Hearing aid

Abstract

The present application discloses a hearing aid comprising a rechargeable battery and a charging interface configured to mechanically interface with a charger device to establish contact charging wherein the charging interface is configured to comprise a plurality of pins, each pin configured to extend through a respective opening of a hearing aid housing, wherein the charging interface is disposed on a substrate having a flexible portion such that the charging interface is disposed at an angle in the range of 70 to 90 degrees with respect to an adjacent substrate portion, and wherein the substrate portion carrying the charging interface and the adjacent substrate portion are formed as a single substrate.

Description

Technical Field

[0001] The present invention relates to the field of hearing aids. More particularly, the present invention relates to rechargeable hearing aids, ie hearing aids having a rechargeable battery, such as an accumulator.

[0002] In one aspect, the present application relates to a hearing device or hearing aid having a contact interface configured for rapid charging of the hearing device or hearing instrument. The interface enables direct contact with the circuitry of the hearing device while also ensuring sealing inside the hearing device, resulting in a compact design and being optimized to compensate for production tolerances. Background Art

[0003] For fast charging of small electronic devices such as hearing aids, direct access to the hearing aid's circuitry is required. Summary of the Invention

[0004] The contact interface also provides access to the hearing aid for initial programming of the hearing aid at the time of manufacture.

[0005] The present invention provides a concept for integrating a contact interface into a hearing aid for contact charging and programming. Charging with high currents (fast charging) requires direct contact from the charger to the hearing device. Therefore, a contact interface is essential that is wear-resistant, corrosion-resistant, easily accessible, and compact.

[0006] The present invention provides a hearing aid charger configured to charge a hearing aid as provided herein. The hearing aid charger includes a hearing aid holder configured to receive at least a portion of a hearing aid to be charged. The hearing aid charger may be provided in a variety of different shapes and sizes. Advantageously, the hearing aid charger may include an internal power supply, such that the hearing aid charger can charge the hearing aid without being connected to a mains power supply.

[0007] The hearing aid receptacle may be shaped to include a charger interface configured to engage with a charging interface of the hearing aid when the hearing aid is located in the hearing aid receptacle, the charger interface including a spring that acts as an electrical conductor during charging.

[0008] The hearing aid holder may be shaped or formed to include first and second magnets configured to interact with the first and second metal pieces of the hearing aid to be charged. In this way, a more reliable connection may be established during charging of the hearing aid.

[0009] The present invention provides a hearing aid with an interface that allows access to the contact pins from outside the hearing aid while ensuring a sealed hearing aid (i.e., preventing water and / or sweat and / or earwax from reaching the hearing aid's electronic circuitry from outside). Furthermore, the hearing aid according to the present invention allows / ensures that production tolerances are compensated and positional tolerances of the charging pins are minimized. Fast charging of small devices is optimally achieved via the interface with a robust contact charging system, which also applies to the charger.

[0010] In one aspect of the present application, a hearing aid comprising a contact charging interface is provided. The hearing aid comprises a rechargeable battery and a charging interface configured to mechanically interface with a charger device to establish contact charging. The hearing aid according to the present invention may be configured such that the charging interface comprises a plurality of pins extending through corresponding openings in the hearing aid housing. This may comprise a relatively small extension from the housing so that the charger interface pins are not felt by the user when wearing the hearing aid. The tips of the pins may be substantially flush with the housing. Preferably, the pins do not contact the user's skin when the hearing aid is mounted at the user's ear, for example when the hearing aid is in its intended position.

[0011] In this specification, the term housing is used. The housing can be, for example, of a type that is assembled from two or more parts to create an enclosed cavity in which the electronic circuitry and / or battery of the hearing aid is stored. Alternatively, the housing can be at least partially composed of a material that encapsulates (a portion of) the electronic circuitry and / or the battery. The encapsulated electronic circuitry portion can be arranged in a housing composed of two or more parts. In addition, the encapsulated electronic circuitry and battery can constitute the exterior of the hearing aid, for example, the in-ear portion with the output transducer. This portion can be connected to the behind-the-ear portion or can be the only part of the hearing aid.

[0012] The hearing aid according to the present invention can be configured such that the charging interface further comprises programming pads configured to serve as the programming interface of the hearing aid, the housing comprising openings at the programming pads. These pads can be flat pieces provided on a substrate (preferably the same substrate as the charging interface).

[0013] A hearing aid according to the present invention can be configured such that the charging interface (and possibly the programming interface) is disposed on a substrate having a flexible portion, such that the charging interface is disposed at an angle in the range of 70 to 90 degrees relative to an adjacent substrate portion, wherein the substrate portion carrying the charging interface and the adjacent substrate portion are formed as a single substrate. This portion can be provided with a seal to prevent earwax and other contaminants from entering the hearing aid housing through the area where the charging interface is exposed to the environment. The seal can provide a continuous seal around the area / substrate carrying the charging interface.

[0014] The hearing aid according to the present invention can be configured such that a rubber spacer is provided between the portion of the substrate carrying the charging interface and the structural portion of the hearing aid housing and / or the battery compartment and / or the battery. This spacer can provide an additional function of stabilizing the area of the substrate carrying the charging interface and / or programming pads.

[0015] The hearing aid according to the present invention can be configured such that the rubber spacer receives (at least a portion of) the substrate portion carrying the charging interface. At least the rubber spacer can be configured to abut a surface of the substrate portion. Thus, the rubber spacer can also ensure that the substrate portion carrying the charging interface is fixed perpendicular to the substrate surface.

[0016] The hearing aid according to the present invention may be configured such that the substrate portion carrying the charging interface is held in a predetermined position by a wall portion of the hearing aid housing. The wall portion may include an extension of the wall side, such as a snap-on portion or the like.

[0017] The hearing aid according to the present invention may be configured such that the hearing aid housing comprises a detachable cover arranged at the opening at the programming pad. The cover can be removed by hand or using a tool.

[0018] The hearing aid according to the invention may be configured such that the cover is colour coded to visually indicate whether the hearing aid is intended for use in the right or left ear of a user. This may be a red / blue colour coding.

[0019] The hearing aid according to the present invention may be configured such that the hearing aid is constituted by or includes an air conduction hearing aid, a bone conduction hearing aid, or a combination thereof.

[0020] The hearing aid according to the present invention may be configured such that two metal sheets are provided at one end of the hearing aid housing and are configured to engage with magnets of the charging device to provide a retaining force that holds the hearing aid in place in the charger during charging.

[0021] In one aspect, the present invention also relates to a hearing aid charger configured to charge the hearing aid disclosed herein.

[0022] A hearing aid according to the present invention may be adapted to provide frequency-dependent gain and / or level-dependent compression and / or frequency transposition of one or more frequency ranges to one or more other frequency ranges (with or without frequency compression) to compensate for a hearing impairment of a user. The hearing aid may comprise a signal processor for enhancing an input signal and providing a processed output signal.

[0023] The hearing aid may comprise an output unit for providing a stimulus perceived by the user as an acoustic signal based on the processed electrical signal. The output unit may comprise a vibrator of a bone conduction hearing aid. The output unit may comprise an output transducer. The output transducer may comprise a receiver (loudspeaker) for providing the stimulus as an acoustic signal to the user (e.g. in an acoustic (air conduction based) hearing aid). The output transducer may comprise a vibrator for providing the stimulus as a mechanical vibration of the skull to the user (e.g. in a bone attached or bone anchored hearing aid). The output unit may (in addition or as an alternative) comprise a (e.g. wireless) transmitter for transmitting the sound picked up by the hearing aid (e.g. via a network, e.g. in telephone operating mode, or in a headset configuration) to another device, such as a remote communication partner.

[0024] The hearing aid may include an input unit for providing an electrical input signal representing sound. The input unit may include an input transducer, such as a microphone, for converting the input sound into the electrical input signal. The input unit may include a wireless receiver for receiving a wireless signal including or representing sound and providing the electrical input signal representing the sound.

[0025] The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the radio frequency range (3 kHz to 300 GHz), for example. The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the optical frequency range (e.g., infrared light 300 GHz to 430 THz or visible light such as 430 THz to 770 THz), for example.

[0026] A hearing aid may include a directional microphone system adapted to spatially filter ambient sound to enhance a target sound source among multiple sound sources in the local environment of a user wearing the hearing aid. The directional system may be adapted to detect (e.g., adaptively detect) the direction from which a particular portion of the microphone signal originates. This can be achieved in a variety of different ways, such as those described in the prior art. In hearing aids, microphone array beamformers are commonly used to spatially attenuate background noise sources. The beamformer may include a linearly constrained minimum variance (LCMV) beamformer. Many beamformer variants are available in the literature. Minimum variance distortionless response (MVDR) beamformers are widely used in microphone array signal processing. Ideally, an MVDR beamformer leaves the signal from the target direction (also known as the line-of-sight direction) unchanged while maximally attenuating sound signals from other directions. The generalized sidelobe canceler (GSC) structure is an equivalent representation of the MVDR beamformer, offering computational and digital representation advantages over a direct implementation of the original form.

[0027] Most sound signal sources (except the user's own voice) are relatively small compared to the size of the hearing aid, such as the distance d between the two microphones of a directional system. mic Located away from the user. The typical microphone distance in a hearing aid is on the order of 10 mm. The minimum distance from the user's sound source of interest (e.g., the sound from the user's mouth or the sound from the audio transmission device) is 0.1 m (>10 d mic ) level. For such a minimum distance, the hearing aid (microphone) will be in the acoustic near field of the sound source and the level difference of the sound signal incident on the respective microphones may be significant. The typical distance of the communication partner is greater than 1m (>100d mic The hearing aid (microphone) will be in the acoustic far field of the sound source, and the level difference of the sound signals incident on the corresponding microphones will not be obvious. The arrival time difference of the sound incident in the direction of the microphone axis (for example, in front of or behind a normal hearing aid) is ΔT = d mic / v sound=0.01 / 343[s]=29μs, where v sound The speed of sound in air at 20°C (343 m / s).

[0028] The hearing aid may include an antenna and transceiver circuitry that enables a wireless link to an entertainment device (e.g., a television), a communication device (e.g., a telephone), a wireless microphone, a separate (external) processing device, or another hearing aid. The hearing aid may thus be configured to wirelessly receive a direct electrical input signal from another device. Similarly, the hearing aid may be configured to wirelessly transmit a direct electrical output signal to another device. The direct electrical input or output signal may represent or include an audio signal and / or a control signal and / or an information signal.

[0029] In general, the wireless link established by the antenna and transceiver circuitry of the hearing aid may be of any type. The wireless link may be a link based on near field communication, for example an inductive link based on inductive coupling between antenna coils of a transmitter part and a receiver part. The wireless link may be based on far-field electromagnetic radiation. Preferably, the frequency used to establish the communication link between the hearing aid and the other device is below 70 GHz, for example in the range from 50 MHz to 70 GHz, for example above 300 MHz, for example in the ISM range above 300 MHz, for example in the 900 MHz range or in the 2.4 GHz range or in the 5.8 GHz range or in the 60 GHz range (ISM = Industrial, Scientific and Medical, such standardized ranges are defined, for example, by the International Telecommunication Union ITU). The wireless link may be based on standardized or proprietary technologies. The wireless link may be based on Bluetooth technology (for example Bluetooth Low Energy technology, for example LE Audio) or Ultra-Wideband (UWB) technology.

[0030] The hearing aid may consist of or may form part of a portable (ie configured to be wearable) device, eg a device comprising a local energy source such as a battery, eg a rechargeable battery.

[0031] The hearing aid may for example be a low-weight, easily wearable device, for example having a total weight of less than 100 g, such as less than 20 g, for example less than 5 g.

[0032] A hearing aid may include a "forward" (or "signal") path between the input and output of the hearing aid for processing audio signals. A signal processor may be located in this forward path. The signal processor may be adapted to provide frequency-dependent gain according to the specific needs of the user (e.g., hearing loss). The hearing aid may include an "analysis" path having functional components for analyzing signals and / or controlling processing of the forward path. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the frequency domain, in which case the hearing aid includes appropriate analysis and synthesis filter banks. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the time domain.

[0033] The analog electrical signal representing the acoustic signal can be converted into a digital audio signal in an analog-to-digital (AD) conversion process, where the analog signal is sampled at a predetermined frequency or sampling rate f. s Sampling, f s For example, in the range from 8 kHz to 48 kHz (adapted to the specific needs of the application) at discrete time points t n (or n) provides digital samples x n (or x[n]), each audio sample is passed through a predetermined N b The bit represents the sound signal at t n The value when N b For example, in the range from 1 to 48 bits, such as 24 bits. Each audio sample thus uses N b bit quantization (resulting in 2 Nb different possible values). A digital sample x has a 1 / f s The length of time, such as 50μs, for f s = 20kHz. Multiple audio samples can be arranged in time frames. A time frame can include 64 or 128 audio data samples. Other frame lengths can be used depending on the actual application.

[0034] The hearing aid may include an analog-to-digital (AD) converter to digitize an analog input (e.g., from an input transducer such as a microphone) at a predetermined sampling rate, such as 20 kHz. The hearing aid may also include a digital-to-analog (DA) converter to convert the digital signal into an analog output signal, such as for presentation to the user via an output transducer.

[0035] The hearing aid, such as the input unit and / or the antenna and the transceiver circuit, may comprise a transform unit for converting a time domain signal into a signal in a transform domain (e.g. the frequency domain or the Laplace domain, a Z transform, a wavelet transform, etc.). The transform unit may be constituted by or include a time-frequency (TF) transform unit for providing a time-frequency representation of the input signal. The time-frequency representation may comprise an array or mapping of corresponding complex or real values of the signal in question in a specific time and frequency range. The TF transform unit may comprise a filter bank for filtering the (time-varying) input signal and providing a plurality of (time-varying) output signals, each output signal comprising a distinct frequency range of the input signal. The TF transform unit may comprise a Fourier transform unit (e.g. a discrete Fourier transform (DFT) algorithm, a short-time Fourier transform (STFT) algorithm, or a similar algorithm) for converting the time-varying input signal into a (time-varying) signal in the (time-)frequency domain. The frequency domain considered by the hearing aid, from the minimum frequency f min To the maximum frequency f maxThe frequency range of may include a portion of the typical human hearing range from 20 Hz to 20 kHz, for example a portion of the range from 20 Hz to 12 kHz. Typically, the sampling rate f s Greater than or equal to the maximum frequency f max twice, that is, f s ≥2f max The signals of the forward and / or analysis paths of the hearing aid may be split into NI frequency bands (e.g., of uniform width), where NI is, for example, greater than 5, such as greater than 10, such as greater than 50, such as greater than 100, such as greater than 500, at least parts of which are processed separately. The hearing aid may be adapted to process the signals of the forward and / or analysis paths in NP different frequency channels (NP ≤ NI). The frequency channels may be of uniform or non-uniform width (e.g., increasing width with frequency), overlapping or non-overlapping.

[0036] A hearing aid can be configured to operate in different modes, such as a normal mode and one or more special modes, which can be selected by the user or automatically. The operating modes can be optimized for specific acoustic situations or environments, such as a communication mode, for example, a telephone mode. The operating modes can include a low-power mode, in which the functionality of the hearing aid is reduced (e.g., to save energy), such as disabling wireless communication and / or disabling specific features of the hearing aid.

[0037] The hearing aid may include a plurality of detectors configured to provide status signals related to the current network environment of the hearing aid (e.g., the current acoustic environment), and / or the current state of the user wearing the hearing aid, and / or the current state or operating mode of the hearing aid. Alternatively or additionally, one or more of the detectors may form part of an external device that communicates with the hearing aid (e.g., wirelessly). The external device may include, for example, another hearing aid, a remote control, an audio transmission device, a phone (e.g., a smartphone), an external sensor, etc.

[0038] One or more of the plurality of detectors may operate on a full-band signal (time domain). One or more of the plurality of detectors may operate on a band-split signal ((time-)frequency domain), eg in a limited number of frequency bands.

[0039] The plurality of detectors may include a level detector for estimating the current level of the signal in the forward path. The detector may be configured to determine whether the current level of the signal in the forward path is above or below a given (L-)threshold. The level detector operates on the full-band signal (time domain). The level detector operates on the band-split signal ((time-)frequency domain).

[0040] A hearing aid may include a voice activity detector (VAD) for estimating whether (or with what probability) an input signal (at a given point in time) includes a voice signal. In this specification, a voice signal may be understood to include a speech signal from a human. It may also include other forms of vocalizations (such as singing) produced by the human speech system. The voice activity detector unit may be adapted to classify the user's current acoustic environment as a "voice" or "no-voice" environment. This has the advantage that time periods containing electrical microphone signals of human vocalizations (such as speech) in the user's environment can be identified and thus separated from time periods containing only (or primarily) other sound sources (such as artificially generated noise). The voice activity detector may be adapted to also detect the user's own voice as "voice." Alternatively, the voice activity detector may be adapted to exclude the user's own voice from the "voice" detection.

[0041] A hearing aid may include a self-voice detector for estimating whether (or with what probability) a particular input sound (e.g., voice, such as speech) originates from the voice of a user of the hearing system. The microphone system of the hearing aid may be adapted to be able to distinguish the user's own voice from the voice of another person and possibly from unvoiced sounds.

[0042] The plurality of detectors may include a motion detector such as an accelerometer. The motion detector may be configured to detect movement of the user's facial muscles and / or bones, such as due to speech or chewing (eg, jaw movement), and provide a detector signal indicative of the movement.

[0043] The hearing aid may comprise a classification unit configured to classify a current situation based on an input signal from (at least part of) the detector and possibly other inputs. In this specification, a "current situation" may be defined by one or more of the following:

[0044] a) the physical environment (e.g., including the current electromagnetic environment, such as the presence of electromagnetic signals (including audio and / or control signals) intended or unintended for reception by the hearing aid, or other properties of the current environment other than acoustics);

[0045] b) Current acoustic conditions (input level, feedback, etc.);

[0046] c) the user’s current mode or state (motion, temperature, cognitive load, etc.);

[0047] d) The current mode or status of the hearing aid and / or another device communicating with the hearing aid (selected program, time elapsed since last user interaction, etc.).

[0048] The classification unit may be based on or may comprise a neural network, such as a recurrent neural network, such as a trained neural network.

[0049] Hearing aids may include acoustic (and / or mechanical) feedback control (e.g., suppression) or an echo cancellation system. Adaptive feedback cancellation has the ability to track changes in the feedback path over time. It is typically based on a linear time-invariant filter to estimate the feedback path, but the filter weights are updated over time. The filter updates can be calculated using a stochastic gradient algorithm, including some form of least mean square (LMS) or normalized LMS (NLMS) algorithm. They all have the property of minimizing the difference signal in terms of mean square, with NLMS additionally normalizing the filter updates by the square of the Euclidean norm of a reference signal.

[0050] The hearing aid may also include other appropriate functions for the application in question, such as compression, noise reduction, etc.

[0051] A hearing aid may comprise a hearing instrument, such as a hearing instrument adapted to be positioned at the ear of a user or fully or partially positioned in the ear canal, such as an earphone, a headset, an ear protection device, or a combination thereof. A hearing system may comprise a loudspeaker amplifier (comprising a plurality of input transducers (e.g. a microphone array) and a plurality of output transducers such as one or more loudspeakers, and one or more audio (and possibly video) transmitters, such as for use in an audio conferencing situation), such as comprising a beamformer filter unit, such as to provide multiple beamforming capabilities.

[0052] In another aspect, there is provided a hearing aid comprising the device described above, in detail in the "Detailed Description of the Invention" and in the claims, and a hearing system comprising an auxiliary device.

[0053] The hearing system may be adapted to establish a communication link between the hearing aid and the auxiliary device so that information (eg control and status signals, possibly audio signals) can be exchanged or forwarded from one device to the other.

[0054] The auxiliary device may include or may consist of a remote control, a smart phone, or other portable or wearable electronic device such as a smart watch.

[0055] The auxiliary device may consist of or include a remote control for controlling the functions and operation of the hearing aid. The functions of the remote control are implemented in a smartphone, which may run an app that enables the functions of the audio processing device to be controlled via the smartphone (the hearing aid includes a suitable wireless interface to the smartphone, for example based on Bluetooth or some other standardized or proprietary solution).

[0056] The auxiliary device may be constituted by or include an audio gateway device, which is suitable for receiving multiple audio signals (for example from an entertainment device such as a TV or music player, from a telephone device such as a mobile phone, or from a computer such as a PC, a wireless microphone, etc.) and is suitable for selecting and / or combining appropriate signals (or signal combinations) from the received audio signals for transmission to the hearing aid.

[0057] The auxiliary device may consist of or may comprise a further hearing aid.The hearing system may comprise two hearing aids adapted to implement a binaural hearing system, eg a binaural hearing aid system.

[0058] definition

[0059] As used herein, a hearing aid, such as a hearing instrument, refers to a device adapted to improve, enhance, and / or protect a user's hearing ability by receiving acoustic signals from the user's environment, 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 may be provided, for example, in the form of acoustic signals radiated into the user's outer ear and / or acoustic signals transmitted as mechanical vibrations through the bony structure of the user's head and / or through portions of the middle ear to the user's inner ear.

[0060] The hearing aid can be configured to be worn in any known manner, such as as a unit worn behind the ear (with a tube that directs the radiated acoustic signal into the ear canal or with an output transducer, such as a loudspeaker, arranged close to or in the ear canal), as a unit arranged entirely or partially in the auricle and / or ear canal, as a unit connected to a fixed structure implanted in the skull, such as a vibrator, etc. The hearing aid can comprise a single unit or several units that communicate with each other (e.g., acoustically, electrically, or optically). The loudspeaker can be arranged in the housing together with the other components of the hearing aid, or it can itself be an external unit (possibly in combination with a flexible guiding element, such as a dome-shaped element).

[0061] Hearing aids can be adapted to the needs of specific users, such as hearing loss. The configurable signal processing circuitry of the hearing aid can be adapted to apply frequency- and level-dependent compression and amplification of the input signal. The customized frequency- and level-dependent gain (amplification or compression) can be determined during the fitting process by the fitting system based on the user's hearing data, such as an audiogram, using basic fitting principles (e.g., adaptation to speech). The frequency- and level-dependent gain can, for example, be reflected in processing parameters, uploaded to the hearing aid via an interface to a programming device (fitting system), and used by a processing algorithm executed by the configurable signal processing circuitry of the hearing aid.

[0062] A "hearing system" refers to a system that includes one or two hearing aids. A "binaural hearing system" refers to a system that includes two hearing aids and is adapted to collaboratively provide audible signals to both ears of a user. A hearing system or binaural hearing system may also include one or more "auxiliary devices" that communicate with the hearing aids and influence and / or benefit from the hearing aids' functionality. Such auxiliary devices may include at least one of the following: a remote control, a remote microphone, an audio gateway device, an entertainment device such as a music player, a wireless communication device such as a mobile phone (e.g., a smartphone) or a tablet, or another device, such as one that includes a graphical interface. A hearing aid, hearing system, or binaural hearing system may be used, for example, to compensate for the hearing loss of a hearing-impaired person, enhance or protect the hearing ability of a person with normal hearing, and / or transmit electronic audio signals to a person. A hearing aid or hearing system may, for example, form part of or interact with a public address system, active ear protection system, hands-free phone system, car audio system, entertainment (e.g., television, music playback, or karaoke) system, teleconferencing system, classroom amplification system, and the like. BRIEF DESCRIPTION OF THE DRAWINGS

[0063] Various aspects of the present invention will be best understood from the following detailed description in conjunction with the accompanying drawings. For clarity, the drawings are schematic and simplified, showing only the details necessary for understanding the present invention and omitting other details. Throughout the specification, the same reference numerals are used for identical or corresponding parts. The various features of each aspect may be combined with any or all features of the other aspects. These and other aspects, features, and / or technical effects will be apparent from and elucidated in conjunction with the following figures, in which:

[0064] Figure 1 schematically shows a block diagram of a hearing aid;

[0065] Figure 2 schematically shows a block diagram of a hearing aid with external processing;

[0066] Figure 3 Schematically illustrates a hearing aid as described herein;

[0067] Figure 4 Schematically shows a hearing aid described herein placed in a charger;

[0068] Figure 5 The hearing aid described here is schematically shown in three figures, in which the charger interface and the programming interface are visible;

[0069] Figure 6 Schematically illustrates a hearing aid as described herein, wherein a rubber spacer is placed between the substrate portion carrying the charging interface and the housing portion;

[0070] Figure 7A hearing aid described herein is schematically shown, wherein different installation states of the charging interface are shown;

[0071] Figure 8 Schematically illustrates the pins of the charging interface disclosed herein;

[0072] Figure 9 Schematically shows the hearing aid described herein with two metal pieces and its insertion into a charger;

[0073] Figure 10 Schematically shows how a hearing aid according to the present invention differs from a conventional hearing aid;

[0074] Figure 11 The force-displacement curves of a conventional hearing aid and a hearing aid according to the present invention are schematically shown.

[0075] By the detailed description provided below, the further scope of application of the present invention will be apparent. However, it should be understood that while the detailed description and specific examples indicate the preferred embodiments of the present invention, they are provided for illustrative purposes only. For those skilled in the art, based on the following detailed description, other embodiments of the present invention will be apparent. DETAILED DESCRIPTION

[0076] The detailed description presented below in conjunction with the accompanying drawings serves as a description of a variety of different configurations. The detailed description includes specific details for providing a thorough understanding of a plurality of 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 a plurality of different blocks, functional units, modules, components, circuits, steps, processes, algorithms, etc. (collectively referred to as "elements"). Depending on the specific application, design limitations or other reasons, these elements may be implemented using electronic hardware, computer programs or any combination thereof.

[0077] The electronic hardware may include microelectromechanical systems (MEMS), (e.g., application specific) integrated circuits, microprocessors, microcontrollers, digital signal processors (DSPs), field programmable gate arrays (FPGAs), programmable logic devices (PLDs), gating logic, discrete hardware circuits, printed circuit boards (PCBs) (e.g., flexible PCBs), and other suitable hardware configured to perform the various functions described in this specification, such as sensors for sensing and / or recording physical properties of the environment, device, user, etc. A computer program shall be construed broadly to mean instructions, an instruction set, code, a code segment, program code, a program, a subroutine, a software module, an application, a software application, a software package, a routine, a subroutine, an object, an executable, a thread of execution, a program, a function, or the like, whether referred to as software, firmware, middleware, microcode, a hardware description language, or otherwise.

[0078] The present invention relates to the field of hearing aids.

[0079] Figure 1 An exemplary block diagram of a hearing device HD, such as a hearing aid, is shown, comprising a noise reduction system NRS for compensating for hearing impairment of a user of the hearing device and a hearing aid (audio) processor HAG. The hearing device comprises an input unit IU for picking up sound s from the environment (e.g. via M input transducers such as microphones). in And provide multiple (M, M>1) electrical input signals (S1,…,S M ), the noise reduction system NRS is used to estimate the input sound s based on the electric input signal and optionally further information such as a mode control signal ("mode") in The target signal in The mode selection input ("mode") may be configured to indicate an operating mode and / or filter coefficient update strategy of a beamformer of a system, e.g., a noise reduction system NRS, e.g., depending on whether the target signal is the user's own voice or a target signal from the user's environment (possibly also indicating the direction or position of the target sound source). The mode control signal may, for example, be provided from a user interface, e.g., from a remote control (e.g., implemented as an APP on a smartphone or similar device, such as a smartwatch). The mode control signal ("mode") may, for example, be automatically generated, e.g., using one or more sensors, e.g., activated by receiving a wireless signal, e.g., from a phone. The output of the noise reduction system NRS may be an estimate of the user's voice. or an estimate of the target sound from the environment The hearing device, such as a hearing aid or headphones, further comprises an (audio) processor PRO for applying one or more processing algorithms to the signal in the forward path from the input to the output, for example (here) to an estimate of the target signal provided by the noise reduction system. (For example, by time-frequency representation This can be done, for example, by a corresponding analysis filter bank (forming, for example, the input unit IU MIC part, possibly together with a corresponding analog-to-digital converter, as appropriate), thereby providing an electrical input signal (S1, ..., S) in a time-frequency representation (k, n) M ), k and n are frequency index and time index respectively. One or more processing algorithms may include, for example, a compression algorithm configured to amplify (or attenuate) the signal according to the needs of the user, for example to compensate for the user's hearing loss. Other processing algorithms may include frequency shifting, feedback control, etc. The processor PRO provides a processed output OUT, which is fed to the synthesis filter bank FBS to convert from a time-frequency representation (frequency domain) to the time domain. The time domain output signal out is fed to the output unit OU to be converted into a stimulus s that can be perceived by the user as sound out("output sound") such as acoustic vibrations (e.g. in the air and / or in the skull), the synthesis filter bank FBS may be omitted. In non-hearing aid applications such as headphones, the processor may be configured to further enhance the signal from the noise reduction system or omit it (making the estimate of the target signal The target signal may be the user's own voice, and / or a target sound in the user's environment (e.g. a person (different from the user) speaking, e.g. communicating with the user).

[0080] Figure 2 An embodiment of a hearing device HD hearing aid configured to be worn at or in an ear of a user is shown, together with a separate, external, possibly body-worn audio processing device APD configured to be worn or carried by the user (or at least positioned sufficiently close to the user to maintain communication with the earpiece via a wireless link WL implemented by transceivers Tx / Rx of the respective devices). The audio processing device APD comprises a computing device CPD apd For example, an audio signal processor or similar device.

[0081] The hearing device comprises (at least one) input transducer (here a microphone M for converting a sound in the environment of the hearing device into an acoustically received electrical input signal y(n) (n being a possible time variation) representing the sound). The hearing device further comprises a wireless transmitter Tx for transmitting the acoustically received electrical input signal y(n) or a part thereof (e.g. a filtered part, such as a low-pass filtered part) to an audio processing device APD. The hearing device further comprises a wireless receiver Rx for receiving a processed signal z(n) from the audio processing device, at least in a normal operating mode of the hearing device. The wireless transmitter and receiver (Tx, Rx) may be provided as an antenna and a transceiver circuit for establishing an audio communication link WL in accordance with a standardized or proprietary (short-range) protocol. The hearing device further comprises an output transducer (here a loudspeaker SPK) for outputting the (final) processed signal (s') to the audio processing device APD. out (n) is converted into a stimulus perceived by the user as sound. The processed signal s' out (n) may consist of or may comprise at least a portion of the processed signal z(n) provided by the audio processing device, at least in a normal operating mode of the hearing device. Alternatively (or in a separate "stand-alone" mode), the processed signal s' out (n) may be formed by a processed signal provided by the earpiece itself (in which case it may comprise suitable means for processing the electrical input signal y(n) and converting the processed signal s' outOptional processing of the acoustically received signal y(n) may, for example, be of interest in operating modes in which no contact with the audio processing device APD can be established (e.g. in order to provide the user with basic functionality of the hearing device (e.g. hearing loss compensation)).

[0082] The audio processing device APD comprises a wireless receiver Rx for receiving an acoustically received electric input signal y(n) or a part thereof from the earpiece EP and is configured to provide a received signal representative of the signal. apd ) further comprises a (hearing aid) processor part HAP for applying a processing algorithm (e.g. comprising a neural network) to the received signal or a signal derived therefrom, such as a transformed version Y thereof (e.g. provided by a transformation unit TRF, such as a Fourier transformation unit), and providing a modified signal Y'. The processor part HAP may for example be configured to compensate for a hearing impairment of the user (e.g. by applying a compression-amplification algorithm, e.g. providing a frequency and / or level dependent gain (or attenuation) to be applied to the input signal (y'(n) or Y)). In Figure 2 In an embodiment of the present invention, the audio processing device APD (eg, the computing device CPD apd ) comprises corresponding transform domain units and inverse transform domain units (TRF, I-TRF) for converting a time domain signal (here the signal y'(n) received from the earpiece) into a transform domain (e.g. the time-frequency domain), see signal Y, and then converting it back into the time domain again (here the processed signal Y' in the transform domain into z(n) in the time domain).

[0083] The signal transmitted from the hearing device to the (external) audio processing device APD and / or from the audio processing device APD to the hearing device via the wireless link WL does not necessarily have to be the aforementioned "audio signal." It can also be a feature derived from the audio signal. For example, instead of transmitting the audio signal back to the hearing device, a gain derived from the predicted signal can be transmitted back to the earpiece and applied to a suitably processed version (e.g., a delayed version) of the electrical input signal y(n).

[0084] The term "processed version" may, for example, cover features extracted from an original audio signal. The term "processed version" may also, for example, cover an original audio signal that has been subjected to a processing algorithm that applies a gain or attenuation and / or a delay to the original audio signal and results in a modified audio signal (preferably enhanced in some way, e.g., noise reduced relative to a target signal, or simply delayed).

[0085] Figure 3The schematic diagram shows a hearing instrument with charging pins and a color-coded cover for the programming interface. Two charging pins 12 are visible, which connect to contact springs in the charger. A cover 14 is positioned over a set of programming interface pads. Here, there are two programming pads. Other numbers of pads may also be used.

[0086] Figure 4 The metal spring is configured to apply force towards the charging port of the hearing aid to establish a reliable contact during charging, pressing against the charging pins to create contact for charging.

[0087] Figure 5 Schematic diagram of a hearing instrument with visible charging pins and color-coded covering of the programming interface (top). The charging pins and programming pads on the PCB are visible through the housing (bottom). In the leftmost image, the hearing aid housing has been removed, in the middle image, the hearing aid housing is transparent, and in the rightmost image, the housing is seen from the user's perspective, but with the programming pad cover removed.

[0088] The programming interface includes two pads on the top, one for clock and the other for data. One of the charging interface pins is used for negative contact and the other for positive contact.

[0089] The hearing aid interface consists of the following parts (see the figure below):

[0090] - Charging pins, used for contact charging, soldered to the hearing aid amplifier using a pick and place process (SMD process);

[0091] - Contact pads, used for programming hearing instruments, gold pads on the PCB;

[0092] - a rubber seal that ensures the tightness between the housing and the amplifier;

[0093] - a spacer, which may be a rubber or foam part, which is compressed and ensures that the charging pad is pressed against the inside of the housing and the sealing lip of the sealing part is compressed;

[0094] - A portion covering the programming interface, which can be used to cover the programming pads. This portion is not required, but makes the hearing instrument more visually appealing. The programming pads are only used during production.

[0095] - Magnets inside the charger, which pull the hearing aids into the charger;

[0096] - Metal tabs in the housing, which are used to pull the hearing instrument into the charger.

[0097] Figure 6 A cross-section of a hearing aid is schematically shown, illustrating the charging interface and the programming interface.

[0098] In the upper left figure, the rubber spacer is placed into the bracket of the hearing aid, ie into a structural part of the hearing aid housing, more precisely, into the inner part or bracket arranged in the hearing aid housing.

[0099] The interface according to the present invention provides at least the following advantages:

[0100] -The charging pins can be assembled using SMD technology (pick and place machines place components on the PCB);

[0101] -Hearing instruments are easy to assemble;

[0102] -Can be integrated into future hearing aids as a "charging and programming module";

[0103] - Two contacts allow the hearing instrument to be charged by placing it in a charger;

[0104] - Two contacts that can be accessed with a probe during production to enable programming of the hearing instrument. These two contacts are placed inside the hearing instrument and can be hidden under a removable part (here color-coded);

[0105] The position of the charging pin is controlled by the hearing instrument housing, which ensures a short tolerance chain and thus minimizes tolerances in the position of the charging pin tip, which has an impact on the displacement of the charger spring within the charger device. This displacement is a result of the spring force, which is necessary to minimize the contact resistance between the battery spring and the charging pin.

[0106] Charging a hearing aid requires physical contact with the charging pins with minimal contact resistance. Therefore, a certain force must be applied to press the contacts together. This is achieved using a contact spring, as shown in the diagram below. When the hearing device is inserted into the charger, a magnet pulls the metal tab into the cavity. The spring slides over the charging pins and displaces, resulting in a spring force pressing against the contacts. To ensure low contact resistance, this force should be as high as possible. The upper limit of this force is set by the magnetic force pulling the hearing aid into the charger.

[0107] This results in a tight window of contact force. The position of the charging pads has a significant impact on the resulting spring force: if they are further inside the hearing instrument, the spring force is lower; if they are further outside, the spring force increases. The same is true for the position of the contact spring. Therefore, the position of the charging pads and charging springs should have tight tolerances to ensure a constant and controlled spring force (production tolerances).

[0108] The spring in the charger is preloaded against the charger cavity. This ensures the correct position of the charging spring in the cavity and further increases the minimum spring force.

[0109] The end of the charging pad needs to be between 0 mm and +0.2 mm from the housing surface. To shorten the tolerance chain, the seal is pressed against the basic housing. In this stacking, the seal body is assumed to be rigid, with only the seal edge deforming.

[0110] Figure 7 The diagram schematically illustrates the assembly of the various components into a hearing aid. Specifically, the charger connector pins are located on the flexible, upper-leftmost region or island of the substrate. This region extends vertically, and a rubber member is positioned where this region or island is located, as shown in the right-hand image. The right-hand image shows the region or island in contact with the rubber member, thereby supporting it. The assembled components are then enclosed in a housing.

[0111] Figure 8 The figure schematically shows the pins of the charging interface according to the present invention.

[0112] Previous hearing aids had four programming pads, requiring four connection points for programming the hearing aid at both the manufacturing and service point. Programming can now be performed using four dedicated pads included on the hearing aid amplifier. These pads can be accessed by opening a portion of the housing, such as the battery drawer or a button. Including this feature in a hearing aid presents some challenges, such as increased size and corrosion risk due to the additional openings.

[0113] In a rechargeable hearing aid, the batteries do not need to be replaced and therefore, features such as a battery drawer are not required. Thus, avoiding a hatch can significantly reduce the overall volume / size of the hearing instrument.

[0114] The present invention provides alternatives, including:

[0115] 1. Combine the programming pad with the charging point;

[0116] Eliminate the need for extra parts such as buttons or battery drawers (which need to be opened / closed to access the required contacts);

[0117] 3. Hide the two programming points under the L / R markings (clock and data);

[0118] 4. Combine L / R markings with covers for clock and data points to improve the hearing instrument aesthetically and reduce the number of parts.

[0119] The rise of rechargeability in hearing instruments has eliminated the need for end-user battery replacement. In other words, the battery is soldered directly to the main PCB / amplifier. Therefore, there's no need for a battery drawer. However, four contact points are still required to provide access in the stand assembly and case-level assembly for R&D, production, and service. These four contact points include positive, ground, clock, and data.

[0120] To provide these four contact points primarily in the housing level assembly, a charging point and two PCB pads are combined. The combination includes two charging points providing positive and ground (negative) connections respectively, with clock and data being exclusively in the PCB pads.

[0121] In addition, the L / R marker is designed to cover two pads on the PCB (clock and data). Therefore, in addition to its main function of indicating the left / right placement of the hearing instrument, the L / R marker also covers pads on the PCB that are not used by the end user.

[0122] To achieve a robust charging system for hearing instruments within a corresponding charger, the ability to attract the hearing instrument toward the bottom of the charger cavity should be controlled. In-ear hearing aids (HIs) contain magnetic elements (magnets / metal sheets / ferrites) that guide them toward the magnetic charger cavity. Including this conventional system within the HI creates several problems:

[0123] 1. Because the metal sheet is placed at the bottom of the hearing instrument (where space is usually limited), it increases the length and overall size of the hearing instrument;

[0124] 2. Industrial design differentiation is very difficult (i.e., it is difficult to have different industrial designs for the same internal architecture) (problematic for branding);

[0125] 3. The tolerance of the magnetic attraction system is difficult to control because the magnetic attraction curve is steep;

[0126] 4. Difficult to implement for sliding contact systems (i.e., limitations on charging contacts and spring placement).

[0127] The hearing aid according to the present invention provides an alternative which:

[0128] 1. Enables large differentiation;

[0129] 2. Production / assembly / material tolerances are controllable;

[0130] 3. Minimal impact on the size of hearing instruments;

[0131] 4. Can be reused in multiple products and hearing aid types.

[0132] exist Figure 9 , a hearing aid is shown from two different angles.

[0133] In contrast to the conventional placement of magnetic elements in the hearing aid and in the charger, the hearing aid according to the present invention uses two metal plates placed on two (opposite) sides of the hearing aid. These two metal plates interact with two adjacent magnets (in the charger).

[0134] As described elsewhere in this specification, the charging interface in a hearing aid consists of two charging pads and two metal tabs. The two charging pads are part of the amplifier, and the metal tabs are mounted on either side of the hearing aid housing. The two charging pads contact two mating springs in the charger. Furthermore, the two metal tabs are attracted by the magnetic field generated by two magnets placed in the charger.

[0135] This configuration enables control and design of the magnetic attraction profile, including peak force location and attraction range.

[0136] A conventional magnet attraction curve includes a peak at the interface between the two components. However, the attraction force decreases dramatically as the distance between the magnetic components (the magnet in the charger and the magnet in the hearing aid) increases. Therefore, to compensate for material, production, and assembly tolerances and ensure adequate attraction, larger metal sheets and / or magnets are required.

[0137] For example, comparing a hearing aid according to the present invention, i.e., an improved hearing aid, and a conventional system with similar magnetic attraction:

[0138] In conventional systems, if there is a 1 mm difference in distance between the magnet and the metal sheet after assembly, up to 50% of the peak magnetic attraction can be lost. However, in a hearing aid according to the present invention, this loss can be less than 5%.

[0139] By placing the magnet and the metal sheet on two (opposite) sides of the hearing aid, the metal sheet slides over the surface of the magnet instead of being more directly adjacent to the magnet. In this new arrangement, the mentioned sharp decrease in attraction is no longer observed. Furthermore, the curve peak and the degree of plateau can be effectively designed and controlled. In other words, the peak of the magnetic attraction can be designed where it should occur. This is in contrast to conventional curves, where the final placement of the hearing instrument in the charger cavity is the peak point. Control of the peak point allows an additional degree of freedom in industrial design and in the positioning of the contact points ... Figure 10 Shown in.

[0140] The system according to the invention offers significant advantages, particularly in sliding contact systems, because the attractive engagement with the hearing instrument begins early (i.e., the hearing instrument is attracted as early as the top of the charger cavity). Thus, for example, the charger contacts can be placed in the middle of the hearing instrument / hearing aid (instead of at the bottom) and still achieve adequate attraction.

[0141] Furthermore, the attraction system improves the charger's usability. Once the hearing aid is near the cavity entrance, it is drawn into the cavity, and the magnets guide it into its proper resting position. This provides the user with improved mechanical assurance that their hearing instrument is properly positioned in the charger.

[0142] Figure 11Schematically shown are the force as a function of displacement for a conventional hearing device and a hearing device / hearing aid according to the present invention.

[0143] The present invention can be characterized by the following items:

[0144] 1. A hearing aid comprising a rechargeable battery and a charging interface configured to mechanically interface with a charger device to establish contact charging, wherein the charging interface is configured to include a plurality of pins extending through corresponding openings in a hearing aid housing.

[0145] 2. The hearing aid according to item 1, wherein the charging interface further comprises a programming pad configured to serve as a programming interface for the hearing aid, and the housing comprises an opening at the programming pad.

[0146] 3. The hearing aid according to item 2, wherein the charging interface and the programming pad are provided on the same substrate.

[0147] 4. A hearing aid according to any one of items 1-3, wherein the charging interface is arranged on a substrate having a flexible portion, so that the charging interface is arranged at an angle in the range of 70 to 90 degrees relative to an adjacent substrate portion, wherein the substrate portion carrying the charging interface and the adjacent substrate portion are formed as a single substrate.

[0148] 5. The hearing aid according to any one of items 1 to 4, wherein a rubber spacer is provided between the substrate portion carrying the charging interface and the structural portion of the hearing aid housing and / or the battery compartment and / or the battery.

[0149] 6. The hearing aid according to item 5, wherein the rubber spacer is configured to receive a portion of the substrate carrying the charging interface.

[0150] 7. The hearing aid according to any of items 5-6, wherein the substrate portion carrying the charging interface is held in the intended position by a wall of the hearing aid housing.

[0151] 8. The hearing aid according to any one of items 2 to 7, wherein the hearing aid housing comprises a removable cover provided at the opening at the programming pad.

[0152] 9. The hearing aid of item 8, wherein the cover is color-coded to visually indicate whether the hearing aid is intended for use in the right or left ear of the user.

[0153] 10. The hearing aid according to any one of items 1 to 9, which is composed of an air conduction hearing aid, a bone conduction hearing aid or a combination thereof, or includes an air conduction hearing aid, a bone conduction hearing aid or a combination thereof.

[0154] 11. The hearing aid according to any one of items 1-10, further comprising two metal plates arranged at one end of the hearing aid housing, which are configured to engage with magnets of the charging device to provide a holding force to keep the hearing aid in the proper position in the charger during charging.

[0155] 12. A hearing aid charger configured to charge the hearing aid according to item 1.

[0156] The structural features of the apparatus described above, described in detail in the "Detailed Description of the Invention" and defined in the claims may be combined with the steps of the method of the present invention when appropriately replaced by corresponding processes.

[0157] Unless expressly stated otherwise, the singular forms "a", "the" and "the" used herein include the plural form (i.e., having the meaning of "at least one"). It should be further understood that the terms "having", "including" and / or "comprising" used in the specification indicate the presence of the described features, integers, steps, operations, elements and / or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and / or combinations thereof. It should be understood that, unless expressly stated otherwise, when an element is referred to as being "connected" or "coupled" to another element, it may be directly connected or coupled to the other element, or there may be an intermediate intervening element. The term "and / or" as used herein includes any and all combinations of one or more listed related items. Unless expressly stated otherwise, the steps of any method disclosed herein do not have to be performed in the exact order disclosed.

[0158] It should be understood that references in this specification to "an embodiment," "an embodiment," "an aspect," or features that "may" include, mean that the specific features, structures, or characteristics described in conjunction with that embodiment are included in at least one embodiment of the present invention. Furthermore, the specific features, structures, or characteristics may be combined as appropriate in one or more embodiments of the present invention. The foregoing description is provided to enable those skilled in the art to practice the various aspects described herein. Various modifications will be apparent to those skilled in the art.

[0159] The claims are not limited to the aspects shown herein, but rather have the full scope consistent with the claim language in which, unless expressly stated otherwise, elements referred to in the singular do not mean "one and only one" but rather "one or more." Unless expressly stated otherwise, the term "some" means one or more.

Claims

1. A hearing aid comprising a rechargeable battery and a charging interface, the charging interface being configured to mechanically interface with a charger device to establish contact charging, wherein the charging interface is configured to include a plurality of pins, each pin being configured to extend through a corresponding opening in a hearing aid housing, wherein the charging interface is disposed on a substrate having a flexible portion such that the charging interface is disposed at an angle in the range of 70 to 90 degrees relative to an adjacent substrate portion, wherein the substrate portion carrying the charging interface and the adjacent substrate portion are formed as a single substrate.

2. The hearing aid according to claim 1, wherein The charging interface further includes a programming pad configured to function as a programming interface for the hearing aid, the housing including an opening at the programming pad.

3. The hearing aid according to claim 1 or 2, wherein: A telecoil is mounted at the adjacent substrate portion.

4. The hearing aid according to claim 3, wherein The first and second portions extend from the adjacent substrate portion toward the telecoil to form a mesh shield for the telecoil against electromagnetic fields that are not parallel to a pickup axis of the telecoil.

5. The hearing aid according to any one of claims 1 to 4, wherein: A rubber spacer is provided between the substrate portion carrying the charging interface and the structural portion of the hearing aid housing and / or the battery compartment and / or the battery.

6. The hearing aid according to claim 5, wherein The rubber spacer is configured to receive or abut a portion of the substrate that carries the charging interface.

7. The hearing aid according to any one of claims 5-6, wherein: The portion of the substrate carrying the charging interface is held in the intended position by the walls of the hearing aid housing.

8. The hearing aid according to any one of claims 2 to 7, wherein: The hearing aid housing includes a removable cover disposed over an opening at the programming pad.

9. The hearing aid according to claim 8, wherein The cap is color coded to visually indicate whether the hearing aid is intended for use in the user's right or left ear.

10. The hearing aid according to any one of claims 1 to 9, which is composed of an air conduction hearing aid, a bone conduction hearing aid or a combination thereof, or includes an air conduction hearing aid, a bone conduction hearing aid or a combination thereof.

11. The hearing aid according to any one of claims 1 to 10, further comprising two metal plates provided at one end of the hearing aid housing, configured to engage with magnets of a charging device to provide a retaining force to hold the hearing aid in place in the charger during charging.

12. A hearing aid charger configured to charge the hearing aid according to claim 1, wherein the hearing aid charger comprises a hearing aid receptacle configured to receive at least a portion of the hearing aid to be charged.

13. The hearing aid charger according to claim 12, wherein: The hearing aid receptacle includes a charger interface configured to engage with a charging interface of the hearing aid when the hearing aid is located in the hearing aid receptacle, the charger interface including a spring that acts as an electrical conductor during charging.

14. The hearing aid charger according to claim 12 or 13, wherein: The hearing aid holder comprises first and second magnets configured to interact with first and second metal plates of a hearing aid to be charged.

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