EP2226795B1 - Dispositif auditif et procédé de réduction d'un bruit parasite pour un dispositif auditif - Google Patents

Dispositif auditif et procédé de réduction d'un bruit parasite pour un dispositif auditif Download PDF

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Publication number
EP2226795B1
EP2226795B1 EP10152645.7A EP10152645A EP2226795B1 EP 2226795 B1 EP2226795 B1 EP 2226795B1 EP 10152645 A EP10152645 A EP 10152645A EP 2226795 B1 EP2226795 B1 EP 2226795B1
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Prior art keywords
reduction
noise
input signal
signal
sound
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EP10152645.7A
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German (de)
English (en)
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EP2226795A1 (fr
Inventor
Eghart Fischer
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Speech or voice signal processing techniques to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Speech or voice signal processing techniques to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/06—Transformation of speech into a non-audible representation, e.g. speech visualisation or speech processing for tactile aids
    • G10L2021/065—Aids for the handicapped in understanding
    • 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
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
    • 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
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing
    • 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 hearing device and a method for reducing a noise for a hearing device.
  • the term 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.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • ITE in-the-ear hearing aids
  • ITE in-the-ear hearing aids
  • ITE in-the-ear hearing aids
  • ITE concha hearing aids or 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 usually integrated in 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 into 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 signal processing unit of a hearing device can also be designed to reduce unwanted noise in a microphone signal of the hearing device. With such a noise reduction, an auditory quality of the acoustic signal output from the hearing aid can be improved.
  • a noise may originate from noise sources in an environment of the equipment carrier. It is therefore detected by the microphones of the hearing aid together with the sound that is to be processed as useful sound from the hearing aid for the equipment wearer.
  • Noise reduction is in many cases achieved by using an input signal, e.g. a microphone signal or even for individual spectral components of the microphone signal, continuously an attenuation factor is calculated.
  • An attenuation factor can have a value between 0 and 1. A small value results whenever a noise dominates in an input signal of the noise reduction.
  • An attenuation factor is often calculated on the basis of an estimate for a signal-to-noise ratio. An example of such a noise reduction is the Wiener Filter.
  • An improved output eventually results when the input signal is multiplied by the corresponding attenuation factor. Also, for noise reduction algorithms where a damping factor is not explicitly calculated, a corresponding damping value can be determined. This value then results as the ratio of a value of an output signal produced by the noise reduction to the corresponding value of the input signal.
  • Non-stationary noise is referred to herein as transient noise.
  • An example of a transient noise is the cracking of a door that is slamming or the clattering of clanging dishes.
  • Another disadvantage of many methods of reducing stationary noise is that they produce unwanted artifacts in the processed signal in transient noise.
  • Another way to distinguish between a useful sound and a noise is used in a multi-microphone arrangement.
  • an incident direction can be determined, from which a sound or spectral components of a sound strike the arrangement.
  • a distinction is made between useful sound sources and noise sources.
  • the sound In order for a direction of incidence of a sound to be determined, however, the sound must be spatially directed. In other words, sound waves of the sound must show a propagation direction. Only then can a sound be assigned a spatial position of a sound source with respect to the microphone arrangement. Allocation becomes increasingly difficult as more reverb mixes with a direct sound source sound. Much reverb occurs especially in closed rooms. A disadvantage of a noise reduction for spatially directed noise is thus that it is only suitable for noise, for which an incident direction of the noise can be determined.
  • a method for reducing acoustic noise is known.
  • signals are received via a plurality of microphones and processed with at least one of the stored noise reduction algorithms. If the noise situation matches the requirements of the at least one noise reduction algorithm, the interference signals are reduced compared to the useful signals.
  • the noise reduction algorithms can be switched on and off separately.
  • characteristic parameters for the noise field are determined, which are assigned to the individual noise reduction algorithms as typical parameters, and depending on the characteristic parameters, the associated noise reduction algorithm is selected.
  • each processor has a different signal-to-noise performance. Depending on the ambient noise, the outputs of the processors are summed to obtain a signal in the beam direction of a microphone array.
  • the object is achieved by a hearing device according to claim 1.
  • the object is also achieved by a method according to claim 6.
  • Advantageous developments of the invention are given by the dependent claims.
  • the hearing device according to the invention has a first reduction device for reducing stationary noise of an input signal and a second reduction device for reducing interference noise spatially directed relative to the hearing device. Furthermore, a hearing device according to the invention has a selection device for selecting the first and / or the second reduction device for an output signal to be formed from the input signal.
  • the invention is based on the finding that in particular a transient noise with a reduction device for reducing spatially directed noise can often be damped much more effectively than is possible with a reduction device for reducing stationary noise.
  • the selector selects between the reducers depending on a criterion for the stationarity of the input signal.
  • a criterion for stationarity can simply be the information as to whether an input signal is stationary in the statistical sense or not. However, the criterion can also be a continuous measure.
  • the method according to the invention is developed in an advantageous manner, by analyzing the input signal for stationarity.
  • determining a stationarity of the input signal it can be decided in a particularly reliable manner whether a noise reduction for stationary noise or a noise reduction for spatially directed noise results in an output signal with a better auditory quality.
  • a hearing device is advantageously further developed if the selection device evaluates as a criterion for the stationarity a value of a damping factor of the first reduction unit or an estimated value for a signal-to-noise ratio of the first reduction unit. Accordingly, the inventive method can be further developed. By evaluating the attenuation factor or the signal-to-noise ratio estimate, there is the advantage that it can reliably be determined from these quantities when reducing noise based on the first reduction unit is not sufficiently accomplished to achieve high auditory quality ,
  • the hearing device according to the invention is further developed in an advantageous manner if the two reduction devices are designed to perform the respective reduction and the selection device to perform the selection for a plurality of different frequency bands. This results in a particularly high auditory quality of the output signal.
  • the method according to the invention can be developed accordingly.
  • a further advantage results if in the hearing device according to the invention the damping factor of the first reduction unit is limited to small values by an anchor gain value and if by the second reduction unit a Damping is generated, which corresponds to a value for a damping factor less than the anchor gain value.
  • An anchor gain value is to be understood as a minimum value which is used for damping instead of the damping factor of the first reduction device whenever a calculation for this damping factor according to a noise reduction algorithm yields a value smaller than the anchor gain value ,
  • the hearing device according to the invention is further developed in an advantageous manner in the case of the hearing device, when the selection results in a change from one of the two reduction devices to the other reduction device, blending the selection device from one reduction device to the other reduction device.
  • a cross-fade here means that it is not instantaneously switched, for example, from the second reduction unit to the first reduction unit, when the input signal has initially behaved in an instantaneous manner and then it is recognized that it is now stationary.
  • the effect of the cross-fading is rather to mix, for example, attenuation factors of both reduction units or output signals calculated with both reduction units during a transition that is limited in time. Mixing can be done, for example, by weighted addition.
  • the method according to the invention can be developed accordingly.
  • Crossfading reduces audible switching effects when switching between the two reduction units.
  • the second reduction device is designed to attenuate signals of a sound when the sound hits the hearing device from a predetermined direction. Accordingly, the method according to the invention is further developed in that the sound reduction for spatially directed interference noises signals of a sound are attenuated when the sound is received from a predetermined direction.
  • a predetermined direction provides the advantage that artifacts in the output signal are avoided for noise reduction for spatially directed noise. This contributes to a high auditory quality of the output signal.
  • FIG. 2 is shown as in a hearing aid that is in FIG. 2 not shown further, from an input signal by means of a signal processing 6, an output signal is generated. In the output signal, a noise contained in the input signal is reduced.
  • the input signal for the signal processing 6 is decomposed by a filter bank 7 into its spectral components. This means here that for different frequency bands contained therein portions of the input signal are determined.
  • the values for the determined spectral components are transferred to a noise reduction 8 for stationary noises and a noise reduction 9 for spatially directed noises.
  • the spectral components are in the example of FIG. 2 independently processed by the signal processing 6. In FIG. 2 Therefore, only the signal flow chart for values of a single spectral component is shown. This is symbolized by simple connecting lines between the blocks of the signal flow diagram. The remaining spectral components are processed in the signal processing 6 in a comparable manner.
  • an attenuation factor is calculated, which is adjusted as a function of the input signal with time.
  • the calculated damping factor is set to an anchor gain value if the calculated damping factor is less than the anchor gain value.
  • the anchor gain value provides a 10 dB attenuation.
  • the gain of the input signal is -10 dB due to the achor gain value.
  • the possibly corrected attenuation factor output by the limiter 10 is offset with the input signal. In FIG. 2 Thus, the output of the limiter 10 is a processed signal.
  • the method used in the noise reduction 8 for calculating the damping factor in combination with the limiter 10 generates a low-artifact, quiet sound impression of the processed signal in that for stationary noise, the reduction of a fixed lower bound, the anchor-gain value, not lower. In stationary noise, this maximum value of the reduction is also usually achieved, so that there is a nearly constant damping. This causes the quiet sound impression.
  • the noise reduction 9 for spatially directed noise is able to attenuate the signal of a sound that hits the equipment carrier from behind. At the same time, the signal of a sound source remains undamped by the noise reduction 9, when the device carrier turns straight to this sound source. The sound then hits the gear tray from the front.
  • the input signal is a multi-channel signal. It is composed of several microphone signals of a microphone arrangement of the hearing aid. In FIG. 2 It is not indicated in any particular way that the connecting lines between the blocks of the signal flow diagram can be multi-channel connections.
  • the directional damping by the noise reduction 9 is achieved by a so-called beamforming, which combines corresponding spectral components of the different channels.
  • the attenuation of a noise caused by the noise reduction 9 may be more than 10 dB in particular.
  • the damping is therefore not limited in the case of noise reduction 9.
  • the noise reduction 9, like the limiter 10, outputs a processed signal which is single-channeled.
  • an output signal is formed by a mixer 11. This output signal is then converted by a synthesis unit 12 into an audio signal.
  • the mixer 11 is controlled by an analysis unit 13.
  • the analysis unit 13 examines each spectral component of the Input signal as to whether he is stationary in a statistical sense or not. For periods of time for which the spectral components are stationary, the mixer 11 is controlled so that only the processed signal of the limiter 10 is output as an output signal to the synthesis unit 12. If, however, a spectral component is unsteady, the mixer 11 switches over to the output of the noise reduction 9. If this results in a change from the output of the noise reduction 9 back to the limiter 10, it is not simply switched back. Instead, the analysis unit 13 controls the mixer 11 in such a way that, within a period of one second, it is gradually faded in from the output of the noise reduction 9 to the output of the limiter 10.
  • the analysis unit 13 not only examines the spectral components of the input signal. Also, the attenuation factor calculated by the noise reduction 8 is observed. This is in FIG. 2 symbolized by a dashed box. If the attenuation factor for a spectral component has a value less than or equal to the anchor gain value, then the analysis unit 13 indicates that the spectral component is stationary. Similarly, if the damping factor is above the anchor gain, then it is decided upon instationarity. Since the signal of the filter bank 7 is also directly observed by the analysis unit 13, further analysis steps can be carried out in order to recheck the analysis which was carried out on the basis of observation of the damping factor.
  • the five diagrams D1 to D5 in FIG. 3 show temporal courses of each one size, as they are for one in FIG. 3 not shown hearing aid revealed.
  • horizontally running time axes are scaled identically, so that simultaneous changes of the quantities in FIG. 3 lie on a common vertical axis.
  • Diagram D1 shows a time profile of a spectral portion 14 of a microphone signal originating from one of several microphones of the hearing aid.
  • the time profile of the spectral component represents an input signal in the sense of the invention.
  • the spectral component 14 behaves stationary in a statistical sense in a total of three time segments 15a, 15b, 15c. Namely, in the periods 15a, 15b, 15c, the spectral component has a constant statistical average and a constant variance.
  • the microphone signal is determined for the periods of time 15a, 15b, 15c predominantly by a fan whose uniform noise is detected by the microphones of the hearing aid.
  • the stationary signal of the fan noise is drowned out by a sound signal.
  • the first sound signal detected in the period 16a it is the speech signal of a speaker.
  • the speaker faces a wearer of the hearing aid.
  • the transient course during the period 16b is caused by the popping of a door that falls behind the wearer of the hearing aid in a lock. The sound generated by the random door thus hits the hearing aid from behind.
  • the course 17 of a gain V is shown, as it is caused by a noise reduction in the hearing aid for stationary noise for the spectral portion 14.
  • An attenuation factor of the noise reduction is limited by a limiter to an anchor gain value at the bottom. This results in a minimum value of the gain V of -10 dB. This minimum value has the gain V in the periods 15a, 15b, 15c when the spectral component 14 is stationary. In the time segments 16a, 16b, for which the spectral component 14 is transient, the noise reduction effects for stationary noise here almost no damping.
  • the spectral component 14 is attenuated, that is, transmitted with a gain V of almost 0 dB by the noise reduction for stationary noise.
  • an analysis result 18 of an analysis unit is shown, which corresponds to the in FIG. 2 similar to the analysis unit 13 shown. It was correctly recognized by the analysis unit that the spectral component 14 behaves unsteadily in the time segments 16a and 16b. The analysis result 18 therefore changes from "stationary” to "unsteady” for the time segments 16a and 16b. In Diagram D3, these two possible analysis results are "stat.” and "instat.” abbreviated.
  • the analysis result 18 is based here on the profile 17 of the gain V.
  • the analysis result 18 shows that the profile of the spectral component 14 here becomes subdivided into two mutually exclusive classes, namely in time segments 15a, 15b, 15c, in which the signal is classified as stationary, and in periods 16a, 16b in which the signal is classified as transient.
  • a curve 19 of a gain V ' is shown, which is caused by a likewise present in the hearing aid noise reduction for spatially directed noise in the spectral component 14.
  • the gain V ' unlike the gain V, is not limited to small values. That's why she can be special even smaller than -10 dB fail. However, their course is also not constant for those time segments 15a, 15b, 15c in which the spectral component 14 is stationary. The course 19 is uneven in the time intervals 15a, 15b, 15c, because a reverberation in the surroundings of the device carrier causes the noise of the fan to strike the microphones of the hearing device from a constantly changing direction.
  • the speech signal of the speaker striking the hearing aid from the front in the period 16a is not audibly changed by the noise reduction for spatially directed noise. Namely, the gain V 'for the period 16a is almost 0 dB. In contrast, the pop of the door, which strikes the wearer's wearer from behind in the period 16b, is very effectively suppressed with a gain V 'of -20 dB.
  • Diagram D5 shows a profile 20 of an overall gain V '' which results during the processing of the spectral component by the signal processing 6.
  • the processed spectral component is combined together with the parallel processed spectral components to form an output signal from which a hearing signal for the wearer of the hearing aid is formed by the hearing aid.
  • the curve 20 results from a selection between the results of the noise reduction, by which the gain V is effected, and the noise reduction, by which the gain V 'is effected.
  • the selection is made according to the analysis result 18.
  • the noise reduction for stationary noise is selected for the time intervals 15a, 15b and 15c, so that a nearly constant gain of -10 dB results for the overall gain V ".
  • the noise reduction is selected for spatially directed noise. Accordingly, there is a very effective damping for the pop of the door in the period 16b.
  • the gain V '' is then -20 dB.
  • the speech signal detected during the period 16a becomes is not distorted, so that the wearer of the hearing aid can understand the speaker well.
  • the wearer of the hearing aid thus perceives an output signal which has a better auditory quality than in a hearing aid in which only a simple noise reduction is provided.

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  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Physics & Mathematics (AREA)
  • Signal Processing (AREA)
  • Health & Medical Sciences (AREA)
  • Human Computer Interaction (AREA)
  • Audiology, Speech & Language Pathology (AREA)
  • Quality & Reliability (AREA)
  • Computational Linguistics (AREA)
  • Multimedia (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)

Claims (6)

  1. Ensemble auditif présentant
    un premier dispositif de réduction (8) qui réduit les bruits parasites stationnaires d'un signal d'entrée,
    un deuxième dispositif de réduction (9) qui réduit les bruits parasites orientés spatialement par rapport à l'ensemble d'audition et
    un dispositif de sélection (11, 13) qui sélectionne le premier dispositif de réduction (8) et/ou le deuxième dispositif de réduction (9) pour un signal de sortie à former à partir du signal d'entrée,
    le dispositif de sélection (11, 13) sélectionnant en fonction d'un critère de stationnarité (18) du signal d'entrée,
    le deuxième dispositif de réduction (9) étant conçu pour atténuer les signaux d'un son si le bruit aboutit sur l'ensemble d'audition dans une direction prédéterminée,
    caractérisé en ce que
    le dispositif de sélection (11, 13) sélectionne le premier dispositif de réduction (8) configuré pour réduire les bruits parasites stationnaires du signal d'entrée lorsque le signal d'entrée est stationnaire et le deuxième dispositif de sélection (9) lorsque le signal d'entrée n'est pas stationnaire.
  2. Ensemble d'audition selon la revendication 1, dans lequel le dispositif de sélection (11, 13) évalue comme critère de stationnarité (18) une valeur (17) d'un facteur d'atténuation (V) de la première unité de réduction (8) ou une valeur estimée d'un rapport signal-bruit de la première unité de réduction (8).
  3. Ensemble d'audition selon l'une des revendications précédentes, dans lequel les deux dispositifs de réduction (8, 9) sont conçus pour exécuter leur réduction et le dispositif de sélection (11, 13) sa sélection sur plusieurs bandes de fréquences (14) différentes.
  4. Ensemble d'audition selon l'une des revendications précédentes, dans lequel le facteur d'atténuation (V) de la première unité de réduction (8) est limité en direction des petites valeurs par une valeur d'ancrage de gain et dans lequel la deuxième unité de réduction (9) peut former une atténuation (V') qui correspond à une valeur du facteur d'atténuation plus petite que la valeur d'ancrage de gain.
  5. Ensemble d'audition selon l'une des revendications précédentes, dans lequel lorsque la sélection entraîne un basculement d'un des deux dispositifs de réduction vers l'autre dispositif de réduction, le dispositif de sélection superpose ce dispositif de réduction à l'autre dispositif de réduction.
  6. Procédé de réduction d'un bruit parasite pour un ensemble d'audition, le procédé comportant les étapes qui consistent à :
    analyser (13) un signal d'entrée (14) pour vérifier sa stationnarité (18), en fonction du résultat (18) de l'analyse, sélectionner (11) ou combiner (11) une première réduction de bruit (8) pour réduire les bruits parasites stationnaires du signal d'entrée et une deuxième réduction de bruit (9) qui réduit les bruits parasites du signal d'entrée orientés spatialement par rapport à l'ensemble d'audition,
    la deuxième réduction de bruit (9) atténuant les signaux d'un son lorsque le son aboutit sur l'ensemble d'audition depuis une direction prédéterminée et
    former un signal de sortie à partir du signal d'entrée (14) au moyen de la réduction sélectionnée (8, 9) du bruit ou des réductions de bruit (8, 9) combinées,
    caractérisé en ce que
    la première réduction de bruit (8) est sélectionnée lorsque le signal d'entrée est stationnaire et la deuxième réduction de bruit (9) est sélectionnée lorsque le signal d'entrée n'est pas stationnaire.
EP10152645.7A 2009-03-06 2010-02-04 Dispositif auditif et procédé de réduction d'un bruit parasite pour un dispositif auditif Active EP2226795B1 (fr)

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Application Number Priority Date Filing Date Title
DE102009012166A DE102009012166B4 (de) 2009-03-06 2009-03-06 Hörvorrichtung und Verfahren zum Reduzieren eines Störgeräuschs für eine Hörvorrichtung

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EP2226795A1 EP2226795A1 (fr) 2010-09-08
EP2226795B1 true EP2226795B1 (fr) 2016-05-11

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US (1) US8600087B2 (fr)
EP (1) EP2226795B1 (fr)
DE (1) DE102009012166B4 (fr)
DK (1) DK2226795T3 (fr)

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EP3107097B1 (fr) * 2015-06-17 2017-11-15 Nxp B.V. Intelligilibilité vocale améliorée
DE102017206788B3 (de) * 2017-04-21 2018-08-02 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
EP3692529B1 (fr) * 2017-10-12 2023-05-24 Huawei Technologies Co., Ltd. Appareil et procédé d'amélioration de signaux
DE102019214220A1 (de) * 2019-09-18 2021-03-18 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
US11587575B2 (en) * 2019-10-11 2023-02-21 Plantronics, Inc. Hybrid noise suppression
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DE102009012166A1 (de) 2010-09-16
EP2226795A1 (fr) 2010-09-08
DK2226795T3 (da) 2016-08-29
US8600087B2 (en) 2013-12-03
US20100226515A1 (en) 2010-09-09

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