Implantable hearing aid system comprising a wireless transcutaneous link

Abstract

An implantable hearing aid system comprising a wireless transcutaneous link, comprising: an external unit comprising an electronics unit operatively connected to a first inductive coil structure configured to transmit power and / or data signals, wherein the first inductive coil structure comprises a ring structure, a coil is wound around and along at least a part of the length of the ring structure, and the ring structure comprises an opening; and an implantable unit comprising a second inductive coil structure configured to form a transcutaneous link with the ring structure and receive power and / or data signals via the transcutaneous link, and wherein the second inductive coil structure is configured to be fully or partially implanted within a part of the ear of a user of the implantable hearing aid system; wherein the external unit comprises a housing and an ear hook, and wherein a first end face of the ring structure is arranged within the ear hook and a second end face of the ring structure is arranged within the housing or within the ear hook.

Description

TECHNICAL FIELD

[0001] The present invention relates to an implantable hearing aid system comprising a transcutaneous link. In particular, the present invention relates to an implantable hearing aid system comprising a wireless transcutaneous link for link transmission of power and / or data signals via a coupling between a first inductive coil structure of an external unit and a second inductive coil structure of an implantable unit, wherein the coupling coefficient between the coil structures is substantially increased. BACKGROUND

[0002] Any discussion of the prior art throughout the specification is in no way an admission that such prior art is widely known or forms part of the common general knowledge of the skilled person in the field.

[0003] Conventional implantable hearing aid systems comprise an external unit and an implantable unit, wherein the implantable unit is arranged between the skin and the skull of a user of the system and the external unit is arranged on the skin and magnetically fixed to the implantable unit. This means that both the external unit and the implantable unit have a magnet. The implantable magnet is associated with risks during MRI scans. As the patient enters the scanner, the powerful magnetic forces of the scanner will try to force the implant magnet into alignment.

[0004] Many cochlear implant manufacturers use an open "soft silicone pocket" design that uses a thin lip of silicone to hold a simple axial magnet in place.

[0005] Due to the soft silicone pocket design, there is minimal resistance to the aforementioned powerful magnetic forces, so the implant magnet can easily misalign. A partially or fully misaligned implant magnet can cause extremely painful, focused pressure. This often results in an incomplete scan and a revision surgery to replace the magnet.

[0006] This is why magnet misalignment is a major risk for cochlear implants. In an attempt to reduce the risk of magnet misalignment, companies with soft silicone pocket designs need tight head wraps combined with special rigid splint kits, which complicate MRI scans. The problem is that this tight head wrap does not eliminate the cause or risk of magnet misalignment. Rather, it can apply painful pressure on the skin between a partially misaligned implant magnet and the rigid splint. And the implant magnet can still misalign and cause a revision surgery.

[0007] A solution is for example a rotatable, self-aligning implant magnet, however, this solution applies a complex mechanical design and does not guarantee a high Tesla MRI scan even without a head wrap.

[0008] Furthermore, having a magnet in place during an MRI scan will cause magnet-induced magnetic field distortions, with consequent more pronounced unnatural signals, thus preventing a large area of examination around the implant / magnet.

[0009] Furthermore, the magnetically fixed external unit results in a rather high weight of the external unit, and likewise, a rather large size of the external unit. This is not only uncomfortable for the user, but also aesthetically unattractive. Furthermore, in the case of MRI (Magnetic Resonance Imaging), the implanted magnet has to be removed by surgery or specially designed. Furthermore, due to the limited attraction force between the magnets, the external unit can move from the desired position or even fall off due to rapid movements of the head, e.g. when the patient jumps.

[0010] For a conventional coil structure with the transmitter coil and the receiver coil placed on both sides of the skin and in parallel planes, the coupling factor is very low, since most of the magnetic field lines generated by the transmitter coil are not picked up by the receiver coil, thus resulting in a poor energy transfer efficiency. Furthermore, since both coils are located on both sides of the skin, any change in the coil separation, e.g. due to an increase in the skin thickness, can result in a rapid decrease of the coupling factor between the two coils. For efficiency reasons, the external unit typically comprises a rather large battery compartment or multiple batteries, so that the implantable hearing aid system can be used for a period of time that does not cause the user to be annoyed, e.g. requiring the user to change the batteries frequently or recharge the battery compartment. In addition to making the external unit less aesthetically attractive, the additional weight of the battery compartment or multiple batteries also requires stronger holding magnets, which can result in discomfort and, in extreme cases, skin irritation or infection under the influence of the constant magnetic force generated between the holding magnets and the implanted magnets.

[0011] For other types of hearing implants than cochlear implants, such as implants relying on bone conduction for transmission of sound, a higher coupling factor can be used in two ways. A higher efficiency in the transmission of power through the skin is used to reduce the required battery (thus reducing the size of the external sound processor) or to prolong the battery life (before recharging or changing the battery is required). However, importantly, for bone conduction devices, a higher efficiency can be used to increase the maximum force output or amplification. For bone conduction devices, an increase in efficiency will directly translate into an increase in amplification, meaning that patients with more severe hearing loss can be treated. SUMMARY

[0012] The present invention provides an alternative coil structure for a wireless transcutaneous link and discloses an implantable hearing aid system comprising a wireless transcutaneous link, wherein one or more of the above mentioned drawbacks are overcome.

[0013] It is an aspect of the present invention to provide an implantable hearing aid system that provides a more aesthetic appearance or less visibility.

[0014] Furthermore, it is an aspect of the present invention to provide a more efficient power transfer efficiency through the skin and between the external unit and the implantable unit of the implantable hearing aid system.

[0015] In addition, an aspect of the present invention is to provide an implantable hearing aid system which is more resistant to strong external magnetic fields such as the magnetic field from an MRI scanner.

[0016] Furthermore, for bone conduction implantable hearing aid systems, higher efficiency can be used to increase amplification and make the inclusion criteria wider.

[0017] According to one or more of the above mentioned aspects, an implantable hearing aid system is disclosed. The implantable hearing aid system comprises an external unit comprising an electronics unit operatively connected to a first inductive coil structure configured to transmit power and / or data signals, wherein the first inductive coil structure comprises a ring structure, a coil is wound around and along at least a part of the length of the ring structure, and the ring structure comprises an opening. Furthermore, the implantable hearing aid system comprises an implantable unit comprising a second inductive coil structure configured to form a transcutaneous link with the ring structure and receive the power and / or data signals via the transcutaneous link, and wherein the second inductive coil structure is configured to be fully or partially implanted within a part of the ear of a user of the implantable hearing aid system. The external unit comprises a housing and an ear hook, and wherein a first end face of the ring structure is arranged within the ear hook and a second end face of the ring structure is arranged within the housing or the ear hook.

[0018] At least a part of the first inductive coil structure can be arranged within or in the vicinity of the through-going hole or opening of the second inductive coil structure when the external unit is wearable at the ear of the user. The through-going hole or opening can also be referred to as a hollow portion in the present specification.

[0019] An advantage of the implantable hearing aid system is that the external unit does not need to be fixed to the implantable unit via a coupling magnet interface. Another effect is that the implantable hearing aid system is more resistant to strong magnetic fields, e.g. from an MRI scanner.

[0020] The external unit can be arranged on or in the ear, thereby providing a more aesthetic appearance, since the external unit is hidden behind or in the ear of the user, or the external unit is small enough to be regarded as a piece of jewelry hanging on the ear.

[0021] The external unit can be shaped as a conventional hearing aid, e.g. a behind-the-ear hearing aid, an in-the-ear hearing aid or an ear hook hearing aid. The housing of the external unit can comprise at least a microphone, an electronics unit, the first inductive coil structure or at least a part of the first inductive coil structure.

[0022] The housing of the external unit can comprise a processing unit configured to process an audio signal based on an acoustic signal received by at least one microphone to improve or enhance the hearing ability of the user of the implantable hearing aid system.

[0023] The housing can comprise at least a microphone and a first inductive coil structure, and wherein the implantable unit comprises the remaining elements of a hearing aid such as a processing unit, a transducer, a rechargeable battery, etc.

[0024] The housing of the external unit can have a top portion comprising an interface to the ear hook, and the housing can further comprise a bottom portion opposite the top portion.

[0025] The housing can have a first longitudinal axis along a longitudinal length from the top portion to the bottom portion, and the ring-shaped structure can have a second longitudinal axis along a length of the ring-shaped structure. The first device is not parallel to the second device.

[0026] The housing can be a behind-the-ear hearing aid, and the ear hook can be curved in a direction that is not parallel to the first longitudinal axis, and the ear hook can be curved such that the end faces of the ring-shaped structure are pointing directly towards each other or partially against each other. The aforementioned end faces will be fully or partially towards each other and through the through-going hole or opening of the second inductive coil structure of the implantable unit when the external unit is arranged on the ear and the implantable unit is beneath the skin of the ear. The ear hook provides an ideal placement of the external unit behind the ear, while also having an optimal position of the ring-shaped structure of the first inductive coil structure relative to the second inductive coil structure.

[0027] The ear hook can be formed such that at least one end face of the ring-shaped structure is directed towards an outer surface of the housing, and the outer surface of the housing is directed towards the skin of the ear.

[0028] The housing can have a region with an inner surface and an outer surface, and the inner surface is arranged opposite the outer surface. At least one end face of the ring-shaped structure is directed towards the inner surface of the region, and at least one end face of the ring-shaped structure is directed towards the outer surface, and the two end faces are fully or partially directed towards each other.

[0029] The through-going hole or opening can form part of a hollow portion of the second inductive coil structure.

[0030] When a user wears the implantable hearing aid system, the external unit can be arranged on or in the ear of the user, and a part of the implantable unit can be arranged between the skin and the skull of the user, and the second inductive coil structure can be fully or partially arranged beneath the ear skin of the user. The external unit can be configured to transmit power and / or data signals to the second inductive coil structure via the first inductive coil structure and through the ear skin.

[0031] The implantable unit can be configured to transmit power and / or data signals to the first inductive coil structure via the second inductive coil structure and through the ear skin.

[0032] The housing can be connected to the ear hook via a connector portion. The connector portion can comprise one or more wires for transmission of power and / or data signals between the ring-shaped structure of the ear hook and the electronic unit of the housing. The one or more wires connect the ring-shaped structure and the electronic unit and / or other units of the external unit.

[0033] The housing can be arranged behind the ear or in the ear of the user while the ear hook is fixed to the ear by a clamping force or by piercing the skin.

[0034] The housing and the ear hook can be connected by a flexible unit. The flexible unit is configured to apply the ear hook into a first position or at least a second position when a force is applied to the ear hook or the housing. In the first position the external unit is not fixed to the ear so that the user can remove the external unit from the ear. In the second position the external unit is fixed to the ear by a clamping force between the housing and the ear hook. The fixing of the external unit to the ear does not mean that the external unit is permanently fixed to the ear. In any example of the external unit the user of the system can detach the external unit. The detachment of the external unit can be performed by changing the position of the ear hook or by changing the position of the end face of the ring-shaped structure. For example, when the end face of the ring-shaped structure is engaged the ear hook cannot be removed and when the end face is not engaged the ear hook can be removed.

[0035] The flexible unit can be made of a resilient material, such as silicone, so that the ear hook can be moved in a direction that makes it easy for the user to remove the ear hook from the ear.

[0036] The flexible unit can comprise a rotating device configured to rotate the ear hook or at least a part of the ear hook between a first position and at least a second position.

[0037] The size of the opening of the ring-shaped structure can be adjusted to change the position of the ear hook between the first position and the at least second position. The size of the opening determines the clamping force between the external unit and the ear.

[0038] The housing and the ear hook can be combined and the housing can be made of a first material and the ear hook can be made of a second material, wherein the second material is softer than the first material. The first material enables the ear hook to move into the first position or the second position when a force is applied to the ear hook or the housing. In the second position the external unit is fixed to the ear by a clamping force between the housing and the ear hook on the ear.

[0039] The clamping force can be provided by the flexible unit or by the material the ear hook is made of.

[0040] The ring-shaped structure can comprise a first ring-shaped structure that can be arranged in the housing and a second ring-shaped structure that can be arranged in the ear hook, both the first ring-shaped structure and the second ring-shaped structure forming the ring-shaped structure. The first ring-shaped structure and the second ring-shaped structure can be connected such that the first ring-shaped structure can be moved relative to the second ring-shaped structure and transfer a visible amount of magnetic field lines between the first ring-shaped structure and the second ring-shaped structure. The first ring-shaped structure can comprise a second end face and the second ring-shaped structure can comprise a first end face.

[0041] The ring-shaped structure can be arranged in a protective sleeve of ferrite material for protecting the ring-shaped structure.

[0042] The first inductive coil structure can comprise a protective cover configured to comprise a toroidal structure and a coil wound around the toroidal structure. The protective cover can be made of a silicone material or any type of material that protects the toroidal structure, but minimizes the reduction of the inductive coupling efficiency between the first and second inductive coil structures. The purpose of the protective cover is to protect the toroidal structure from damage when the first inductive coil structure is dropped from the ear.

[0043] The toroidal structure can consist of a magnetic core formed of a ferromagnetic material, such as iron laminations, iron powder or ferrite, around which a wire is wound. The toroidal structure can be ring-shaped, have a through hole in the center of the toroidal structure, and wherein the magnetic core surrounds the through hole.

[0044] The toroidal structure can be ring-shaped having a circular, elliptical, rectangular, square, polygonal, curvilinear shape or any combination thereof.

[0045] The toroidal structure can comprise a shape selected from the group consisting of: circular, elliptical, rectangular, square, polygonal, curvilinear shape or any combination thereof.

[0046] The coil wound around a portion of the toroidal structure can be disposed within the ear hook, i.e. outside the housing of the external unit, in order to protect the electronic unit and / or other units of the external unit that are sensitive to external and unwanted external electromagnetic fields provided by the first inductive coil structure.

[0047] The external unit can comprise a shielding unit configured to magnetically shield the electronic unit and other units of the external unit from unwanted external electromagnetic fields provided by the first inductive coil structure. The shielding unit can be a resonant element provided within the near field of the toroidal structure, which is connected to ground potential through an energy dissipating means to terminate and dissipate electromagnetic noise from at least a portion of the toroidal structure. The shielding unit can be disposed between the toroidal structure and the electronic unit and other units of the external unit. The resonant element implements a notch filter that filters electromagnetic radiation noise.

[0048] The term "other units of the external unit" includes one or more of the following: processing unit, rechargeable battery, control unit, communication unit, RF antenna, other antenna types, speaker, microphone, etc.

[0049] The resonant element is connected to ground potential through the battery of the external unit.

[0050] The winding density of the coil of the toroidal structure along the first inductive coil structure can be higher near the first end face and the second end face of the toroidal structure compared to the rest of the toroidal structure. The purpose of the higher density is to provide more concentrated magnetic field lines between the end faces of the toroidal structure of the first inductive coil structure and through the through opening of the second inductive coil structure. The more concentrated magnetic field lines provide a more efficient transcutaneous link for the energy transfer between the first and second inductive coil structures.

[0051] The winding density of the coil along the loop structure of the first induction coil structure can be equal or partially equal along the length of the loop structure.

[0052] The implantable unit can be an implantable processor and / or an implantable stimulator configured to generate an output. The output can be configured to generate a perceivable stimulus for a user. For example, the aforementioned perceivable stimulus includes the perception of sound in the case of an implantable hearing aid. For an implantable hearing aid system, the output can include a stimulation pulse (typically frequency specific) or a signal for generating a vibratory force (typically frequency specific). In an embodiment, the implantable unit includes a power controller adapted to control the utilization of power received at the second induction coil structure.

[0053] The data signal transmitted via the transcutaneous link can include a control signal, a configuration signal, an information signal and / or an audio signal, and the implantable unit can include a transducer, such as a vibration-based transducer and / or an electrical stimulator, for generating vibrations and / or electrical stimulation, respectively, based on the audio signal. The vibrations are transmitted to the user's skull via a fixation device or via a vibrating housing. The electrical stimulation is applied to the user's cochlea via an electrode array comprising a plurality of electrodes arranged within the user's cochlea. The vibration-based transducer can be an electromagnetic-based vibrator or a piezoelectric-based transducer.

[0054] The second induction coil structure can be within an implantable housing comprising the transducer or within an implantable coil housing connected to the implantable housing via one or more leads. The implantable coil housing can be arranged beneath the user's ear skin, and the implantable housing can be arranged between the user's skin and skull.

[0055] The implantable coil housing, the implantable housing or the second induction coil structure can comprise an implantable loop structure, the coil being wound around and along at least a portion of the length of the implantable loop structure and through a hole, the through hole being configured to have an overlap area with the first induction coil structure and / or the loop structure of the first induction coil structure.

[0056] When the implantable unit is arranged beneath the ear skin, the radius or diagonal of the through hole or opening of the second induction coil structure can be parallel or almost parallel to a portion of the ear skin, and the depth of the through hole or opening can be orthogonal or almost orthogonal to the portion of the ear skin.

[0057] The through hole or opening of the implantable housing can have an inner side, which is a chamfered inner side or a partially chamfered inner side. The purpose of the chamfered inner side is to guide the loop structure of the external unit into an optimal position when positioning the ear hook on the ear. When in the optimal position, an optimal inductive connection is provided between the end face of the loop structure and the implantable loop structure. The chamfered inner side is angled such that the loop structure is directed towards the center of the through hole of the second induction coil structure when applying the ear hook to the ear.

[0058] The ear hook can have a tip which can be configured to have an overlapping face with the second inductive coil structure. The tip can comprise a portion of the loop structure, for example one of the end faces of the loop structure.

[0059] The first or second end face of the loop structure of the first inductive coil structure can be configured to have an overlapping face with the second inductive coil structure.

[0060] The overlapping face can be provided within the through hole or within an area enclosed inside a chamfer.

[0061] The overlapping face provides an improved optimal inductive coupling since the distance between the end face of the loop structure and the implantable loop structure is reduced.

[0062] The transcutaneous link can be a bidirectional or unidirectional inductive link.

[0063] At least a portion of the second inductive coil structure can be disposed in at least one of the following portions of the ear: the helix, the antihelix, the scapha, the triangular fossa, the concha, the tragus and the external ear. Disposing the implantable unit, and more particularly the second inductive coil structure, within the ear results in a significant reduction in the distance between the first and second inductive coil structures, as compared to disposing the implantable unit between the patient's head, i.e. the skull and the skin. The reduction in distance provides a more efficient coupling between the first and second inductive coil structures.

[0064] The end faces of the loop structure can be merged together to form a closed loop structure having a geometry comprising a closed curve, wherein a point moving along the closed curve forms a path from a starting point to an ending point, the ending point coinciding with the starting point when the closed curve is in a closed mode. In an embodiment, the closed curve can comprise a single portion loop structure comprising an openable portion comprising the first end face and the second end face. The openable portion is connected at a first end face end to the rest of the loop structure and at a second end face end is adapted to open the openable portion (i.e. to form an open mode when the openable portion is open) to enable access to the hollow portion of the first inductive coil structure, i.e. the through hole or opening, and to position a portion of the ear within the hollow portion. The closed mode is formed when the openable portion is engaged at the second end face with the rest of the loop structure to form the closed curve.

[0065] The loop structure can be integral.

[0066] The loop structure can be integral and can move together with the ear hook. The tip of the ear hook can be made of a resilient material which makes it easier for the user to apply the ear hook to the ear or to remove the ear hook from the ear.

[0067] The ring structure can comprise a multi-part ring structure, wherein the multi-part comprises a plurality of separable parts, such as a first sub-part and a second sub-part, configured to be connected to each other to form a closed ring structure. The closed mode is formed when the plurality of separable parts are connected to each other. Thus, the open mode can be formed when the plurality of separable parts are not connected to each other, and in the open mode the ring structure is adapted to enable a part of the body to be located within the hollow part of the ring structure. This can be achieved when the ring structure is in the open mode.

[0068] The ring structure can be defined by a geometry comprising an open curve forming an open ring structure, wherein a point moving along the open curve forms a passage from a starting point to an end point, the end point being proximate to the starting point but separated from the starting point by a distance. The distance is typically a function of the thickness of the body tissue and / or skin to which the ring structure is connected, i.e. the distance is configured such that the ring structure can be connected to the user's ear. The distance is formed between the first end face and the second end face. The distance is selected from the group consisting of a length smaller than the thickness of the ear tissue, a length larger than the thickness of the ear tissue but adapted to be reduced such that the changed length is smaller than the thickness of the ear tissue, a length smaller than (even close to zero) the thickness of the ear tissue but adapted to be increased such that the changed length is slightly smaller than the thickness of the ear tissue. Obviously, a length smaller or slightly smaller than the thickness of the ear tissue is adjusted such that a compression holding force is exerted against the body tissue between the first end face (i.e. the first point of the geometry) and the second end face (i.e. the second point of the geometry).

[0069] Obviously, the length of the opening is smaller or slightly smaller than the thickness of the ear tissue and the second inductive coil structure. Alternatively, the length of the opening can be adjusted such that a compression holding force is exerted against the ear tissue between the tip of the ear hook and the housing of the external unit (or between the end faces of the ring structure). The skilled person will realize that the distance can be changed to achieve a balance between reliable holding and user comfort, especially for long time wearing of the external unit.

[0070] The ear hook can comprise a tip with a compression reducing means, and wherein the tip is configured to contact the skin of the ear portion when the external unit is worn by the user. The advantage of having a compression reducing means is to improve the comfort of wearing the ear hook, and the ear hook can be adapted to different ear types, e.g. ears with different ear thickness and / or ear shape.

[0071] The compression reducing means can comprise a spring configured to compress when the tip contacts the skin.

[0072] The compression reducing means can be made of an elastic material, such as foam or silicone.

[0073] The tip can be made of slow-recovery foam to reduce the pressure on the skin, and the shape of the tip should also be optimized for optimal holding and comfort. For example, it can be made more flat and have high friction properties.

[0074] The term "in proximity" to or "near" a second inductive coil structure means that the first inductive coil structure is arranged close to the second inductive coil structure such that inductive coupling between the first inductive coil structure and the second inductive coil structure is achieved. This is achieved when the ring-shaped structure is attached to the ear.

[0075] The term "hollow portion" or "through-going hole or opening" is formed by the area enclosed by the closed ring-shaped structure when the closed ring-shaped structure is in the closed mode.

[0076] The term "hollow portion" or "through-going hole or opening" can be formed by the area enclosed by the ring-shaped structure in combination with an imaginary line separating the distance between the first end face and the second end face.

[0077] The external unit can comprise a first RF antenna configured to communicate with a second antenna arranged in the implantable unit, such that data signals can be transmitted via the communication between the first and second RF antennas, and power signals can be transmitted to the second inductive coil structure via the first inductive coil structure. It is advantageous to transmit the power signals and the data signals via separate communication interfaces, such as the RF and inductive interfaces. The RF link between the first and second RF antennas can be based on Bluetooth, Bluetooth Low Energy or other types of short-range communication protocols.

[0078] The external unit can be configured to transmit power signals and data signals via the inductive coil structure in different communication modes, wherein in a first communication mode data signals are transmitted to the implantable unit, and in a second communication mode power signals are transmitted to the implantable unit. In the respective communication modes, the resonance frequency of the inductive coil structure can be different, and / or the modulation of the power signals and data signals can be different.

[0079] In this specification, unless explicitly stated otherwise, different embodiments disclosed should be considered as combinable. BRIEF DESCRIPTION OF DRAWINGS

[0080] Various aspects of the application will be best understood with reference to the following detailed description together with the drawings, in which like reference numerals refer to like elements throughout. The drawings are schematic and simplified for clarity and the deliberate use of

[0081] Figures 1A-1E Different examples of implantable hearing aid systems are shown;

[0082] Figures 2A-2F Different examples of external units are shown;

[0083] Figures 3A-3D Different examples of ring structures are shown;

[0084] Figures 4A-4B An implantable coil housing is shown;

[0085] Figure 5 Examples of second inductive coil structures are shown;

[0086] Figures 6A-6D Different examples of flexible units are shown;

[0087] Figure 7 Examples of flexible units are shown;

[0088] Figure 8 Examples of external units are shown;

[0089] Figures 9A-9D Different examples of ear hook tips are shown;

[0090] Figures 10A-10B Different examples of housings are shown;

[0091] Figure 11 An implantable hearing aid system is shown;

[0092] Figures 12A-12B Examples of second inductive coil structures are shown;

[0093] Figure 13A Arrangements of ring structures are shown;

[0094] Figure 13B Arrangements of second inductive coil structures are shown; and

[0095] Figure 13C A housing is shown. DETAILED DESCRIPTION

[0096] The detailed description set forth below, in connection with the appended drawings, is intended as a description of various configurations and is not intended to limit the concepts. The detailed description includes specific details for the purpose of providing a thorough understanding of the concepts. However, it will be apparent to those skilled in the art that these concepts can be practiced without these specific details. Several aspects of the apparatus and methods are described by way of various blocks, functional units, modules, elements, and the like (collectively referred to as "elements"). Such elements can be implemented using other equivalent elements in hardware, software, firmware, or combinations thereof.

[0097] A hearing aid is adapted to improve or enhance the hearing ability of a user by receiving acoustic signals from the user's surroundings, generating corresponding audio signals, possibly modifying the audio signals, and providing the possibly modified audio signals as audible signals to at least one ear of the user. The audible signals can be provided in the form of acoustic signals as mechanical vibrations through the bone structure of the user's head to the inner ear of the user.

[0098] A hearing aid can be replaced by a system comprising one or two hearing aids. A "binaural hearing system" refers to a system comprising two hearing aids, wherein the hearing aids are adapted to cooperatively provide audible signals to both ears of the user, or a bone-anchored hearing aid can be part of a bimodal system comprising a cochlear implant and a bone-anchored hearing aid. The system can further comprise an auxiliary device in communication with at least one of the hearing aids, which auxiliary device influences the operation of the hearing aid and / or benefits from the functionality of the hearing aid. A wired or wireless communication link is established between the at least one hearing aid and the auxiliary device to enable exchange of information, such as control and status signals, possibly audio signals, therebetween. The auxiliary device can comprise at least one of the following: a remote control, a remote microphone, an audio gateway device, a mobile phone, a radio system, a car audio system, a music player, or a combination thereof. The audio gateway device is adapted to receive a plurality of audio signals, e.g. from an entertainment device such as a TV or a music player, from a telephony device such as a mobile phone, or from a computer such as a PC. The audio gateway device is further adapted to select and / or combine appropriate ones of the received audio signals (or combinations of signals) for transmission to the at least one hearing aid. The remote control is adapted to control the functionality and operation of the at least one hearing aid. The functionality of the remote control can be implemented in a smart phone or another electronic device, which smart phone / electronic device possibly runs an application program controlling the functionality of the at least one hearing aid.

[0099] Generally, a hearing aid comprises i) an input unit, such as a microphone, for receiving acoustic signals from the surroundings of the user and providing corresponding input audio signals; and / or ii) a receiving unit for electronically receiving the input audio signals. The hearing aid further comprises a signal processing unit for processing the input audio signals and an output unit for providing audible signals to the user based on the processed audio signals.

[0100] The input unit can comprise a plurality of input microphones, e.g. for providing directional audio signal processing. The aforementioned directional microphone system is adapted to enhance a target sound source among a plurality of sound sources in the surroundings of the user. In one aspect, the directional system is adapted to detect, e.g. adaptively detect, from which direction a particular portion of the microphone signals originates. This can be achieved using conventionally known methods. The signal processing unit can comprise an amplifier adapted to apply a frequency-dependent gain to the input audio signals. The signal processing unit can further be adapted to provide other suitable functionality, such as compression, noise reduction, etc. The output unit can comprise an output transducer for transcutaneous or percutaneous provision of mechanical vibrations to the skull.

[0101] Figures 1A-1E A different example of an implantable hearing aid system 1 is shown. The implantable hearing aid system 1 comprises an external unit 2 comprising an electronic unit 4 (not shown) operatively connected to a first inductive coil structure 6 (not shown) configured to transmit power and / or data signals. Furthermore, the implantable hearing aid system comprises an implantable unit 14 comprising a second inductive coil structure 16 (not shown) configured to form a transcutaneous link 18 (not shown) with the first inductive coil structure 6 (not shown). The second inductive coil structure 16 is implanted within a part of an ear 20 of a user of the implantable hearing aid system 1. The second inductive coil structure 16 has a hollow portion 30 configured to receive a part of an ear hook 24. The external unit comprises a housing 22 and the ear hook 24, wherein the first inductive coil structure can be arranged within the ear hook 24 or partly within the ear hook 24 and partly within the housing 22.

[0102] The implantable unit 14 can comprise an implantable stimulator and / or an implantable vibrator. In Figures 1A-1E A specific example of the implantable hearing aid system 1 is shown, wherein the implantable unit 14 comprises an implantable stimulator having an electrode array 34 for providing electrical stimulation to the cochlea 36 of the user.

[0103] Figure 1A An example of the implantable hearing aid system 1 is shown, wherein the housing 22 is shaped as a behind-the-ear hearing aid having the ear hook 24 connected thereto. The ear hook 24 is arranged around the top of the ear 20 and exerts a pressure between the ear hook 24 and the housing 22 onto the skin of the ear 20. A part of the ear hook 24 is arranged in proximity to the hollow portion 30. The hollow portion 30 can be referred to as a through-going hole or opening.

[0104] Figure 1B An example of the implantable hearing aid system 1 is shown, wherein the ear hook is in a position such that the user can remove the external unit 2 from the ear 20.

[0105] Figure 1C An example of the implantable hearing aid system 1 is shown, wherein the housing 22 and the ear hook 24 are merged. The implantable unit 14 comprises one or more of the following elements: a processor unit, an implantable transducer and / or implantable stimulator unit, a memory and a rechargeable battery 22. The external unit 2 comprises one or more of the following elements: a processor unit, an implantable transducer and / or implantable stimulator unit, a memory and a rechargeable battery 22. In this specific example, the external unit 2 comprises a microphone and circuitry for driving the microphone, the ear hook 24 and the housing 22, and the implantable unit 14 comprises the second inductive coil structure 16, a processor unit, an implantable stimulator unit, a memory and a rechargeable battery. In this specific example, the size of the external unit 2 is significantly reduced compared to Figure 1A and 1B the examples described in the examples described in

[0106] Figure 1D An example of an implantable hearing aid system 1 is shown, wherein the housing 22 is shaped as an in-the-ear hearing aid and the housing 22 is connected to an ear hook 24 via a connector portion 32, which can comprise one or more wires for transmitting power and / or data signals between a first induction coil structure 6 (not shown) of the ear hook 24 and an electronic unit 4 (not shown) of the housing 22. The ear hook 24 can be attached to the ear 20 by a clamping force provided by a clamping device (not shown) forming part of the ear hook 24.

[0107] The ear hook 24 can comprise a needle configured to pierce the ear 20 to secure the ear hook 24 to the ear 20.

[0108] Figure 1E An example of an implantable hearing aid system 1 is shown, wherein the housing 22 is shaped as a behind-the-ear hearing aid. The ear hook 24 is connected to the housing via a connector portion 32 (not shown), which can comprise one or more wires for transmitting power and / or data signals between a first induction coil structure 6 (not shown) of the ear hook 24 and an electronic unit 4 (not shown) of the housing 22. The ear hook 24 can be attached to the ear 20 by a clamping force provided by a clamping device (not shown) forming part of the ear hook 24.

[0109] The ear hook 24 can comprise a needle configured to pierce the ear 20 to secure the ear hook 24 to the ear 20.

[0110] Figures 2A-2F A different example of an external unit 2 is shown, which comprises an ear hook 24 with a ring structure 8 and an electronic unit 4 arranged within the housing. Figure 2A A specific example of an external unit 2 is shown, wherein the housing 22 is a behind-the-ear hearing aid and is connected to an ear hook 24. The ring structure 8 is partly arranged within the housing 22 and partly within the ear hook 24, and wherein the ring 10 is arranged on the part of the ring structure within the housing 22. An opening 12 is formed between a first end face 26 and a second end face 28 for receiving a part of the ear 20 and a second induction coil structure 16. The current 11 applied to the coil 10 travels within the ring structure 8 in a direction opposite to the magnetic field lines 9, which travel through a hollow part of the second induction coil structure 16 (not shown) being part of an implantable unit 14 (not shown) when the external unit 2 is worn by a user.

[0111] Figure 2B An external unit 2 similar to the one described in Figure 2A However, the coil 10 is arranged within the ear hook, since the distance between the coil 10 and the other units of the external unit 2 is increased. Furthermore, the opening 12 between the end faces (26, 28) or the outer surface 23 of the housing 22 and the tip 25 of the ear hook can be clearly visible.

[0112] Figure 2CA specific example of an external unit 2 is shown, where the housing 22 is an in-the-ear hearing aid and is connected to an ear hook 24 via a connector section 32 comprising one or more wires for transferring current to the coil 10 and for transmitting power and / or data signals to be transmitted via the transcutaneous link 18 to the implantable unit 14. The ear hook 24 is a separate part from the housing 22, where the housing 22 is arranged in the ear canal of the user, and the ear hook 24 is applied to the ear such that the opening 12 receives a part of the ear 20 of the user.

[0113] Figure 2D The external unit 2 in Figure 2C is similar to the external unit 2 shown in Figure 2E , however, the housing 22 is a behind-the-ear hearing aid. Figure 2D An external unit 2 similar to the one shown in , however, the ear hook is configured to be fixed on the ear by a clamping force between the end faces (26, 28) of the at least ring-shaped structure 8. The clamping force is provided by a clamping device 33 and a spring unit 31, to which the first induction coil structure 6 is applied.

[0114] Figure 2F A specific example of an external unit 2 is shown, where the housing 22 is merged with the ear hook 24 such that both the housing 22 and the ear hook 24 are arranged on the pinna of the ear 20 when the external unit 2 is placed on the ear. In this example, the implantable unit 14 comprises a rechargeable battery, a processor unit and other units driving the implantable unit 14 together with the external unit 2. The external unit 2 comprises at least one microphone, the electronic unit 4 and the first induction coil structure 6.

[0115] Figures 3A-3D Different examples of the ring-shaped structure 8 are shown. In Figure 3A , two sets of coils (10, 10A, 10B) are applied such that the coil density at the end faces (26, 28) of the ring-shaped structure 8 is higher than the coil density in the rest of the ring-shaped structure. In Figure 3B , the ring-shaped structure 8 is symmetric about a symmetry axis 13, and the two sets of coils (10, 10A, 10B) are arranged at different positions on the ring-shaped structure 8 and on each side of the symmetry axis 13. Figure 3C One set of coils (10, 10A) is shown arranged on one side of the symmetry axis 13, and in one example, this one set of coils (10, 10A) is arranged in the ear hook 24 and outside the housing 22. Figure 3D The coils 10 are shown distributed along the ring-shaped structure 8 with the same or partly the same density.

[0116] Figure 4A and 4BAn example of a second inductive coil structure 16 is shown. The second inductive coil structure 16 comprises an implantable coil housing 43 having a hollow portion 30 with a chamfered inner side 42. In another example, the hollow portion can have a straight inner side. The chamfered inner side 42 is configured to guide the first inductive coil structure 6 to obtain an optimal position of the toroidal structure 8 with respect to the hollow portion of the second inductive coil structure 16. The straight inner side provides a more fixed connection between the first inductive coil structure 6 and the second inductive coil structure 16. The hollow portion 30 can be tube-shaped or box-shaped or any shape enabling an optimal inductive connection between the first inductive coil structure 6 and the second inductive coil structure 16.

[0117] Figure 4A An implantable coil housing 43 is shown having a connection interface 41 to an implantable housing 14 (not shown). The implantable coil housing 43 can be arranged under the skin of a user and the implantable housing can be arranged between the skin and the skull of a user. The implantable housing can comprise a transducer, e.g. a vibration-based transducer, and / or an electrical stimulator. Figure 4B A cross-sectional view of the implantable coil housing 43 is shown. Within the implantable coil housing 43, a toroidal structure 44 is shown, around which a coil 45 is wound over a length of the toroidal structure 44.

[0118] The implantable coil housing 43 has a first axis 46 which is parallel or partly parallel to the ear skin when the second inductive coil structure 16 is arranged under the skin of the ear 20 of a user. The radius or diagonal of the hollow portion is parallel to the first axis 46. The implantable coil housing 43 has a second axis 47 which is parallel to the first axis 46 and is arranged centrally in the hollow portion 30. An optimal inductive connection between the first inductive coil structure 6 and the second inductive coil structure 16 is obtained when the end faces (26, 28) are aligned with the second axis 47.

[0119] Figure 5 An example of the second inductive coil structure 16 integrated within a printed circuit board (PCB) 48 is shown. Implementing the second inductive coil structure 16 within a PCB is to reduce the size of the coil structure 16.

[0120] Figures 6A-6D Different examples of a flexible unit 50 configured to provide a flexible connection between the housing 22 and the ear hook 24 are shown. In Figure 6AIn one embodiment, the flexible unit 50 is configured to move the ear hook 24 in any direction, which will result in an optimal position of the housing 22 and the ear hook 24 on the user's ear 20. For example, when moving the ear hook 24 from a first position to a second position by applying a force to the ear hook 24, the ear hook 24 can be held in the second position or will return to the first position when the force is released. The second position of the ear hook 24 can be suitable for removing the external unit 2 from the ear 20, and the first position of the ear hook 24 can be suitable for obtaining an optimal connection between the first and second inductive coil structures 6, 16.

[0121] In one embodiment, the flexible unit 50 is configured to move the ear hook 24 in any direction, which will result in an optimal position of the housing 22 and the ear hook 24 on the user's ear 20. For example, when moving the ear hook 24 from a first position to a second position by applying a force to the ear hook 24, the ear hook 24 can be held in the second position or will return to the first position when the force is released. The second position of the ear hook 24 can be suitable for removing the external unit 2 from the ear 20, and the first position of the ear hook 24 can be suitable for obtaining an optimal connection between the first and second inductive coil structures 6, 16. Figure 6B

[0122] Figure 6C An example of a flexible unit 50 similar to the one shown in Fig. 1 is shown, however, the spring unit 52 is applied along the length of the ring structure (8A, 8B) in Fig. 2. In this specific example, the spring unit 52 is applied at the end faces (26B, 28B) along said length. The purpose of the spring unit 52 is to ensure that the first and second end faces (26, 28) are optimally positioned in relation to the second inductive coil structure 16 when the external unit 2 is positioned on the ear 20 and the implantable unit 14 is positioned under the user's skin. For example, when the user wants to apply the external unit 2 to the ear 20, the user has to move the ear hook 24 into a position where the opening 12 can receive a part of the ear 20, and when the user releases the ear hook, the ear hook will return such that an optimal inductive connection between the first and second inductive coil structures (6, 16) is obtained. Figure 6B Figure 6C The spring unit 52 can have one stable equilibrium position.

[0123]

[0124] Figure 6D ​​​Another example of a spring unit 52 is shown. In this example, the spring unit 52 is a metal spring shaped to obtain two stable equilibrium positions of the ear hook 24 relative to the housing 22. The spring unit 52 is inside the flexible unit 50 and separate from the loop structure 8.

[0125] Alternatively, the flexible unit 50 can be shaped as a sleeve configured to receive the housing 22 at one end and the ear hook 24 at the other end. The housing 22 and the ear hook 24 are snap connected to the flexible unit 50, thereby preventing the flexible unit 50 from being accidentally released from the housing 22 and the ear hook 24. The ear hook 24 is configured to rotate in a direction around the center of the hollow portion of the flexible unit 50.

[0126] Figure 7 An example of a flexible unit 50 is shown. The inside of the opening 60 of the housing 22 includes a protrusion configured to receive and seal the ear hook 24. The end 61 of the ear hook configured to be inserted into the opening 60 includes an inside having a protrusion configured to connect with the protrusion of the opening 60 when the end 61 of the ear hook 24 is inserted into the opening 60 of the housing, thereby the housing 22 can be sealably connected to the ear hook 24. The ear hook can be rotated around the center of the opening 60. The flexible unit 50 includes a pin 63 configured to be freely rotatable within a trace portion 64 of the flexible unit 50 and between a first fixed position 64A and a second fixed position 64B. When the ear hook 24 is rotated, the pin 63 moves within the trace portion 64 and when the pin 63 reaches the first or second fixed position 64B, the ear hook 24 is fixed to a position enabling the user to remove the ear hook 24 from the ear 20 or to form an optimal inductive connection between the first and second inductive coil structures (6, 16).

[0127] Figure 8 An example of an external unit 2 is shown, in which the end face 61 of the ear hook 24 and the periphery of the opening 60 are shaped to prevent the user from incorrectly assembling the ear hook 24 and the housing 22. In this specific example, the end face 61 of the ear hook 24 and the periphery of the opening 60 are stepped (71, 72), the inward portion 75 of the opening 60 is configured to receive the outward portion 73 of the end face 61 and the outward portion 76 of the opening 60 is configured to receive the inward portion 74 of the end face while the other end face (26B, 28B) is snap connected. For example, if the outward portions meet when trying to assemble the ear hook 24 and the housing 22, the snap connection between the other end faces (26B, 28B) will not occur.

[0128] Figures 9A-9D Different examples of the tip 25 of the ear hook 24 are shown. Figure 9A and 9BAn example of a tip 25 comprising a first part 81 mounted into the ear hook 24 and can comprise the first end face 26 of the loop structure 8 is shown. The first part has a hollow spring part 80 configured to receive a spring 82 and a tip 81. A second part 83 is configured to be assembled to the first part 81 so that the spring 82 and the tip 81 are held in place within the tip 25. The spring force of the spring 82 is configured to reduce the pinch force between the ear and the opening 12 of the external unit 2 when the tip 81 contacts the ear skin. Thereby, the external unit 2 can be adapted to different ear thicknesses.

[0129] Figure 9C and 9D A further example of a tip 25 is shown. The first part 81 is mounted into the ear hook 24 and the first part 81 comprises the first end face 26 of the loop structure 8. The tip 25 comprises a spring 82 wrapped around the first end face 26 of the loop structure 8. The tip 25 comprises a tip 84 comprising a hollow part configured to receive the spring 82 and a part of the first end face 26 when the tip 84 is assembled onto the first part 81. Thereby, the external unit 2 can be adapted to different ear thicknesses and the distance between the first end face and the second end face is reduced.

[0130] Figure 10A and 10B Different examples of the housing 22 of the external unit 2 are shown. In Figure 10A the outer surface 23 of the housing 22 comprises an outward bag 90. When the user applies the external unit 2 onto the ear 20 and when the external unit 2 is in the optimal position where the best connection between the coil structures (6, 16) is obtained, the outward bag 90 is partly or fully inserted into the hollow part 30 from one side of the second inductive coil structure 16 while the tip 25 of the ear hook is partly or fully inserted into the hollow part 30 from the opposite side of the second inductive coil structure 16. When the outward bag 90 is partly or fully inserted into the hollow part 30, a tactile signal is generated between the outward bag 90 and the hollow part 30 of the second inductive coil structure 16. The purpose of the tactile signal is to enable the user to know that the external unit 2 is in the optimal position.

[0131] In Figure 10B the outer surface of the housing, which faces the ear skin when the external unit 2 is placed on the ear, comprises a plurality of protrusions 91 for reducing possible skin inflammation / discomfort. For example, skin inflammation can be caused by heat generated between the housing and the ear skin and by applying protrusions 91 onto the surface 23, air is able to propagate between the spaces between the protrusions when the external unit 2 is on the ear 20.

[0132] Figure 11An implantable hearing aid system is shown, which comprises at least a further ear hook 24B comprising a first secondary inductive coil structure 6A, and wherein the electronics unit 4 is configured to be connected to the first inductive coil structure 6 and the first secondary inductive coil structure 6A. In this example, the implantable unit 14 comprises at least a second secondary inductive coil structure (not shown) configured to form a further transcutaneous link (not shown) with the loop structure 100 of the first secondary inductive coil structure 6A and to receive power and / or data signals from the first secondary inductive coil structure 6A via the further transcutaneous link, wherein the second secondary inductive coil structure is configured to be fully or partially implanted within a part of the user's ear.

[0133] The second secondary inductive coil structure can be provided within the ear opposite to the ear in which the second inductive coil structure is provided. Thereby, a binaural implantable hearing aid system is provided.

[0134] The second secondary inductive coil structure can be provided within the same ear as the second inductive coil structure. Thereby, the amount of power and / or data signals transmitted in the transcutaneous link is increased without increasing the delay between the signals.

[0135] The implantable unit comprises at least a second secondary inductive coil structure (not shown) configured to form a further transcutaneous link with the loop structure of the first secondary inductive coil structure and to receive power and / or data signals from the first secondary inductive coil structure via the further transcutaneous link, wherein the second secondary inductive coil structure is configured to be fully or partially implanted within a part of the user's ear.

[0136] Figure 12A and 12B An example of the second inductive coil structure 16 is shown with a flange 101 comprising a plurality of holes for improving the tissue anchoring of the coil structure 16. The plurality of holes can be an internal growth means for skin and / or tissue to grow into, thereby anchoring the second inductive coil structure 16 within the ear. In Figure 12B In the example, the implantable unit 14 is in place and the second inductive coil structure 16 is provided between the skin layer 103 and the cartilage layer 104 of the ear 20. After implantation of the implantable unit 14, a healing clip 105 is installed into the ear and the coil structure 16 to keep the coil structure 16 in place during the interlacing of the tissue around the coil structure 16. After implantation and anchoring of the coil structure 16 within the ear, the healing clip 105 improves the healing process of the ear.

[0137] Figure 13A An example is shown in which the first end face 26 and the second end face 28 of the loop structure 8 are provided within the housing 22, and wherein the loop structure 8 comprises a plurality of loops. Figure 13BAn example is shown where the second inductive coil structure 16 is implanted in the ear, for example in the concha region of the ear. In this particular example, the second inductive coil structure 16 comprises a plurality of loops. Figure 13C An example is shown where the housing 22 is a behind-the-ear hearing aid, where the plurality of loops of the loop-shaped structure 8 is aligned with the plurality of loops of the second inductive coil structure. The loop-shaped structure 8 being aligned with the second inductive coil structure 16 means that the plurality of loops of the loop-shaped structure 8 is parallel or approximately parallel with the plurality of loops of the second inductive coil structure 16.

[0138] It is to be appreciated that a reference herein to "one embodiment" or "an embodiment" or "aspect" or "may" include a particular feature, structure, or characteristic described in connection with at least one embodiment of the application. Moreover, the particular features, structures, or characteristics can be combined in any suitable manner in one or more embodiments of the application. The foregoing description has been presented for purposes of illustration. Various modifications, alterations, and permutations of the embodiments disclosed herein are

[0139] The claims are not to be limited to the various aspects illustrated herein but include whatever falls within the scope of the claims language. Which reference to an element in the singular is not intended to mean "one and only one" unless specifically so stated, but rather "one or more." Unless specifically stated otherwise, the term "some" refers to one or more.

[0140] Thus, the scope of the application should be determined by the claims and their legal equivalents rather than by the description of the various aspects.

Claims

1. An implantable hearing aid system, comprising: an external unit comprising an electronics unit operatively connected to a first inductive coil structure configured to transmit power and / or data signals, wherein the first inductive coil structure comprises a ring structure, a coil is wound around and along at least a part of a length of the ring structure, and the ring structure comprises an opening; and an implantable unit comprising a second inductive coil structure configured to form a transcutaneous link with the ring structure and receive power and / or data signals via the transcutaneous link, and wherein the second inductive coil structure is configured to be fully or partially implanted within a part of an ear of a user of the implantable hearing aid system; wherein the external unit comprises a housing and an ear hook, and wherein a first end face of the ring structure is arranged within the ear hook and a second end face of the ring structure is arranged within the housing; wherein the ear hook is configured to be formed such that the first end face of the ring structure is directed towards an outer surface of the housing, and the outer surface of the housing is configured to be directed towards the ear skin when the external unit is worn by the user.

2. The implantable hearing aid system according to claim 1, comprising a flexible unit, wherein the ear hook is connected to the housing of the external unit by the flexible unit, and wherein the ear hook is configured to be in a first position and at least a second position when a force is exerted on the ear hook.

3. The implantable hearing aid system according to claim 2, wherein the flexible unit comprises a rotating device configured to rotate the ear hook or at least a part of the ear hook between the first position and the at least second position.

4. The implantable hearing aid system according to claim 2 or 3, wherein the opening of the ring structure is adjustable in size to change the position of the ear hook between the first position and the at least second position.

5. The implantable hearing aid system according to claim 1, wherein the ear hook comprises a tip having a compression reducing device, and wherein the tip is configured to contact the skin of the ear part when the external unit is worn by the user.

6. The implantable hearing aid system according to claim 5, wherein the compression reducing device comprises a spring configured to compress when the tip contacts the skin.

7. The implantable hearing aid system according to claim 5, wherein the compression reducing device is made of a foam material.

8. The implantable hearing aid system according to claim 1, wherein at least a part of the second inductive coil structure is arranged in at least one of the following parts of the ear: the helix, the antihelix, the scapha, the triangular fossa, the concha, the tragus and the external ear.

9. The implantable hearing aid system according to claim 1, wherein the opening is arranged between the first end face and the second end face of the ring structure, and wherein the two end faces are fully or partially directed towards each other at a position of the ear hook.

10. The implantable hearing aid system of claim 1, wherein, The winding density of the coil of the first inductive coil structure is higher near the first end face and the second end face of the ring structure compared to the rest of the ring structure.

11. The implantable hearing aid system according to claim 1, wherein the second inductive coil structure comprises an implantable housing comprising an implantable ring structure, a coil is wound around and along at least a part of a length of the implantable ring structure, and wherein the implantable housing comprises a through hole, and the through hole is configured to have an overlapping face with the first inductive coil structure.

12. The implantable hearing aid system according to claim 11, wherein the through hole of the implantable housing has a chamfered inner side.

13. The implantable hearing aid system according to claim 1, wherein at least the tip of the ear hook or an end face of the loop structure of the first induction coil structure is configured to have an overlapping face with the second induction coil structure.

14. The implantable hearing aid system according to claim 1, wherein the external unit comprises a shielding unit configured to magnetically shield the electronic unit and other units of the external unit from unwanted external electromagnetic fields provided by the first induction coil structure.

15. The implantable hearing aid system according to claim 1, comprising at least a further ear hook comprising a first secondary induction coil structure, and wherein the electronic unit is configured to be connected to the first induction coil structure and the first secondary induction coil structure.

16. The implantable hearing aid system according to claim 15, wherein the implantable unit comprises at least a second secondary induction coil structure configured to form a further transcutaneous link with the loop structure of the first secondary induction coil structure and to receive power and / or data signals from the first secondary induction coil structure via the further transcutaneous link, wherein the second secondary induction coil structure is configured to be implanted completely or partially within a portion of the user's ear.

17. The implantable hearing aid system according to claim 1, wherein the external unit is a behind-the-ear hearing aid.

18. The implantable hearing aid system of claim 11 or 12, wherein, At least a portion of the first induction coil structure is arranged within or in the vicinity of the through hole of the second induction coil structure when the external unit is worn at the user's ear.

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