromagnetic influence determination method for the cochlear implant according to any one of claims 1 to 6.

9. A computer device, characterized in that, include: Memory and processor The memory stores computer programs; The processor is configured to execute a computer program stored in the memory, wherein when the computer program is executed, the processor performs the method for determining the electromagnetic influence of the cochlear implant according to any one of claims 1 to 6.

10. A computer program product, comprising a computer program, characterized in that, When the computer program is executed by the processor, it implements the method for determining the electromagnetic influence of the cochlear implant as described in any one of claims 1 to 6.

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