EP2373063A1 - Dispositif auditif et procédé de réglage de celui-ci pour un fonctionnement sans contre-réaction - Google Patents

Dispositif auditif et procédé de réglage de celui-ci pour un fonctionnement sans contre-réaction Download PDF

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Publication number
EP2373063A1
EP2373063A1 EP11154523A EP11154523A EP2373063A1 EP 2373063 A1 EP2373063 A1 EP 2373063A1 EP 11154523 A EP11154523 A EP 11154523A EP 11154523 A EP11154523 A EP 11154523A EP 2373063 A1 EP2373063 A1 EP 2373063A1
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EP
European Patent Office
Prior art keywords
feedback
parameter
directional
hearing device
hearing
Prior art date
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Granted
Application number
EP11154523A
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German (de)
English (en)
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EP2373063B1 (fr
Inventor
Georg-Erwin Arndt
Jens Hain
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
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Siemens Medical Instruments Pte Ltd
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Publication of EP2373063A1 publication Critical patent/EP2373063A1/fr
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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
    • 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
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/49—Reducing the effects of electromagnetic noise on the functioning of hearing aids, by, e.g. shielding, signal processing adaptation, selective (de)activation of electronic parts in hearing aid
    • 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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers

Definitions

  • the invention relates to a method for adjusting a hearing device in order to enable a feedback-reduced operation of the hearing device.
  • the invention also relates to a hearing device in which such a feedback reduced operation can be made possible.
  • at least one directional parameter for defining a directional characteristic of a microphone arrangement of the hearing device can be set.
  • hearing device is understood in particular to mean a hearing device.
  • the term includes other portable acoustic devices such as headsets, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • hearing aids such as behind-the-ear hearing aids (Hd0), receiver in the canal (RIC) and in-the-ear hearing aids (IdO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • Hd0 behind-the-ear hearing aids
  • RIC receiver in the canal
  • IdO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is standard integrated into a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • a hearing device in particular a hearing aid, it may happen that the sound generated by the listener passes out of the ear canal of the device wearer and back to a microphone of the hearing device.
  • a passage opening for aerating the auditory canal a so-called vent
  • a feedback path may also pass through portions of the skull of the implement carrier if these areas are e.g. be excited by the sound waves of the listener to vibrations and the sound signal propagates as structure-borne noise.
  • the listener already produces a structure-borne noise, which may be fed back under certain circumstances.
  • the sound signal of the listener If the sound signal of the listener is detected by a microphone, it can be amplified in the hearing device and back from the listener be radiated. In such a case, the acoustic feedback path and the signal processing of the hearing aid together constitute a feedback loop. In the context of illustrating the invention, the transmission of a signal along a feedback loop is referred to as a feedback effect.
  • the feedback effect is critical when there is an overall gain in the feedback loop greater than unity. If, for example, an earmold of the hearing device has not been inserted into the auditory canal in the intended manner, so that an air gap remains between the earmold and the skin of the device wearer, a feedback path may result, which leads mainly through this gap. An attenuation of the feedback sound is then particularly low. At the microphone, the fed-back sound has a correspondingly high volume. If the received microphone signal is then amplified and converted again into a sound by the listener, this can lead to the listener producing an ever louder sound.
  • a feedback loop having a gain greater than one may result in self-excitation of the hearing device resulting in a whistling sound referred to as feedback or feedback in the context of the illustration of the invention.
  • a whistling sound is usually disturbed by the equipment wearer and by persons in his vicinity.
  • the probability of a feedback increases, in particular, when the microphone unit signals are amplified very strongly in some frequency ranges by the signal processing unit of the hearing device in order to compensate for a hearing loss of the equipment wearer.
  • a gain that triggers feedback also means critical amplification.
  • the directional characteristic describes how strongly a sound signal is attenuated by the signal processing of the hearing device as a function of which direction the sound strikes the hearing device. If it is found that a sound fed back from the listener from one direction strikes the microphones, for which a particularly strong attenuation results according to the directional characteristic, this may possibly prevent feedback. If, on the other hand, a feedback sound from one direction reaches the microphones, for which, according to the directional characteristic, a particularly low attenuation results, this can even encourage feedback.
  • the directional characteristic can be set by means of a directional parameter. Then, in the hearing apparatus, it may be possible to control the value of the directional parameter, for example, depending on environmental parameters, so that in different situations, e.g. in a conversation or during a concert, in each case a directional characteristic is provided by which a device carrier can perceive its environment particularly well.
  • a method and a hearing aid with a directional microphone system which has at least two microphones. By weighting the microphone signals in different frequency bands, a direction-dependent sensitivity of the directional microphone is determined. With the method, at least one acoustic interference signal can thus be effectively suppressed.
  • a hearing aid device which compensates for acoustic and electromagnetic feedback signals by means of an adaptive compensation device.
  • the hearing aid device in this case has a weighting device with which the signal of the microphone and / or the electromagnetic receiver is weighted.
  • the object of the present invention is to enable a hearing device in which a directional characteristic of a microphone arrangement depends on a value of a directional parameter, a feedback-reduced operation of the hearing device.
  • the object is achieved by a method according to claim 1.
  • the object is also achieved by a method according to claim 6 and by a hearing device according to claim 9.
  • Advantageous developments of the method according to the invention and the hearing device according to the invention are given by the subclaims.
  • a hearing device By means of the method according to the invention, a hearing device can be operated.
  • the first of these procedures concerns while a hearing device with a microphone arrangement, in which a directional parameter for setting a directional characteristic of the microphone arrangement is adjustable.
  • Such adjustable microphone arrangements are known in principle from the prior art in many embodiments.
  • a stability condition for a feedback-reduced operation of the hearing device is specified.
  • a stability condition can for example be based on a calculation rule by means of which it can be determined whether the system is stable in the sense described above. It is always given a stability condition in which it depends on the value of the directional parameter, whether it is satisfied or not. Based on the stability condition, those values of the directional parameter for which the stability condition is fulfilled are then determined according to the method. In a further step, the values for the directional parameter which are possible during operation of the hearing device are then limited to the determined values. In other words, such settings of the directional characteristic are prevented, by which a feedback is favored. This is achieved by the exclusive admission of the determined values.
  • Which of the permitted values is actually set can thereby be determined by another method.
  • Such a method may be, for example, the already mentioned method for optimizing the directional characteristic as a function of environmental parameters.
  • a stability condition may be that an overall gain resulting from one sweep of a feedback loop is less than one.
  • the overall gain is a dependent on the directional characteristic of the microphone array size. That the overall gain is less than one, but need not always be the condition for a stable, so essentially feedback-free, operation. If, for example, an algorithm for feedback suppression is also provided in the hearing device, then a stability condition can be that only such feedback is prevented, which can no longer be suppressed by the algorithm in a time period acceptable to the device carrier.
  • the overall gain of the feedback loop must be significantly less than unity. This can be useful, for example, if changes in the transfer function are to be expected and also for such changed transfer functions a substantially feedback-free operation should still be guaranteed.
  • a transfer function can change, for example, in that the hearing device slips on an ear of the device carrier.
  • a stability condition can also include the criterion that a measured value of a physical variable or a value of a control parameter lies within a correspondingly predetermined interval.
  • a term of a denominator of a total transfer function is specified, the term comprising at least the directional parameter and a transfer function of a feedback path. Those values are determined for the directional parameter for which the stability condition is satisfied, that the term fulfills a predetermined criterion. The term preferably determines a position of one pole of the total transfer function in the complex number plane.
  • the overall transfer function also includes a transfer function of a feedback path. This also becomes an influence of an environment the hearing device on the feedback behavior taken into account. Since the total transfer function also includes the directivity parameter itself, an analytical calculation of the stability value or an interval of stability values is advantageously possible. Preferably, a corresponding transfer function is determined for each microphone.
  • the method according to the invention is also advantageously developed if the values are determined as a function of a frequency of a signal. Then, for example, different stability values can be provided for individual channels of a filter bank. As a result, a different stability condition can be specified for each channel, without having to unnecessarily restrict a directional characteristic in another channel in order to fulfill a stability condition in one channel.
  • the overall transfer function A / B allows, for the first time, an analytical calculation of values for stable operation.
  • the directional parameter here is preferably the weighting factor a.
  • the development of the first method according to the invention is based on the knowledge that a feedback-reduced or substantially feedback-free operation is often possible for entire intervals a ⁇ a 0 . Accordingly, then advantageously only the limit a o of the interval must be determined. For each value from this interval, there is the certainty that a feedback reduced operation is possible.
  • By accurately calculating values for the weighting factor it is advantageously ensured that a predetermined stability condition is maintained and yet the weighting factor is not unnecessarily severely restricted.
  • an amount of a term H c [F 1 (1 + a exp (- j ⁇ ⁇ i)) - F 2 ( a + exp (- j ⁇ ⁇ i))] is less than a stability limit.
  • the term can be used to easily calculate an interval of possible stability values for the weighting factor a.
  • a measure of a strength of the feedback effect can be provided by the term. This measure allows, for example, to determine how robust the hearing device is for a given value of the weighting factor a against feedback. A hearing device is all the more robust, the more the transfer function F 1 and F 2 and other variables contained in the term can change, without this leading to an unforeseen feedback comes. As the stability limit, the value of one is preferably used.
  • the second method according to the invention relates to the operation of a hearing device in which a directional parameter for determining a directional characteristic of a microphone arrangement can be set as a first parameter and a control parameter for controlling a device for feedback suppression as a second parameter.
  • the method provides a measure of a feedback effect.
  • An example of such a measure is the overall transfer function already described or the mathematical term above. From the term, a strength of the feedback effect, e.g. the feedback gain can be determined.
  • a value for the dimension is determined. Depending on the determined value, at least one of the parameters is set.
  • the directional characteristic or the feedback suppression can be advantageously set to avoid or suppress a feedback. It is only known from the prior art to reduce the gain of the receiver signal.
  • An advantageous development of the second method according to the invention results if a measure of the distance to a stability limit as a function of the directional parameter is specified as the measure for the feedback effect and a step size for an adaptation algorithm of the unit for feedback suppression is set as the parameter. In this case, an adaptation speed of the adaptation algorithm is then increased if the hearing device is operated near the stability limit.
  • the adaptation algorithm may for example be part of a feedback suppression unit as already described.
  • the step size thereby controls the adaptation speed of the algorithm.
  • the adaptation speed is increased if it results from the value of the directional parameter that the hearing device is operated near a stability limit.
  • a measure of the feedback effect is analyzed as to whether there is feedback, and in the setting step the instantaneous value of the directional parameter is changed until a feedback effect falls below a predetermined threshold.
  • a threshold is determined in particular by the fact that for the feedback loop, a gain is less than one, so that an existing feedback decays independently.
  • a further aspect of the invention relates to a hearing apparatus in which a directional parameter for determining a directional characteristic of a microphone arrangement can be set as a first parameter and a control parameter for controlling a device for feedback suppression can be set as a second parameter. Furthermore, a control device is provided in the hearing device according to the invention, which is designed to operate the hearing device according to at least one of the two methods according to the invention or one of the described developments thereof.
  • the hearing device according to the invention is thus advantageously able to independently ensure a feedback-reduced operation by means of the control device.
  • a directional characteristic can be made possible, for example, by superimposing a cardioid directional characteristic and an anti-cardioid directional characteristic. It can be provided be that a proportion of the anti-Kardioid directional characteristic of the overall directional characteristic of the microphone array is determined by a weighting factor a. Then the overall directional characteristic is adjustable by means of the weighting factor a.
  • FIG. 2 a hearing aid 12 with a microphone assembly 14 of two microphones 16, 18 is shown.
  • the hearing aid 12 may be, for example, a behind-the-ear hearing aid, of which a in FIG. 2 not further illustrated housing with the microphone assembly 14 is located behind an ear of a device carrier.
  • the hearing device 12 may also include, for example, a sound tube and an earmold.
  • the earmold can be used in an ear canal of the equipment wearer.
  • a receiver 20 of the hearing aid 12 By a receiver 20 of the hearing aid 12, a sound is generated, which is passed through the sound tube and earmold in the ear canal.
  • another type of earmold can also be provided.
  • An air surrounding the hearing device 12 and the ear of the equipment wearer form an environment of the hearing device 12, which together with the hearing aid 12 form a system 10, in which it can come to a feedback.
  • the feedback paths 22, 24 are formed, via which a sound Y of the listener 20 can get to the microphone assembly 14.
  • the feedback paths 22, 24 include, for example, an acoustic propagation path which passes through a vent opening of the earmold.
  • the sound signal Y is changed according to a transfer function F 1 , which in FIG. 2 designated by the reference numeral 26.
  • F 2 For the feedback path 24 results in a transfer function F 2 , which in FIG. 2 designated by the reference numeral 28.
  • a sound X is received by a sound source, which is located in a vicinity of the equipment carrier.
  • the sound X also hits the microphone 18 with a time delay ⁇ e.
  • the time delay ⁇ e depends on a distance d of the microphones 16, 18 and on an angle ⁇ between the direction of propagation of the sound X and an axis of the microphone arrangement 14 in the one described Way off.
  • the sound X and the sound Y passed through the feedback paths 22, 24 are superimposed on the microphones 16, 18. This is in FIG. 2 indicated by sum symbols 30, 30 '.
  • the hearing device 12 has a device 32 for generating a directivity of the microphone arrangement 14.
  • the microphones 16 and 18 themselves can each have an omnidirectional directivity, ie each of the microphones 16, 18 detects a sound in this case, without direction.
  • the device 32 comprises delay elements 34, by means of which a microphone signal can be delayed by a delay time ⁇ i . Such a delay may be effected, for example, by varying a phase of a spectral component of the microphone signal.
  • the device 32 also includes summers 36, 38, 40, by means of which two signals can be superimposed, ie added, in each case. It is in the summers 36, 38 inverts one of the input signals before the superposition. This is in FIG. 2 indicated by a minus sign.
  • the unit 32 further comprises a multiplier 42, by which a signal with a weighting factor a can be weighted, ie multiplied.
  • a cardioid branch 44 and an anti-cardioid branch 46 are provided as signal paths.
  • signal components are attenuated in accordance with a cardioid directional characteristic of the microphone arrangement 14.
  • a signal is sent to the summer 40 via the anti-cardioid branch 46, in which signal portions are attenuated in accordance with an anti-cardioid directional characteristic of the microphone arrangement 14.
  • a portion of the signal of the branch 46 on a sum signal at the output 48 of the unit 32 is determined by the weighting factor a.
  • the weighting factor a is a directional parameter of the device 32.
  • the output 48 of the unit 32 is coupled to an amplifier 50 of the hearing aid 12. Through the amplifier 50, a signal may be amplified in response to a hearing curve of the equipment wearer to compensate for hearing loss.
  • a signal path consisting of the feedback path 22 and the electrical path from the microphone 16 to the listener 20 forms a first feedback loop.
  • the feedback path 24 and the electrical signal path from the microphone 18 to the handset 20 together form a second feedback loop.
  • the two feedback loops give a feedback effect. Of a gain along the feedback loops depends on whether a signal to a feedback in the sense already described, i. an audible whistle, leads.
  • a stability limit of the system 10 can be calculated in dependence on values for the transfer functions F 1 and F 2 . Is a stability condition for the system 10 that the amount of the term H c [F 1 (1 + a exp (- j ⁇ ⁇ i)) - F 2 (a + exp (- j ⁇ ⁇ i))] less than or equal 1 is. Then the sound X does not generate feedback. That is to say, a sound Y of the handset 20 that reaches the microphone arrangement 14 via the feedback paths 22 and 24, while producing a feedback effect, can be used to cause a microphone signal in the hearing aid 12 to be re-processed. However, the signal is always attenuated along the feedback loop so much that it decays independently over time.
  • summands C 1 and C 2 are less than 1, the system 10 is more stable than a system with a single omnidirectional microphone. Then, a larger amplification of the signal by the amplifier 50 is possible than in a Hearing aid with a single microphone.
  • Both summands C 1 and C 2 depend on the weighting factor a for the anti-cardioid branch 46 and on the frequency ⁇ . Depending on the weighting factor a, the critical gain value is greater than in a hearing aid with a single omnidirectional microphone. In such a case, a correspondingly greater amplification can be provided by the hearing device 12 without a feedback being triggered in the process.
  • a calculation of a maximum weighting factor a for the anti-cardioid branch 46 is possible, up to which a substantially feedback-free operation of the hearing aid 12 is possible.
  • This calculation requires a measurement of the transfer functions F 1 and F 2 of the feedback paths 22, 24.
  • Transfer functions F 1 and F 2 and further transfer functions for the individual feedback paths can be determined, for example, by a device carrier carrying a hearing device intended for it in the intended manner and test measurements, for example by a hearing care professional. On the basis of the transfer functions of the feedback paths thus determined, it is then possible to determine, for example, an interval a ⁇ a 0 of values for which a reduced-feedback operation results.
  • the weighting factor a can then be limited to the maximum value a o , ie to the upper limit of the determined interval.
  • a device carrier perceives such a limitation as reduced directivity in those situations in which feedback is expected.
  • an algorithm for feedback suppression can also be controlled. If the weighting factor a is set to a value close to the maximum permissible value a o at a certain point in time, a relatively small change in the weighting factor a lead to an unstable system. Similarly, the instability may be caused by a slight change in the transfer functions F 1 or F 2 . If the system 10 is close to such a stability limit, then an adaptation rate of the feedback suppression algorithm can be increased. If it actually comes to a feedback, this is suppressed by the algorithm very quickly.
  • a feedback suppression algorithm detection or detection may also be provided for feedback.
  • an adaptive limitation of the weighting factor a can be made possible. If a feedback is detected, then a limit for the weighting factor a can be reduced. As a result, the instantaneous value of the weighting factor a itself is also reduced until the system is stable again. Then the feedback sounds self-contained. If no further feedback is subsequently detected for a predetermined period of time, the limit for the weighting factor a can be raised again. In such an adaptive limitation, it can be ensured by specifying appropriate time constants that no cyclic repetition of feedbacks is caused.
  • the adaptive adaptation of the weighting factor a for the anti-cardioid branch 46 using the algorithm for feedback suppression results in the advantage that a hearing aid always allows a correspondingly maximum possible value for the weighting factor a even when the environment changes.
  • a particular aspect of the invention is the ability to mathematically determine a stability limit for a system based on the directivity parameter a and the transfer functions F 1 , F 2 for feedback paths. This makes it possible to limit the weighting factor a, so that a stable system is always ensured. In this case, the predetermined for example by a hearing curve of a device carrier gain of the microphone signals are taken into account.
  • a particularly high gain as is possible for hearing aids with only a single omnidirectional microphone, can also be achieved for a hearing aid with directivity.
  • a notch of a directional characteristic is such a detection direction, for which results in a comparatively strong attenuation.
  • a control device 52 a directional microphone device 54 and a device for suppressing a feedback, ie a feedback suppression 56, are shown.
  • the three devices 52, 54, 56 may be provided as programs on a signal processing processor of a hearing device.
  • the directional microphone device 54 can process signals of a microphone arrangement, for example in the manner explained in connection with the device 32, in order to generate a directional characteristic for the microphone arrangement.
  • the feedback suppression 56 may be configured to estimate transfer functions of feedback paths to generate a compensation signal from the estimated transfer functions to attenuate a signal of acoustic feedback.
  • the directional microphone device 54 and the feedback suppression 56 are each coupled to the controller 52.
  • a directional parameter of the directional microphone device 54 is adjustable.
  • a step size for an adaptation algorithm of the feedback suppression 56 can be set by the control device 52.
  • instantaneous values of these parameters can also be read from the directional microphone device 54 and the feedback suppression 56.
  • the estimated transfer functions for the feedback paths from the feedback suppression 56 can also be read out.
  • the control device 52 is designed to use these values to determine the directional parameter or the step size in connection with FIG. 2 to control described manner.
  • the hearing device it is possible in the hearing device to control the directional microphone device 54 and / or the feedback suppression 56 to prevent or suppress an acoustic feedback accordingly.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP11154523A 2010-03-17 2011-02-15 Dispositif auditif et procédé de réglage de celui-ci pour un fonctionnement sans contre-réaction Active EP2373063B1 (fr)

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DE102010011729A DE102010011729A1 (de) 2010-03-17 2010-03-17 Hörvorrichtung und Verfahren zum Einstellen derselben für einen rückkopplungsfreien Betrieb

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EP (1) EP2373063B1 (fr)
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US20140270291A1 (en) * 2013-03-15 2014-09-18 Mark C. Flynn Fitting a Bilateral Hearing Prosthesis System
US9763006B2 (en) 2015-03-26 2017-09-12 International Business Machines Corporation Noise reduction in a microphone using vowel detection
EP3139636B1 (fr) * 2015-09-07 2019-10-16 Oticon A/s Dispositif auditif comprenant un système d'annulation de rétroaction sur la base d'une relocalisation de l'énergie d'un signal
DE102018208657B3 (de) 2018-05-30 2019-09-26 Sivantos Pte. Ltd. Verfahren zur Verringerung eines Auftretens einer akustischen Rückkopplung in einem Hörgerät

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DE19844748A1 (de) 1998-09-29 1999-10-07 Siemens Audiologische Technik Verfahren zum Bereitstellen einer Richtmikrofoncharakteristik und Hörgerät
DE10313330A1 (de) 2003-03-25 2004-10-21 Siemens Audiologische Technik Gmbh Verfahren zur Unterdrückung mindestens eines akustischen Störsignals und Vorrichtung zur Durchführung des Verfahrens
WO2005091675A1 (fr) * 2004-03-23 2005-09-29 Oticon A/S Aide auditive avec systeme anti-retroaction
DE102005019149B3 (de) 2005-04-25 2006-08-31 Siemens Audiologische Technik Gmbh Hörhilfevorrichtung mit Kompensation von akustischen und elektromagnetischen Rückkopplungssignalen
WO2007098808A1 (fr) * 2006-03-03 2007-09-07 Widex A/S Prothèse auditive et procédé d'utilisation de limitation de gain dans une prothèse auditive
WO2007113282A1 (fr) * 2006-04-01 2007-10-11 Widex A/S Appareil auditif et procédé permettant de commander la vitesse d'adaptation dans des systèmes anti-rétroaction pour appareils auditifs

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DK2373063T3 (da) 2012-10-01
US8452035B2 (en) 2013-05-28
EP2373063B1 (fr) 2012-06-20
US20110228960A1 (en) 2011-09-22
DE102010011729A1 (de) 2011-09-22

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