EP4333463A1 - Procédé de surveillance de placement intra-auriculaire d'un dispositif auditif - Google Patents

Procédé de surveillance de placement intra-auriculaire d'un dispositif auditif Download PDF

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Publication number
EP4333463A1
EP4333463A1 EP22193220.5A EP22193220A EP4333463A1 EP 4333463 A1 EP4333463 A1 EP 4333463A1 EP 22193220 A EP22193220 A EP 22193220A EP 4333463 A1 EP4333463 A1 EP 4333463A1
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EP
European Patent Office
Prior art keywords
feedback path
hearing device
feedback
gain
signal
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Pending
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EP22193220.5A
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German (de)
English (en)
Inventor
Jean-Louis Durrieu
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Sonova Holding AG
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Sonova AG
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Application filed by Sonova AG filed Critical Sonova AG
Priority to EP22193220.5A priority Critical patent/EP4333463A1/fr
Publication of EP4333463A1 publication Critical patent/EP4333463A1/fr
Pending legal-status Critical Current

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/15—Determination of the acoustic seal of ear moulds or ear tips of hearing devices

Definitions

  • the invention relates to a method for monitoring an in-ear placement of a hearing device.
  • an earpiece of the hearing device When a hearing device is fitted to a user by an audiologist, an earpiece of the hearing device is placed in a desired (target) position in an ear canal of the user. Once the earpiece is in the desired position, processing parameters of the hearing device are set according to a prescribed gain model in order to compensate the hearing loss of the user. The gain is thereby adjusted to avoid squealing of the hearing device due to acoustic feedback. Feedback may occur when sound emitted by a receiver of the hearing device travels back to a microphone of the hearing device thus creating a feedback loop. This is particularly critical in cases where a high gain model is applied during audio processing in the hearing device.
  • the proneness for a feedback loop to develop is significantly increased if the in-ear placement of the earpiece of the hearing device is not as desired, i.e. the earpiece is not in the desired target position, as an insufficient seal between the earpiece and the ear canal leads to acoustic leakage between the microphone and the receiver.
  • a feedback results in an unwanted and in particular uncomfortable squealing sound of the hearing device
  • development of a feedback loop needs to be avoided during normal operation of the hearing device.
  • One method for avoiding such a squealing sound includes applying a feedback cancelling algorithm during audio processing in the hearing device.
  • the feedback cancelling algorithm may be based on adaptive filtering of the input signal provided by the microphone, wherein the occurrence of feedback is continuously suppressed.
  • Such a feedback cancelling algorithm may at the same time reduce the gain of the hearing device or may lead to unpleasant artefacts in the sound of the hearing device which is output to the user.
  • applying a feedback cancelling algorithm generally provides for an optimal compromise.
  • the position of the earpiece is typically not detected or monitored, resulting in discrepancies between an actual gain provided by the hearing device and a prescribed gain. This is a problem in particular, when the hearing device is used by an unexperienced user, who may have difficulties to correctly place the earpiece of the hearing device in a target position in his ear canal.
  • the start of the processing may be postponed after starting the hearing device; however this results in a delay before starting the hearing device and may thus be unsatisfying.
  • the object is achieved by a method for monitoring an in-ear placement of a hearing device according to claim 1.
  • the term feedback path in the context of the present invention may include a feedback gain and a feedback phase.
  • An audio signal in the present context may be any electrical signal which carries acoustic information.
  • an audio signal may comprise unprocessed or raw audio data, for example raw audio wave forms, and/or processed audio data, for example extracted audio features, compressed audio data, a spectrum, in particular a frequency spectrum, a cepstrum and/or cepstral coefficients and/or otherwise modified audio data.
  • the present invention proposes a method for monitoring an in-ear placement of a hearing device which is configured to be worn at least partially in an ear canal, the hearing device comprising
  • the squealing sound may stop by itself when the actual feedback path is close to the reference feedback path and the hearing device may start normal operation.
  • a feedback canceller may suppress squealing.
  • Normal operation of a hearing device in the context of the present invention may denote an operational mode in which a maximum possible gain setting for the hearing device is determined and applied, e.g. by determining a feedback threshold, i.e. a maximum gain setting for a hearing device, for which maximum gain setting there occurs only just no signal feedback, in particular as described in EP 1 624 719 A2 .
  • the processing unit is configured to operate as a feedback canceller to suppress acoustic feedback from the receiver to the microphone.
  • the feedback canceller is used as a compensation unit.
  • the target location for which a reference in-ear placement is defined is one of an ear canal of a user and a charger for the hearing device.
  • the coefficients of the filter are impulse response coefficients or frequency response coefficients.
  • an output is generated encouraging a user to stop touching the hearing device when having corrected the position thereof.
  • an input of a gain model block is provided with a compensated signal obtained by subtracting an output signal of a filter block representing the reference feedback path from an input signal.
  • a Euclidian distance between complex vectors constituted by the filter coefficients of the actual feedback path and the reference feedback path is calculated to assess whether the actual feedback path equals the reference feedback path within the predetermined margin.
  • a distance between a modulus of complex vectors constituted by the filter coefficients of the actual feedback path and the reference feedback path is calculated to assess whether the actual feedback path equals the reference feedback path within the predetermined margin.
  • a maximum gain is set in the feedback threshold gain model before activating the processing unit.
  • a visual signal is output once the actual feedback path equals the reference feedback path within the predetermined margin.
  • the visual signal is output on a mobile device wirelessly connected to the hearing device.
  • setting the gain model to generate feedback includes:
  • these steps are performed separately for each one of a plurality of frequency bands.
  • the coefficients of the feedback canceller may be adapted to accommodate for discrepancies due to the presence of the hand of the user. This may be a slow, full adaptation or only a partial adaptation of only the phase component.
  • a hearing device is proposed, wherein the hearing device is configured to perform the above described method.
  • the hearing device may start to whistle before it is introduced and inserted properly in the ear canal.
  • Figure 1 is a schematic flowchart of an exemplary embodiment of a method for monitoring an in-ear placement of a hearing device 1, e.g. in a user's ear 2 or in a charger.
  • Figure 2 is a schematic view of the method using pictograms.
  • the hearing device 1 comprises a receiver configured for playing back sound in an ear canal of the user, at least one microphone configured for obtaining an audio signal from received ambient sound, and a processing unit 100 configured to process the audio signal, wherein the receiver is configured for outputting sound to the ear canal based on the processed audio signal, the processing unit configured to filter signals played back on the receiver or picked up from the sound played back by the receiver with a filter representing a feedback path having a feedback gain and a feedback phase and to subtract the filtered signals from the sound signal picked up by the microphone.
  • a step S1 the hearing device 1 is started.
  • reference values Ho of a filter representing a physical reference feedback path of the hearing device 1 are loaded and applied to the filter of the processing unit.
  • the reference values Ho may apply to a situation such as that the hearing device 1 or an earpiece 3 thereof is correctly placed in a user's ear 2 or in a charger.
  • the reference values may be determined by a measurement in situ, i.e. in the ear 2 or in the charger. This measurement may be performed by the user or by a hearing care professional.
  • the reference values Ho may be the impulse response, the transfer function or the frequency response of the filter. More specifically, the reference values Ho may be implemented by filter coefficients, e.g. impulse response coefficients in the time domain or frequency response coefficients in the frequency domain.
  • the hearing device 1 outputs sound by the receiver.
  • a step S4 the hearing device 1 or an earpiece 3 thereof is being placed into or toward a target location such as the user's ear 2 while the sound is still being output.
  • the actual feedback path converges toward the reference feedback path as the hearing device 1 approaches the target location due to the user adjusting it in a step S5 so the volume of the sound output gradually reduces or is gradually reduced in a step S6.
  • the processing unit may be configured as a feedback canceller configured to suppress acoustic feedback from the receiver to the microphone.
  • the active mechanism may be configured to use the feedback canceler to estimate the actual feedback path, which can then be compared to the reference feedback path.
  • the sealing i.e. the correct in-ear placement of the hearing device 1, is therefore actively monitored, and can be used to control an audio output signal level, which provides a feedback to the user about how well the sealing currently is.
  • Figure 3 is a schematic flowchart of the active variant of the method.
  • the hearing device 1 is started.
  • the feedback canceller is activated on the whole frequency range.
  • the feedback canceller may be configured to work on a reduced frequency range, for instance from frequency 1700Hz to 8500Hz). It is only active at frequencies where there is a risk of feedback.
  • the compensation is applied as broadly as possible hence the feedback canceller is set to operate on the whole frequency range.
  • this frequency range may be configurable in order to discard certain frequencies, for instance very low frequencies and/or very high frequencies.
  • the hearing device 1 outputs sound by the receiver, e.g. it plays back sine waves while the ambient audio, i.e. sound picked up by the microphone, is bypassed.
  • a step S4 the hearing device 1 or an earpiece 3 thereof is placed into a target location such as the user's ear 2 while the sound is still being output.
  • the actual feedback path converges toward the reference feedback path as the hearing device 1 approaches the target location due to the user adjusting it in a step S5 so the feedback coefficients are updated in a step S6.1 and the volume of the sound output gradually reduces or is gradually reduced in a step S6.2.
  • the hearing device 1 stops outputting the sound and starts normal operation in a step S7.
  • the output sound level is explicitly or actively reduced. This creates a sound that is gradually fading away.
  • the method is performed independently in each of a number of several frequency bands.
  • the sound generation in a previously stopped band may be reactivated upon the detection that the hearing device 1 was moved away from the target location, i.e. the actual feedback path diverges from the reference feedback path.
  • Figure 4 is a schematic flowchart of the passive variant of the method.
  • step S1 the hearing device 1 is started.
  • step S2 the feedback canceller is activated on the whole frequency range.
  • reference values Ho i.e. filter coefficients, of a filter representing a physical reference feedback path of the hearing device 1 are loaded and applied to the filter of the processing unit.
  • a gain model designed to determine a feedback threshold (also referred to as a feedback threshold gain model), e.g. as described in EP 1 624 719 A2 , is started, consequently the hearing device 1 outputs sound by the receiver at a sound level enforced by the gain model, e.g. a squealing sound due to the actual feedback path outside the target location, i.e. the user's ear 2 or the charger, differing from the reference feedback path.
  • the gain is set such that it generates a feedback condition.
  • the gain model is embodied in a processing unit which uses a sound level of a hearing device input signal, e.g. a microphone signal, as an input and computes a gain to be applied to the input signal to generate an output signal.
  • a step S4 the hearing device 1 or an earpiece 3 thereof is placed into a target location such as the user's ear 2 while the sound is still being output.
  • the actual feedback path converges toward the reference feedback path as the hearing device 1 approaches the target location due to the user adjusting it in a step S5 so the gain model computes the gain in a step S6.1, i.e. at each processing frame (or interval), the processing unit running the gain model will compute the sound level of the input signal, then compute the corresponding gain, e.g. according to the feedback threshold gain model, and multiply the input signal with this computed gain to generate the output signal.
  • the feedback canceller coefficients are updated in a step S6.2, e.g. with regard to its phases, not its magnitudes. In other embodiments, the whole complex feedback canceller coefficients could be updated very slowly, or could not be updated at all.
  • the volume of the sound output gradually reduces in a step S6.3.
  • the output level is not directly controlled. Instead, a parameter of the gain model that relates to the output level, e.g. a target output, is modified.
  • a parameter of the gain model that relates to the output level, e.g. a target output, is modified.
  • the parameter b is an offset related to the target output. Lowering the offset b over time then allows to indirectly reduce the output level.
  • the phase of the feedback canceller coefficients may be adapted using a least mean squares algorithm, in particular a normalized least mean squares algorithm, while the magnitudes are kept.
  • the hearing device 1 stops outputting the sound and starts normal operation in a step S7.
  • the passive version uses a similar principle to the feedback threshold gain model as described in EP 1 624 719 A2 : the hearing device 1 will whistle as long as the feedback path is not close enough to the reference feedback path defined by the reference values Ho, thanks to the special gain model. Indeed, with this gain computation, the output of the hearing device 1 is controlled to reach a desired level. This gain may depend on the (noise) input level, feedback path and desired output level. This gain model saturates when it reaches the maximum allowable gain of the hearing device 1. If we activate the feedback canceller, in static mode and initialized with a reference path defined by the reference values Ho, the feedback path, from the device point of view, will then be equal to the difference between the physical and the electric paths: H-Ho.
  • the gain in this gain model, tends to be inverse proportional to the feedback gain
  • the coefficients of the feedback canceller may optionally be updated as well, but only the phase terms of the complex coefficients, thus preserving the global spectral shape of the reference feedback path.
  • the gain model causes the volume of the sound output to be high only when the difference of the actual feedback path from the reference feedback path is rather high. As the actual feedback path converges toward the reference feedback path, the gain of the gain model is maximized and the hearing device 1 stops squealing and starts normal operation. In normal operation, the feedback canceller may suppress squealing. In an exemplary embodiment, normal operation is started and the squealing stops.
  • a melody or a tone sequence may be output which may be more comfortable to listen to. If a remote device is available, the melody may be streamed from or via the remote device.
  • the passive solution does not need to actively generate sound and adapt it to the acoustic situation. Instead, the sound is automatically generated and thus automatically fades away as the acoustic coupling gets close to the reference.
  • the algorithm shown in Figure 4 may be performed independently in each one of a plurality of frequency bands. This can be done simultaneously in all bands, or as a sequence, one band after the other. In this scenario, there may be a loop over the frequency bands, encapsulating the loop that includes steps S6.1, S6.2, S6.3 in figure 4 . In this case, in step S6.1 the gain is set to 0 in all bands, except for the active band, i.e. the currently considered band, where the gain model is set to determine the feedback threshold in that band.
  • the condition in step S5 to skip to step S7 also includes the fact that the gain has to be high enough in all the tested bands.
  • the order in which the frequency bands are cycled through is not important for the performance. Hence, an arbitrary order can be chosen such that the resulting audio output is the most comfortable one to the end-user. For instance, a seemingly random sequence may make the audio output more enjoyable and less monotonic.
  • Both, the active and the passive variant may be configurable and have a timeout parameter. Otherwise, the active variant stops after the threshold on the estimated feedback path is reached. The passive variant stops when the maximum gain is hit.
  • different tones may be used to help the user differentiate the left and the right hearing device 1, before placing the earpieces 3 in the ear 2, in case notably when the hearing devices 1 are not very different otherwise.
  • in-ear placement may be used in addition, e.g. an in-ear-canal microphone, or a skin contact captor.
  • a visual cue displayed on a screen of a mobile device could further help the user recognize correct placement, or even replace the audio cue, thus making the process silent and possibly more pleasant.
  • a hard switch between the startup and normal operation may not be necessary.
  • the above mechanisms could probably also operate in a continuous manner, for instance by acting on gain fading mechanisms, reducing the gain while the position of the hearing device 1 is unsatisfying, and raising the gain to normal operation when the position is deemed correct.
  • the final audible sound design may be configurable.
  • the generated signal may be configured almost arbitrarily, while with the passive method, this may be more limited.
  • the hearing device 1 may be configurable by the user to allow for de-activating the described method, e.g. if they decide that they are able to place the hearing device 1 or the earpiece 3 thereof well enough without assistance.
  • the hand of the user may have a contribution to the feedback path.
  • the user may thus be encouraged to remove their hand after correcting the placement, e.g. by an audio message or by a hint in a user's manual.
  • the spectral shape of the sound output may be modified in accordance to the detected feedback path, modifying the energy output in a given frequency channel with respect to the in-ear placement in that channel.
  • the generated sound helps guiding the user such that they know whether they are far from the optimal position (loud excitation) or close to it (very soft / inaudible signal). For mild and higher hearing losses, this could however mean that the generated sound should be as loud as needed, such that the user can actually hear it.
  • a user may be able to associate spectral characteristics to the actual acoustic coupling.
  • the presently proposed method does not necessarily require a tool for placing the earpiece 3, although this could be helpful, notably in order to avoid to have a discrepancy between the reference feedback path and the measured one, which is then "polluted" by the presence of the user's fingers and hand.
  • the processing unit is indeed not designed to generate a sound, but rather to modify the input, i.e. the ambient sound, by enforcing the output to reach a desired level.
  • This processing automatically results in gains equal to the inverse of the feedback path, provided that sufficiently high gain is available.
  • the passive approach does not modify the gain model depending on the proximity to the reference, but proposes to modify the input signal of the gain model such that the input signal of the gain model is the signal from which the reference feedback signal has been removed, optionally adapted to accommodate for discrepancies due to the presence of the hand of the user. This means that such a system would not need to explicitly steer the output power, but rather automatically and implicitly stops creating feedback as the acoustic situation comes close to the reference situation.
  • the passive approach may perform the following steps:
  • Step 1 is based on the following considerations: a hearing aid is characterized by a processing block referred to as the gain model or embodying such a gain model, in order to compensate a hearing loss.
  • the present invention proposes to reuse the same gain model processing block, as in EP 1 624 719 A2 to determine a "feedback threshold" - leading to the "feedback test” procedure.
  • the gain model may be configured in a more complex way.
  • the hearing aid gain model may have more parameters, but it can be configured to compute the same formula.
  • Step 3 may be performed by one of the following methods:
  • FIG. 5 shows a block diagram for a feedback system as it is generally known.
  • a processing unit having a transfer function G and, by 200, a feedback unit having a transfer function K are identified.
  • An input signal I is fed to one of the two inputs of an addition unit 10 of which the only output is fed to the processing unit 100.
  • an output signal O is generated that is fed to the second input of the addition unit 10 via the feedback unit 200, besides the circumstance that the output signal O is fed to the outside.
  • FIG. 6 schematically shows a block diagram of a hearing device 1, comprising a processing unit 100 with a transfer function G. Seen from a propagation direction of signals in the hearing device 1, a loudspeaker 30, which is also called receiver 30 in the technical field of hearing devices, is positioned after and connected to the processing unit 100, and a microphone 20 is positioned before and connected to the processing unit 100.
  • the output signal of the hearing device 1, respectively of the receiver 30, is fed via a feedback unit 200 to an addition unit 10, to which also an input signal I is being fed.
  • An output signal is generated in the addition unit 10, which output signal is fed to the microphone 20.
  • Figure 6 only represents a simplified structure of a hearing device 1 in that only a microphone 20, a signal processing unit 100 and a receiver 30 are shown.
  • other functional units e.g. other microphones, an analog-to-digital converter, observation units for observation of power supply, a digital-to-analog converter, memory units, etc. - might be provided. Such additional units do not have an impact on the concept of the present invention.
  • the feedback unit 200 having a transfer function K is the actual equivalent circuit for the effects mentioned above, of which the acoustic signal feedback contributes the largest part.
  • the overall transfer function of the block diagram according to Figure 6 is equal to the one according to Figure 5 .
  • Figure 7 shows, in a schematic view, a course for the gain of a compressive system, as it is used in a hearing device 1 to compensate a hearing loss. While on the horizontal axis the level of the input signal I is drawn using a logarithmic scale and the unit decibel (dB), on the vertical axis the gain V is drawn also by using a logarithmic representation. The course of the gain in function of the input signal level has a negative slope which is characteristic for a compressive system.
  • the system will adjust to a steady state in which the gain in the forward path will be equal to the damping in the backward path.
  • the gain in the forward path will be equal to the feedback threshold gain V KRIT .
  • the feedback threshold gain V KRIT can be assessed, according to the present invention, by assessing the gain in the forward path or the damping in the backward path, e.g. in one of the following ways:
  • the feedback unit 200 having a transfer function K is the actual equivalent circuit for the effects mentioned above, of which the acoustic signal feedback contributes the largest part.
  • the addition unit 10 is an equivalent circuit representing the superposition of the input signal I with the signals from the acoustic signal feedback.
  • the feedback unit 200 and the addition unit 10 are not or do not necessarily have to be actual tangible entities but may represent effects occurring in a feedback system or hearing device 1.
  • a generic definition for a gain model is: the processing unit 100 computes the gain V as a function of the input level I, and then applies (multiplication in linear domain) it to the signal to generate the output signal O.
  • the gain model is specific.
  • EP 1 624 719 A2 mentions that a "compressive system” would suffice: this means that the computed gain decreases as the input level increases.
  • the gain g(I input ) equals - I input + L out , where the compression rate is -1, I input is the input level and Lout is a desired output level, with all quantities expressed in the logarithmic domain (usually in dB).
  • the computed gain will converge to - 20 log 10 (
  • This method works for a frequency domain processing, while for the time domain processing, the method may have to be adapted.
  • One way to implement the method in time domain is to use band-pass filters, one for each of the frequency band, and proceed for each band in a sequence, one after the other.
  • Figure 8 is a schematic view of a feedback canceller 300, comprising a gain model block G(z), a filter block ⁇ ( z ) and a subtraction block SB.
  • the filter block ⁇ ( z ) and the subtraction block SB constitute a compensation unit.
  • the subtraction block SB subtracts the output of the filter block ⁇ ( z ) from input signal s(n) to obtain a compensated signal e(n).
  • the actual feedback path H(z) representing the actual acoustic feedback path is shown.
  • the squealing of the hearing device 1 will stop as the hearing device 1 approaches its reference in-ear placement because the distance H-Ho converges to 0, so the gain V computed by the gain model tends to -20 log 10 (
  • the resetting of the gain model and the deactivation of the compensation may occur after it has been detected that the squealing has stopped or that the distance
  • Distance in this case may refer to the Euclidian distance between the complex valued vectors H and H0, which are, as described above, the frequency domain coefficients for the feedback path filter model.
  • may be used in the alternative.
  • further distortion measures exist, such as the Kullback-Leibler divergence, or the Itakura-Saito divergence.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP22193220.5A 2022-08-31 2022-08-31 Procédé de surveillance de placement intra-auriculaire d'un dispositif auditif Pending EP4333463A1 (fr)

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EP22193220.5A EP4333463A1 (fr) 2022-08-31 2022-08-31 Procédé de surveillance de placement intra-auriculaire d'un dispositif auditif

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EP22193220.5A EP4333463A1 (fr) 2022-08-31 2022-08-31 Procédé de surveillance de placement intra-auriculaire d'un dispositif auditif

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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6134329A (en) 1997-09-05 2000-10-17 House Ear Institute Method of measuring and preventing unstable feedback in hearing aids
EP1624719A2 (fr) 2005-09-13 2006-02-08 Phonak Ag Procédé pour déterminer le seuil de couplage dans une prothèse auditive
WO2010049543A2 (fr) * 2010-02-19 2010-05-06 Phonak Ag Procédé pour le contrôle d’un ajustement d’une prothèse auditive et prothèse auditive
US20130170660A1 (en) * 2012-01-03 2013-07-04 Oticon A/S Listening device and a method of monitoring the fitting of an ear mould of a listening device
US20210204074A1 (en) * 2019-12-31 2021-07-01 Starkey Laboratories, Inc. Methods and systems for assessing insertion position of hearing instrument
US20210258702A1 (en) * 2018-06-15 2021-08-19 Widex A/S Method of testing microphone performance of a hearing aid system and a hearing aid system

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6134329A (en) 1997-09-05 2000-10-17 House Ear Institute Method of measuring and preventing unstable feedback in hearing aids
EP1624719A2 (fr) 2005-09-13 2006-02-08 Phonak Ag Procédé pour déterminer le seuil de couplage dans une prothèse auditive
WO2010049543A2 (fr) * 2010-02-19 2010-05-06 Phonak Ag Procédé pour le contrôle d’un ajustement d’une prothèse auditive et prothèse auditive
US20130170660A1 (en) * 2012-01-03 2013-07-04 Oticon A/S Listening device and a method of monitoring the fitting of an ear mould of a listening device
US20210258702A1 (en) * 2018-06-15 2021-08-19 Widex A/S Method of testing microphone performance of a hearing aid system and a hearing aid system
US20210204074A1 (en) * 2019-12-31 2021-07-01 Starkey Laboratories, Inc. Methods and systems for assessing insertion position of hearing instrument

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