Charging and updating of implantable hearing aids

Abstract

Charging and updating of an implantable hearing aid is disclosed, wherein an implantable hearing aid system, including a charger unit comprising a coil unit having a first resonant frequency, a hearing aid and an implantable part comprising an implantable coil; the hearing aid comprising: a rechargeable battery; an inductive coil structure having a second resonant frequency, the inductive coil structure configured to form an inductive charging link with the coil unit to receive a power signal from the charger unit; a step-down converter configured to reduce a voltage of the power signal received from the charger unit for charging the rechargeable battery; and a step-up converter configured to increase a voltage of a signal obtained from the rechargeable battery; and wherein the inductive coil structure is further configured to form a transcutaneous link with the implantable coil to transfer at least one of data and power to the implantable part, and wherein the first resonant frequency and the second resonant frequency are matched or partially matched.

Description

Technical Field

[0001] This invention relates to an implantable hearing aid system for charging and renewing hearing aids via an induction coil structure. Background Technology

[0002] Implantable hearing aid systems designed to improve hearing in individuals with hearing loss may utilize electrical stimulation of the cochlea or vibrations applied to the skull, or a combination of both. In most cases, implantable hearing aid systems comprise an external hearing aid placed on or over the head, and an implantable component positioned between the skin and skull. The implantable component applies electrical stimulation and / or vibrations. In any of the aforementioned cases, a rechargeable battery may be incorporated into the hearing aid, and in this case, a charger is required to recharge the battery. Several conventional wireless technology standards exist for charging lithium-ion batteries and other batteries that are now more readily available, often integrated into furniture, electronics, and other components around us. An example of a conventional wireless technology standard is the Qi standard, which defines wireless power delivery using inductive charging.

[0003] Therefore, when reading US 2017 / 0040841 A1, it is known to manufacture a charger for recharging the rechargeable battery of an implantable hearing aid. However, the disadvantage of the solution disclosed in that patent application is that the charger is not part of a conventional wireless technology standard such as the Qi standard; rather, the charger is specifically customized for a particular implantable hearing aid. Consequently, the likelihood of being able to recharge the disclosed implantable hearing aid when you are away from home and do not have the customized charger with you is significantly lower.

[0004] Therefore, implantable hearing aids that can be recharged using traditional wireless technology standards are needed. Summary of the Invention

[0005] One aspect of the present invention is to provide an implantable hearing aid system that recharges the hearing aid via conventional wireless technology standards, thereby improving the accessibility of the charger unit when away from home, wherein the charger unit is configured to recharge the hearing aid.

[0006] Another aspect of the present invention is to provide an implantable hearing aid system that allows for hearing aid software updates via an induction coil structure also used for recharging.

[0007] According to one or more of the mentioned aspects, an implantable hearing aid system includes a charger unit comprising a coil unit having a first resonant frequency, a hearing aid, and an implantable component. The hearing aid includes a rechargeable battery and an induction coil structure having a second resonant frequency, the induction coil structure being configured to form an inductive charging link with the coil unit to receive a power signal from the charger unit. The implantable component includes an implantable coil, wherein the induction coil structure is further configured to form a transcutaneous link with the implantable coil to transmit at least one of data and power to the implantable component.

[0008] The first resonant frequency and the second resonant frequency are matched or partially matched, such that the induction coil structure is configured to receive and / or transmit data and / or power via an inductive charging link, which may be part of a conventional wireless technology standard such as the Qi standard.

[0009] The induction coil structure may be disposed outside the housing of the hearing aid, wherein the induction coil structure is connected to the housing via a connector portion comprising one or more wires.

[0010] The induction coil structure can be placed inside the hearing aid's housing.

[0011] The induction coil structure can be connected to the rest of the hearing aid via a connector section that includes one or more wires.

[0012] The connector portion can be a flexible tube, which allows the hearing aid to be placed on the skin of the user's head, for example, behind the user's ear, while the induction coil structure is placed on the user's head.

[0013] In addition, the hearing aid includes a buck converter and a boost converter. The buck converter is configured to reduce the voltage of the power signal received from the charger unit for charging the rechargeable battery, and the boost converter is configured to increase the voltage of the signal obtained from the rechargeable battery.

[0014] Because the first and second resonant frequencies are matched or partially matched, the inductive charging link can efficiently provide a voltage higher than acceptable to the rechargeable battery in the hearing aid. In this case, a buck converter is needed in the hearing aid to reduce the voltage of the power signal provided by the charging unit. Therefore, the lifespan of the rechargeable battery is not shortened by overcharging.

[0015] Rechargeable batteries may include lead-acid, nickel-cadmium (NiCd), nickel-metal hydride (NiMH), lithium-ion (Li-ion), or lithium-ion polymer (Li-ion polymer).

[0016] Furthermore, when a hearing aid is used to communicate with an implantable component via a transcutaneous link, the hearing aid receives a voltage signal from a rechargeable battery. In this case, the voltage of the signal obtained from the rechargeable battery needs to be increased by a boost converter; otherwise, communication and / or power transfer will not be robust and / or efficient when established via the transcutaneous link.

[0017] The first and second resonant frequencies are located in the frequency range between 80 kHz and 300 kHz or between 110 kHz and 205 kHz. The hearing aid is configured to switch between these two frequency ranges based on the type of charger unit. For example, a charger unit operating between 80 kHz and 300 kHz is characterized as a medium-power Qi charger, and a charger unit operating between 110 kHz and 205 kHz is characterized as a low-power Qi charger. Low-power Qi chargers deliver up to 5 watts, and medium-power Qi chargers deliver up to 120 watts.

[0018] Thus, if a hearing aid user has a low-power Qi charger unit on hand, the user can configure the second resonant frequency to a frequency range of 110kHz to 205kHz; the reverse is true for a medium-power Qi charger unit. The user can switch between these two ranges via the hearing aid's user interface or via the user interface of an external communication device such as a smartphone or smartwatch.

[0019] To ensure a stable inductive charging link between the charger unit and the hearing aid, the induction coil structure may include a magnet configured to align the induction coil of the induction coil structure with the coil unit of the charger unit.

[0020] The charger unit may have a magnet, a metal surface or metal parts, which are configured as a magnet to attract an induction coil structure.

[0021] A metal surface or metal component may be located at the center of the coil unit, and the center of the coil unit is surrounded by the coil of the coil unit.

[0022] The induction coil structure may have a third resonant frequency that resonates with the resonant frequency of the implantable coil, and the third resonant frequency may be in the frequency range of 4MHz to 6.5MHz, 4MHz to 10MHz, or 4MHz to 12MHz. The defined frequency range is suitable for establishing a percutaneous link, but not suitable for establishing an inductive charging link that may be part of a conventional wireless technology standard such as the Qi standard.

[0023] Hearing aids may include a capacitor circuit structure configured to tune the resonant frequency of an induction coil structure to a plurality of resonant frequencies, including at least a second resonant frequency. The capacitor circuit structure may be connected to the induction coil structure, a buck converter, and a boost converter.

[0024] A capacitor circuit structure may include a plurality of capacitors, wherein one or more of the plurality of capacitors have contacts configured to couple and decouple the one or more capacitors such that when a capacitor is decoupled, the capacitor is not an effective part of the capacitor circuit structure, and when a capacitor is coupled, the capacitor is an effective part of the capacitor circuit structure.

[0025] The position of the contact can be controlled based on a measure of the Q factor of the induction coil structure or a measure of the power level of the signal received by the induction coil structure.

[0026] The position of the contacts of one or more capacitors can be controlled by selecting the resonant frequency through the user interface of the hearing aid or through the user interface of an external communication device such as a smartphone or smartwatch.

[0027] The hearing aid may include a processor configured to transmit control signals to a capacitor circuit structure, wherein the capacitor circuit structure includes a switch, a first tuning circuit, and at least a second circuit, each of the two tuning circuits being connectable to the switch, and the switch being configured to receive the control signal, wherein the switch is configured to connect an induction coil structure to the first tuning circuit or the second tuning circuit based on the control signal. Thus, the hearing aid's ability to adjust the resonant frequency of the induction coil structure is improved.

[0028] The processor can be part of an external communication device such as a smartphone or smartwatch.

[0029] The first tuning circuit can be configured to form a percutaneous link with the implantable coil when connected to the induction coil structure via a switch, and the second tuning circuit can be configured to form an inductive charging link with the coil unit when connected to the induction coil structure via a switch.

[0030] The capacitor circuit structure may include at least a first filter and a first tuning circuit, wherein the first filter and the first tuning circuit are connected. The capacitor circuit structure may also include a second filter and a second tuning circuit, wherein the second filter and the second tuning circuit are connected. The first tuning circuit may be connected to an induction coil structure, wherein the first filter, the first tuning circuit, and the induction coil structure are configured to form a transdermal link with an implantable coil. The second tuning circuit may be connected to the induction coil structure, wherein the second filter, the second tuning circuit, and the induction coil structure are configured to form an inductive charging link with a coil unit.

[0031] The two filters, namely the first filter and the second filter, can be configured to separate the charging power transmitted by the charger unit from the power / data to be transmitted.

[0032] The two filters can be notch filters that include one or more capacitors and one or more inductors.

[0033] For example, the first filter may have a resonant frequency of about 6.78 MHz, and the second filter may have a resonant frequency of about 140 kHz.

[0034] The control signal can be determined based on a measure of the Q factor of the induction coil structure, or based on a measure of the power level of the signal received by the induction coil structure.

[0035] Control signals can be determined based on the user interface of the hearing aid or external communication device.

[0036] Because the control signal and / or contact position can be determined by measuring the Q factor or the power level, the resonant frequency of the induction coil structure can be automatically adjusted.

[0037] Because the control signal and / or contact position can be determined via user interface input, the resonant frequency of the induction coil structure can be adjusted more easily.

[0038] The hearing aid may include a first antenna configured to form a communication link with a second antenna of the charger unit for communicating charging data. This communication link may be based on Bluetooth or Bluetooth Low Energy. The charging data may include charging capacity information or temperature of the rechargeable battery.

[0039] The charger unit can be configured to transmit data to the hearing aid via an inductive charging link or a second inductive link between the coil unit and the inductive coil structure. The data transmitted includes charging data, software update data, and / or firmware update data. This allows for simultaneous charging and updating of the hearing aid's software or firmware. This makes it possible to update the hearing aid at home. Furthermore, by utilizing the inductive coil structure, the hearing aid is made more compact while reusing the inductive coil structure for multiple purposes. Additionally, if a second antenna is used for updating the hearing aid, the hearing aid requires power from the battery to drive the second antenna, resulting in a longer charging time. Therefore, by using the inductive coil structure for multiple purposes, such as charging and updating, a shorter charging time is achieved compared to examples with a second antenna.

[0040] Multiple resonant frequencies may include a fourth resonant frequency for the second induction link.

[0041] The charger unit may include a far-field communication interface configured to transmit update response / acknowledgment signals via the far-field communication interface, and to receive software update data and / or firmware update data via the far-field communication interface based on the update acknowledgment signals.

[0042] The update confirmation signal includes information data about the hearing aid, such as identification data.

[0043] The far-field communication interface may include a transceiver interface configured to transmit and receive software update data over a communication network, wherein the communication network includes a mobile network, a local area network, and / or a wireless network. Attached Figure Description

[0044] Various aspects of the invention will be best understood from the following detailed description taken in conjunction with the accompanying drawings. For clarity, these drawings are schematic and simplified, showing only the details necessary for understanding the invention while omitting other details. Throughout the specification, the same reference numerals are used for the same or corresponding parts. Features of each aspect may be combined with any or all features of other aspects. These and other aspects, features, and / or technical effects will be apparent from and illustrated in the following figures, wherein:

[0045] Figure 1A and 1B Different examples of implantable hearing aid systems are shown;

[0046] Figure 2A and 2B Different examples of implantable hearing aid systems are shown;

[0047] Figure 3A and 3B Different examples of capacitor circuit structures are shown;

[0048] Figure 4A and 4B Different examples of implantable hearing aid systems are shown;

[0049] Figure 5 An example of an implantable hearing aid system is shown;

[0050] Figure 6A and 6B Different examples of capacitor circuit structures are shown. Detailed Implementation

[0051] The detailed description below, taken in conjunction with the accompanying drawings, serves as a description of various different configurations. This detailed description includes specific details to provide a thorough understanding of several different concepts. However, it will be apparent to those skilled in the art that these concepts can be implemented without these specific details. Several aspects of the apparatus and method are described by various different blocks, functional units, modules, elements, etc. (collectively, “elements”). These elements may be implemented using other equivalent elements depending on a particular application, design constraints, or other reasons.

[0052] Hearing aids are designed to improve or enhance a user's hearing ability by receiving sound signals from the user's environment, generating corresponding audio signals, possibly modifying those audio signals, and providing the possibly modified audio signals as audible signals to at least one of the user's ears. The audible signals can be provided as sound signals transmitted through the bone structures of the user's head to the user's inner ear as mechanical vibrations.

[0053] Hearing aids may be replaced by a system comprising one or two hearing aids. A “binaural hearing system” refers to a system comprising two hearing aids adapted to collaboratively provide audible signals to both of the user’s ears, or a bone conduction hearing aid may be part of a bimodal system comprising a cochlear implant and a bone conduction hearing aid. The system may also include an assistive device that communicates with at least one hearing aid, influencing and / or benefiting from the operation of the hearing aid. A wired or wireless communication link is established between at least one hearing aid and the assistive device to allow the exchange of information (such as control and status signals, possibly audio signals). The assistive device may include at least one of the following: a remote control, a remote microphone, an audio gateway device, a mobile phone, a broadcasting system, a car audio system, a music player, or a combination thereof. The audio gateway device is adapted to receive multiple audio signals, such as from an entertainment device like a TV or music player, from a telephone device like a mobile phone, or from a computer like a PC. The audio gateway device is also adapted to select and / or combine appropriate signals from the received audio signals (or combinations of signals) to transmit to at least one hearing aid. The remote control is suitable for controlling the functions and operation of at least one hearing aid. The functions of the remote control can be implemented in a smartphone or another electronic device, which may run an application that controls the functions of at least one hearing aid.

[0054] Generally, a hearing aid includes i) an input unit, such as a microphone, for receiving sound signals from the user's surroundings and providing a corresponding input audio signal; and / or ii) a receiver unit for electronically receiving the input audio signal. The hearing aid also includes a signal processing unit for processing the input audio signal and an output unit for providing an audible signal to the user based on the processed audio signal.

[0055] The input unit may include multiple input microphones, for example, for providing direction-dependent audio signal processing. The aforementioned directional microphone system is adapted to enhance a target sound source among multiple sound sources in a user's environment. In one aspect, the directional system is adapted to detect (e.g., adaptively detect) the direction from which a specific portion of the microphone signal originates. This can be achieved using methods conventionally known. The signal processing unit may include an amplifier adapted to apply a frequency-dependent gain to the input audio signal. The signal processing unit may also be adapted to provide other suitable functions such as compression, noise reduction, etc. The output unit may include an output converter for providing mechanical vibrations to the skull percutaneously or transdermally.

[0056] Figure 1A and 1B Different examples of an implantable hearing aid system 1 are shown, wherein the implantable hearing aid system 1 includes a charger unit 3, the charger unit including a coil unit 8 having a first resonant frequency. Furthermore, the implantable hearing aid system 1 includes hearing aids (2, 2A, 2B) including a rechargeable battery 4 and an induction coil structure 6 having a second resonant frequency, the induction coil structure 6 being configured to form an inductive charging link 10 with the coil unit 8 to receive a power signal from the charger unit 3. Additionally, the implantable hearing aid system 1 includes an implantable component (not shown) including an implantable coil, wherein the induction coil structure is further configured to form a transcutaneous link with the implantable coil to transmit at least one of data and power to the implantable component, wherein the first resonant frequency and the second resonant frequency are matched or partially matched. Figure 1A In the hearing aid 2, the induction coil structure 6 is disposed inside the housing 12, and in... Figure 1B In this design, the induction coil structure 6 is disposed outside the housing 12 of the hearing aid 2B. Figure 1B In the case, the induction coil structure 6 is connected to the housing 12 via the connector portion 5, which includes one or more wires for transmitting data and power between the induction coil structure 6 and the hearing aid 2B.

[0057] Figure 2A and 2B Different examples of implantable hearing aid system 1 are shown, wherein the hearing aids (2, 2A, 2B) include a buck converter 24 and a boost converter 26. The buck converter is configured to reduce the voltage of the power signal received from the charger unit 3 for charging the rechargeable battery 4, and the boost converter 26 is configured to increase the voltage of the signal obtained from the rechargeable battery 4. Figure 2A In this configuration, at least the rechargeable battery 4, the boost converter 26, and the buck converter 24 are disposed within the area surrounded by the induction coil structure 6 or near the center of the induction coil structure 6. Figure 2B In the hearing aid 2B, at least the rechargeable battery 4, the boost converter 26 and the buck converter 24 are disposed inside the housing 12, and the induction coil structure 6 is disposed outside the housing 12.

[0058] exist Figure 2A and 2B In the hearing aid (2,2A,2B), therein, there is a capacitor circuit structure (20,200) configured to adjust the resonant frequency of the induction coil structure to a plurality of resonant frequencies including at least a second resonant frequency and a third resonant frequency.

[0059] exist Figure 2A and 2BIn the hearing aid (2, 2A, 2B), a processor 22 is included, which is configured to transmit control signals to a capacitor circuit structure (20, 200).

[0060] Figure 3A and 3B Different examples of capacitor circuit structures (20, 200) are shown. Figure 3A In the capacitor circuit structure 20, at least one of a first switched capacitor 204 and a second switched capacitor 201 may be included, wherein the first switched capacitor 204 may be connected in parallel with the first circuit element 203, and the second switched capacitor 201 may be connected in series with the second circuit element 202. Furthermore, the resonant frequency of the induction coil structure 6 may be adjusted based on at least one measured Q factor of the induction coil structure or based on a power level metric of the signal received by the induction coil structure, and at least one of the first and second switched capacitors 201 and 204 may be selectively connected to the circuit constituting the capacitor circuit structure 20.

[0061] exist Figure 3B In the capacitor circuit structure 200, there are at least switches (206A, 206B), a first tuning circuit (20, 20A), and at least a second circuit (20, 20B). Each of the two tuning circuits (20, 20A, 20B) is connected to a switch (206A, 206B). The switches (206A, 206B) are configured to receive control signals (208A, 208B) and, based on the control signals (208A, 208B), connect the induction coil structure 6 and the remaining parts (4, 22) of the hearing aid (2, 2A, 2B) (210A, 210B) to either the first tuning circuit (20, 20A) or the second tuning circuit (20, 20B).

[0062] The first tuning circuit (20, 20A) is configured to form a percutaneous link with an implantable coil (not shown) when connected to the induction coil structure 6 via switches (206A, 206B), and the second tuning circuit (20, 20B) is configured to form an inductive charging link 10 with the coil unit 8 when connected to the induction coil structure 6 via switches (206A, 206B).

[0063] The control signal can be determined by processor 22, which is configured to determine the control signal based on a metric of the Q factor of the induction coil structure 6, or the control signal can be determined based on a metric of the power level of the signal received by the induction coil structure 6.

[0064] Figure 4A and 4B Different examples of implantable hearing aid system 1 are shown, wherein the induction coil structure 6 may include a magnet 30 configured to align the induction coil 6A of the induction coil structure 6 with the coil unit 8 of the charger unit 3. Figure 4AIn the charger unit, there is a magnet 32, which is configured such that the coil unit 8 surrounds the magnet 32, and a magnet 30 in the induction coil structure 6 is configured such that the induction coil 6A surrounds the magnet 30.

[0065] exist Figure 4B In this embodiment, the charger unit may have a second magnet, a metal surface, or a metal component configured to magnetically attract the magnet in an induction coil structure. The metal surface or metal component may be disposed at the center of the coil unit 8, and the center of the coil unit 8 is surrounded by the coil of the coil unit 8.

[0066] Figure 5 An implantable hearing aid system 1 is shown, wherein a charger unit 3 is configured to transmit data to a hearing aid via an inductive charging link 10 or via a second inductive link 51 between a coil unit 8 and an inductive coil structure 6, and the data transmitted therein includes charging data, software update data, and / or firmware update data.

[0067] The charger unit 3 may include a far-field communication interface 50, which is configured to transmit update response / acknowledgment signals via the far-field communication interface 50, and to receive software update data and / or firmware update data via the far-field communication interface 50 based on the update acknowledgment signals.

[0068] The far-field communication interface 50 includes a transceiver interface configured to transmit and receive software update data via a communication network 52, wherein the communication network 52 includes a mobile network, a local area network, and / or a wireless network.

[0069] Local area networks (LANs) may include one or more of the following: Bluetooth, Bluetooth Low Energy, and Wi-Fi.

[0070] Figure 6A and 6B Different examples of capacitor circuit structures (20, 200) are shown. Figure 6A In the capacitor circuit structure (20, 200), the capacitor circuit structure (20, 200) can be a passive element including at least first and second filters (60, 61).

[0071] The first and second filters can be notch filters, bandpass filters, lowpass filters, shortwave filters, or any filter type suitable for filtering the first, second, and third resonant frequencies.

[0072] exist Figure 6B In the capacitor circuit structure 200, there are a first filter 60 and a second filter 61, wherein both filters (60, 61) receive data / power through connector portion 5, and the first filter 60 and the second filter 61 are also connected to buck converter 24 and boost converter 26 respectively.

[0073] The first filter 60 is configured to pass through resonant frequencies in a frequency range of 80kHz to 300kHz (medium-power Qi charger), 110kHz, and 205kHz (low-power Qi charger). For example, the first filter 60 is configured to pass through a first and / or second resonant frequency and eliminate or reduce signal levels with resonant frequencies outside of that resonant frequency. For example, the first filter 60 is configured to eliminate or reduce signal levels with resonant frequencies in a frequency range of 4MHz to 6.5MHz, 4MHz to 10MHz, or 4MHz to 12MHz. The first filter 60 is configured to eliminate or reduce signal levels with respect to a third resonant frequency.

[0074] The second filter 61 is configured to pass through resonant frequencies in the frequency ranges of 4MHz to 6.5MHz, 4MHz to 10MHz, or 4MHz to 12MHz. For example, the second filter 61 is configured to pass through a third resonant frequency and eliminate or reduce signal levels at resonant frequencies outside of that resonant frequency. For example, the second filter 61 is configured to eliminate or reduce signal levels at resonant frequencies in the frequency range of 80kHz to 300kHz (medium-power Qi charger), 110kHz, and 205kHz (low-power Qi charger). The second filter 61 is configured to eliminate or reduce signal levels with respect to the first and / or second resonant frequencies.

[0075] Unless explicitly stated otherwise, the singular forms “a” and “the” as used herein include the plural forms (i.e., meaning “at least one”). It should be further understood that the terms “having,” “comprising,” and / or “including” as used in the specification indicate the presence of the stated features, elements, components, and / or steps, but do not preclude the presence or addition of one or more other features, elements, components, and / or steps. It should be understood that, unless explicitly stated otherwise, when an element is referred to as “connected” or “coupled” to another element, it may be a direct connection or coupling to the other element, or there may be intermediate inserting elements. The term “and / or” as used herein includes any and all combinations of one or more of the listed related items. Unless explicitly stated otherwise, the steps of any method disclosed herein do not necessarily have to be performed in the exact order disclosed.

[0076] It should be understood that references to "an embodiment," "an embodiment," "an aspect," or "may" in this specification mean that a particular feature, structure, or characteristic described in connection with that embodiment is included in at least one embodiment of the invention. Furthermore, particular features, structures, or characteristics may be suitably combined in one or more embodiments of the invention. The foregoing description is provided to enable those skilled in the art to implement the various aspects described herein. Various modifications will be apparent to those skilled in the art, and the general principles defined herein may be applied to other aspects.

[0077] The scope of this invention should be determined based on the claims.

Claims

1. An implantable hearing aid system, comprising: Implantable components, including implantable coils; A charger unit that includes a coil unit; Hearing aids, including Rechargeable batteries Induction coil structure, A capacitor circuit structure configured to adjust the resonant frequency of the induction coil structure includes a switch, a first tuning circuit, and at least a second tuning circuit, wherein each of the at least two tuning circuits is connected to the switch. A processor configured to transmit control signals to the switch, wherein the switch is configured to connect an induction coil structure to a first tuning circuit or a second tuning circuit based on the control signals. The first tuning circuit is configured to form a percutaneous link with the implantable coil when connected to the induction coil structure via a switch to transmit at least one of data and power to the implantable component, and the second tuning circuit is configured to form an inductive charging link with the coil unit when connected to the induction coil structure via a switch to receive a power signal from the charger unit. The hearing aid further includes: a buck converter configured to reduce the voltage of a power signal received in the inductive charging link for charging a rechargeable battery; and a boost converter configured to increase the voltage of a signal obtained from the rechargeable battery for transmission in a transcutaneous link; and The control signal of the processor is determined based on a metric of the Q factor of the induction coil structure, or the control signal is determined based on a metric of the power level of the signal received by the induction coil structure.

2. The implantable hearing aid system of claim 1, wherein the resonant frequency is in a first frequency range between 80 kHz and 300 kHz or in a second frequency range between 110 kHz and 205 kHz.

3. The implantable hearing aid system of claim 1, wherein the induction coil structure includes a magnet configured to align the induction coil of the induction coil structure with the coil unit of the charger unit.

4. The implantable hearing aid system of claim 2, wherein the capacitor circuit structure includes a first filter and a second filter, the first filter being configured to pass signals in a first or second frequency range, and the second filter being configured to pass signals in a third frequency range of 4 MHz to 12 MHz.

5. The implantable hearing aid system according to any one of claims 1-4, wherein the hearing aid includes a first antenna configured to form a communication link with a second antenna of the charger unit for communicating charging data.

6. The implantable hearing aid system of claim 5, wherein the charging data includes charging capacity information or temperature of the rechargeable battery.

7. The implantable hearing aid system according to any one of claims 1-4, wherein the charger unit is configured to transmit data to the hearing aid via the inductive charging link or via a second inductive link between the coil unit and the inductive coil structure, wherein the transmitted data includes charging data, software update data, and / or firmware update data.

8. The implantable hearing aid system of claim 7, wherein the charger unit includes a far-field communication interface configured to transmit an update response / acknowledgment signal via the far-field communication interface, and to receive software update data and / or firmware update data via the far-field communication interface based on the update acknowledgment signal.

9. The implantable hearing aid system of claim 8, wherein the update confirmation signal includes information data about the hearing aid.

10. The implantable hearing aid system of claim 8 or 9, wherein the far-field communication interface includes a transceiver interface configured to transmit and receive software update data via a communication network, wherein the communication network includes a mobile network, a local area network, and / or a wireless network.

11. The implantable hearing aid system of claim 4, wherein the second filter is configured to pass signals in a third frequency range of 4 MHz to 10 MHz.

12. The implantable hearing aid system of claim 4, wherein the second filter is configured to pass signals in a third frequency range of 4 MHz to 6.5 MHz.

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