EP3068146B1 - Procede de fonctionnement d'un appareil auditif et appareil auditif - Google Patents

Procede de fonctionnement d'un appareil auditif et appareil auditif Download PDF

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Publication number
EP3068146B1
EP3068146B1 EP16158247.3A EP16158247A EP3068146B1 EP 3068146 B1 EP3068146 B1 EP 3068146B1 EP 16158247 A EP16158247 A EP 16158247A EP 3068146 B1 EP3068146 B1 EP 3068146B1
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EP
European Patent Office
Prior art keywords
noise
gain factor
intensity
ovd
parameter
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EP16158247.3A
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German (de)
English (en)
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EP3068146A1 (fr
Inventor
Homayoun KAMKAR-PARSI
Marko Lugger
Tobias Daniel Rosenkranz
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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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
    • H04R25/30—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
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/43—Electronic input selection or mixing based on input signal analysis, e.g. mixing or selection between microphone and telecoil or between microphones with different directivity characteristics
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • 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
    • H04R25/48—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using constructional means for obtaining a desired frequency response
    • 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
    • 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

Definitions

  • the invention relates to a method for operating a hearing device and a hearing aid suitable for this purpose.
  • a hearing aid is typically used by a user to improve their hearing.
  • the hearing device comprises at least one microphone for recording noises in the environment of the user, which are then amplified in the hearing aid by means of an amplifier and output via a receiver.
  • Different configurations are possible for the hearing aid, which are then carried in different ways by the user: for example, a CIC device is completely worn in the ear, in a RIC device, only the earpiece is worn in the ear and the other components in a common housing behind the ear and a BtE device all components are arranged in a common housing, wherein the sounds emitted by the listener are often passed through a sound tube or the like to the ear.
  • the gain of an input signal generated by the microphone is essentially determined by an amplification factor set in the amplifier.
  • an amplification factor set in the amplifier.
  • the amplification performed by the hearing aid changes when its own voice is detected.
  • the EP 1 744 589 A2 For example, a hearing apparatus and a method for self-detection are described.
  • the activity of one's own voice is permanently captured and included in the control of algorithms of the hearing device, thereby avoiding artifacts and false control triggered by one's own voice.
  • an automatic gain control of the hearing aid is frozen.
  • WO 2014/075195 discloses a hearing aid in which an automatic gain adjustment depends on the detection of the user's own voice and in addition on the ambient noise.
  • the disadvantages which result from a dynamic adaptation of the amplification factor as a function of the user's voice should at least be reduced and avoided as far as possible.
  • a suitable hearing aid should be specified.
  • the hearing aid is worn by a user and includes at least one microphone for receiving sounds from the environment of the user, an amplifier and a handset, to output amplified sounds.
  • an input signal is generated by the microphone, which is amplified in the amplifier with an adjustable gain factor.
  • the amplification factor can be adjusted manually by means of a control element on a housing of the hearing device or by means of a remote control by the user in the sense of a volume control.
  • the hearing aid further includes an OVD unit, where OVD stands for own voice detection.
  • OVD stands for own voice detection.
  • an OVD parameter is determined which indicates whether the user speaks for himself or not. In this way, an inherent voice recognition is realized in particular.
  • the OVD parameter is a first parameter here.
  • the OVD parameter is realized as a Boolean parameter, which is true if the user speaks for himself and otherwise is false.
  • a continuous OVD parameter is conceivable.
  • a suitable OVD unit is in particular in the above-mentioned, subsequently filed application with the file reference DE 10 2014 217 172.5 , described.
  • the amplification factor is set within a certain value range as a function of the OVD parameter, whereby a dynamic gain adaptation is realized in eigen providedsituationen.
  • Characteristic of an eigen providedsituation are in particular temporally alternating phases of speaking and silence of the user, ie this leads, for example, a conversation with another person.
  • the gain of the input signal then takes place depending on whether the user speaks or not.
  • the gain factor is reduced in a situation in which the user speaks, compared to a situation in which the user does not speak.
  • the amplification factor is additionally set as a function of a noise which is not the user's own voice, but rather a particular external noise, for example a fan or engine noise or generally a background noise.
  • a noise which is not the user's own voice, but rather a particular external noise, for example a fan or engine noise or generally a background noise.
  • a detection or an estimate of the noise occurs. It is therefore first determined whether a noise is present.
  • the noise is in particular a stationary noise, which does not change at all or only to a small extent over a longer period of time.
  • stationary is understood to mean that the noise has an acoustic frequency spectrum with an average level which does not change by more than 3 to 6 dB over a period of about 1 to 10 s. In other words, the statistical properties of the frequency spectrum of the noise remain essentially constant over a certain period of time.
  • an environmental noise at a substantially constant volume level i.e., an ambient noise level.
  • a stationary noise or interference signal so this is correspondingly times more and sometimes less amplified.
  • stationary noise are fan and engine noise in a vehicle. Due to the temporally varying amplification of the stationary ambient noise due to a constantly adjusted amplification factor as a function of the user's speech activity, this results in a perceived as unpleasant modulation of ambient noise. If no noise is present, especially no stationary noise, i. if no noise is detected, in particular a conventional gain adjustment is made as a function of the OVD parameter.
  • An essential advantage of the invention is now in particular that an unpleasant modulation of a stationary noise due to one of the own voice of the User-dependent dynamic gain adjustment is prevented, in particular by advantageously reducing the value range of the dynamic gain adjustment.
  • the additional adjustment as a function of a noise prevents its unpleasant modulation, in particular in that the modulation of the amplification factor due to the OVD unit is suitably reduced.
  • the amplified input signal, ie the output signal of the hearing aid has a modulation depth which is adjusted as a function of the noise, ie in particular reduced.
  • a hearing aid operated in this way offers significantly improved hearing comfort, in particular since the user's own voice is reproduced correctly and at the same time a modulation of otherwise stationary noise is avoided or at least reduced to an acceptable level.
  • the amplification factor is set not only independently of each other on the one hand as a function of the OVD parameter and, on the other hand, as a function of the noise. Rather, these two dependencies also affect each other, i. E. the setting of the gain as a function of the OVD parameter is itself dependent on the presence and / or the properties of a noise. Depending on what kind of noise situation is present, another dynamic gain adjustment based on the OVD parameter makes sense.
  • the adjustment of the amplification factor as a function of the noise thus altogether aims to modify that setting of the amplification factor which takes place as a function of the OVD parameter, namely as a function of the noise. This is done, for example, by setting the value range of the dynamic gain adjustment depending on the noise, ie by a direct intervention in the dynamic gain adjustment.
  • the amplification factor is additionally set in order to counteract the adjustment as a function of the OVD parameter, ie by superimposing the dynamic gain adjustment in order to modify it in the end result.
  • modify is generally understood that ultimately an adjustment, compensation or change takes place. In the present case, a modification of the gain adjustment by an additional adjustment in response to a noise occurs.
  • the gain adjustment due to the OVD unit is optimally modified as a function of the noise.
  • the gain is reduced if the user speaks for himself, and increased if the user does not speak himself.
  • the amplification factor for example, at a speech activity of the user is not reduced or less, compared to a hearing aid without such additional adjustment in response to a stationary noise.
  • a modulation of the noise when changing the user's speech activity is then reduced accordingly or avoided altogether and it results in a more pleasant and more natural reproduction of ambient noise for the user.
  • an intensity of the noise is determined by means of a noise estimator, also referred to as a noise estimator, and the amplification factor adjusted depending on the intensity.
  • the intensity is a second parameter which is used in addition to the OVD parameter for setting the amplification factor.
  • the user's own speech activity at a higher detected intensity, i. with a louder noise, set a larger gain than with a lower intensity, i. a lesser noise, and at a lower detected intensity a lower gain than at a higher intensity.
  • This advantageously reduces the difference between the amplification factor set during phases of one's own speech activity and the amplification factor set during phases of inherent inactivity when changing the amplification factor as a function of the OVD parameter.
  • Under his own speech activity is understood in particular that the user speaks himself, while this does not speak itself in own inactivity.
  • the described measure is based on the finding that the modulation of a noise with a lower volume, ie lower intensity is perceived as less disturbing than the modulation of a noise with higher intensity in comparison. Therefore, in an inherent voice situation with a loud noise, advantageously, the gain factor from the self-inactivity gain factor is less reduced than with a quieter noise, so that in particular the modulation of the noise due to the OVD unit switchover is advantageously reduced with noisy noise.
  • the gain factor from the self-inactivity gain factor is less reduced than with a quieter noise, so that in particular the modulation of the noise due to the OVD unit switchover is advantageously reduced with noisy noise.
  • the gain factor from the self-inactivity gain factor is less reduced than with a quieter noise, so that in particular the modulation of the noise due to the OVD unit switchover is advantageously reduced with noisy noise.
  • the gain factor from the self-inactivity gain factor is less reduced than with a quieter noise, so that in particular the modulation of the noise due to the OVD
  • the first intensity is about 50 dB and the second intensity is greater and about 80 dB, then a lower gain factor is set in the case of the first intensity than in the case of the second intensity, both gain factors being smaller than the gain factor which is set if the user does not speak himself. A louder noise is then less modulated compared to a quieter noise.
  • the change in the gain produced by the OVD unit is preferably reduced, thereby setting a higher gain factor at times of own speech activity.
  • the change in the amplification factor is correspondingly increased so that a lower amplification factor is set at times of one's own speech activity.
  • the setting of the amplification factor at times own speech activity is proportional to the determined intensity or alternatively under or disproportionately.
  • the noise estimator determines the intensity, ie the volume or the volume level of the noise, in particular from the input signal.
  • a method, in particular algorithm is used which takes into account only stationary portions of a noise.
  • the advantage in this case is, in particular, that such a method can be used in principle only to determine stationary noise and non-stationary noise can not be detected.
  • the gain factor will then be set substantially dependent on the OVD parameter. Only in the presence of a stationary signal, the gain is additionally adjusted depending on this only stationary noise. On the other hand, in the case of only modulated noise, an optimal OVD functionality of the hearing aid is thus ensured.
  • a particularly suitable method is a so-called minimum-statistics method. Therefore, in a suitable variant, the intensity of the noise is determined by means of a minimum statistics method. The noise estimator is then designed to carry out such a minimum statistics method and determines the intensity, ie the volume level, in particular by means of a corresponding statistical evaluation of the input signal.
  • a possible embodiment of a minimum-statistics method is described, for example, in: Martin, R. (1994), "Spectral subtraction based on minimum statistics
  • a minimum-statistics method is particularly simple to implement and, in principle, can only be used to detect stationary noise, while non-stationary noise is essentially ignored, which in turn results in the advantages mentioned above.
  • the input signal is first of all subdivided into a multiplicity of successive time intervals, from which a frequency spectrum is determined in each case by means of a Fourier transformation, ie a spectrum in which a specific level is assigned to each frequency.
  • the noise estimator the intensity is then determined in particular by measuring the level in a number of frequency ranges of a respective frequency spectrum which corresponds in particular to the intensity of the noise in the corresponding frequency range.
  • a certain and in particular frequency-dependent minimum intensity for example a sound pressure level of about 50 dB
  • a steady-state noise with a higher intensity than the minimum intensity is determined, an additional adaptation of the amplification factor to avoid or at least reduce a possible modulation of the noise by the OVD unit takes place.
  • a stationarity of the noise is determined as a third parameter by means of a stationarity detector and the amplification factor is set as a function of the stationarity.
  • the determination of the stationarity is suitably carried out by means of a statistical examination of the input signal. Therefore, in a suitable embodiment, the stationarity is determined as an intensity stability, for example as a variance of the mean level or the level in a certain frequency range and over a certain period of time, ie in particular over several frequency spectra. For example, the variance of the level is determined at about 1 kHz over a period of about 1 s.
  • the stationarity is suitably determined as a frequency stability.
  • a level maximum is determined, in particular in the frequency spectrum of the input signal, and the variance of the frequency assigned to this level maximum is determined.
  • the stationarity is suitably determined as the ratio of the levels of stationary and non-stationary portions of the noise.
  • the respective levels are determined and set in relation to each other.
  • a stationarity threshold value it is expedient to carry out a defined demarcation between stationary and non-stationary noise by specifying a stationarity threshold value. If a stationarity is then determined which exceeds the stationarity threshold, then the noise is regarded as non-stationary and no additional adjustment of the amplification factor takes place. However, if the stationarity is below the stationarity threshold, a stationary noise is correspondingly detected and the amplification factor is set accordingly.
  • the parameters are each mapped to a scaling factor, for example in the range from 0 to 1, and the amplification factor is set by multiplication by the scaling factors.
  • the amplification of the input signal is performed with the amplification factor specified by the amplifier.
  • the gain factor is set in a particularly simple manner depending on the parameters, namely depending on the OVD parameter, i. from an OVD situation, stationarity, i. the presence of a stationary noise, as well as the intensity, i. the volume of the stationary noise.
  • the mapping takes place in particular in the sense of a so-called mapping, in which a value of the dimensionless interval 0 to 1 is assigned to a specific value of a parameter.
  • a limited value range of a respective parameter is mapped to the interval. For example, a picture of the intensity only for sound pressure level from a range of about 50 to 80 dB, wherein at a higher sound pressure level, ie higher intensity and while the user does not speak even higher amplification to take place and assigned according to an intensity of 80 dB, the scaling factor 0 and, with an intensity of 50 dB, a scaling factor of 1.
  • the assignment takes place, for example, linearly or logarithmically; outside is correspondingly constant 0 or 1 assigned.
  • the scaling factors are first combined into a total scaling factor, and the gain factor is then set by multiplying by the total scaling factor.
  • the combining takes place in particular by means of a multiplier, with the scaling values as input values and the total scaling factor as the output value. This then forms in particular the result of a scene analysis, which is performed by the hearing aid in terms of the user's speech activity and the presence of stationary noise.
  • the input signal is typically composed of different frequencies, which in particular form an acoustic frequency spectrum with a number of frequency ranges. Frequently, moreover, different frequencies or frequency ranges of the frequency spectrum are amplified differently, since, for example, a particular frequency range is given greater importance.
  • the gain factor is set frequency-dependent, in particular the scaling factors are frequency-dependent, i. each a function of frequency.
  • an independent adjustment of the amplification factor is carried out in different frequency ranges, also referred to as frequency bands, of the input signal.
  • different significant frequency ranges are independent of each other and subject to a correspondingly adapted dynamic gain adjustment as needed.
  • the hearing device has a control unit for carrying out the method.
  • This is suitably connected to the amplifier and comprises corresponding modules for adjusting the amplification factor.
  • the modules are in particular the OVD unit as well as the noise estimator and / or the stationarity detector.
  • an embodiment of the control unit as an application-specific integrated circuit, so-called ASIC, conceivable, wherein the modules are each realized as part of this circuit.
  • ASIC application-specific integrated circuit
  • a configuration as a programmable microcontroller is possible, in which the modules are partially or completely implemented as program modules.
  • the advantages of the invention are, in particular, that in addition to a dynamic adjustment of the amplification factor as a function of the speech activity of the user of the hearing aid, an extended dynamic adjustment is made taking into account stationary noise.
  • the intensity and / or stationarity is determined as characteristic parameters of a respective stationary noise and used to adapt the amplification factor.
  • the determined parameters are mapped to scaling factors.
  • a hearing aid 2 which here is a so-called RIC device and comprises a housing 4, which is supported by a user, not shown, behind the ear.
  • the hearing device 2 further comprises a number of microphones 6, a control unit 8, an amplifier 10 and a receiver 12. Furthermore, a battery 14 for the power supply is present.
  • an input signal E is generated which, during operation, is passed on to the amplifier 10 for amplification and amplified there with a specific amplification factor V.
  • the thus amplified input signal E is then output via the handset 12, more precisely via a loudspeaker of the handset 12, not shown here in detail.
  • the handset 12 is worn by the user directly in the ear and is connected via a suitable lead 16 to the amplifier 10.
  • the hearing device 2 it is also possible for the hearing device 2 to be a BTE device, in which the handset 12 is mounted in or on the housing 4 and the supply line 16 is designed as a sound tube.
  • the hearing aid 2 is a CIC device, which is worn completely in the ear.
  • the amplification factor V is adjustable by means of the control unit 8.
  • the amplification factor may also be adjustable in another way, not shown in more detail, for example manually by an operating element (not shown) on the hearing device 2.
  • the amplification factor V is set by the control unit 8 FIG. 2 by an overall scaling factor G provided by the control unit 8.
  • the conventionally used amplification factor V is multiplied by the overall scaling factor G in order to obtain a matched amplification factor V.
  • the overall amplification factor G is the result of an analysis of the input signal E carried out by the control unit 8.
  • the analysis essentially takes place with regard to the speech activity of the user and possible noises in the environment of the user.
  • the control unit 8 comprises several, here three modules 20, 22, 24, namely an OVD unit 20, a noise estimator 22 and a stationarity detector 24. These each generate a scaling factor S1, S2, S3 on the basis of characteristic parameters derived from the input signal E can be determined. These three scaling factors S1, S2, S3 are combined by means of a multiplier 26 to the total scaling factor G.
  • an OVD parameter is first determined by means of the OVD unit 20, which indicates whether the user speaks for himself, that is, whether the user's speech activity is present. If this is the case, the gain factor V should be reduced, otherwise increased.
  • the OVD parameter is mapped to the scaling factor S1 in a range between 0 and 1. For example, the mapping takes place in such a way that the scaling factor S1 is 0 in the case of the user's own speech activity and otherwise 1.
  • the gain V is then adjusted according to the situation such that either no gain or maximum gain occurs.
  • a gradation, z. B. due to the level, ie the volume of the user's voice.
  • a possibly recorded noise is analyzed, with respect to its intensity.
  • the determined intensity as a characteristic parameter of the noise indicates in particular its volume and is thus a measure of the volume of stationary background noise.
  • the intensity is now mapped to the scaling factor S2, that stationary noise when modulating the scaling factor S1 by the OVD unit 22 are modulated as little as possible, and the less, the louder the noise.
  • no or only a slight adjustment of the amplification factor V is made via the scaling factor S2 of the noise estimator 22.
  • the predetermined by the OVD unit 20 scaling factor S1 is counteracted.
  • the stationarity detector 24 additionally determines to what extent the noise is actually a stationary noise.
  • the input signal E is examined with respect to its temporal evolution, to determine a stationarity.
  • the intensity and frequency stability in one or more frequency ranges are statistically investigated and, for example, variances of specific levels or frequencies in the frequency spectrum of the input signal E are determined. These variances are then mapped to a scaling factor S3 to exert further influence on the gain factor V.
  • the amplification factor V is adjusted as a function of the overall acoustic situation around the user.
  • an adjustment is made as a function of the speech activity of the user by the OVD unit 20 and a setting in response to a stationary noise by the modules 22, 24. It is possible by means of the modules 22, 24, negative effects in adjusting the gain V through compensate or at least reduce the OVD unit.

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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)

Claims (14)

  1. Procédé de mise en fonctionnement d'un appareil auditif (2), dans lequel
    - un signal d'entrée (E) est généré au moyen d'un microphone (6),
    - le signal d'entrée (E) est amplifié dans un amplificateur (10) à gain réglable (V),
    - le signal d'entrée amplifié (E) est délivré par l'intermédiaire d'un écouteur (12),
    - un paramètre OVD est déterminé en tant que premier paramètre au moyen d'une unité OVD (20), dans lequel le paramètre OVD indique si l'utilisateur parle lui-même ou non,
    - le gain (V) est réglé en fonction du paramètre OVD en tenant compte d'un bruit de fond,
    - le réglage du gain en fonction du paramètre OVD est lui-même fonction de la présence et/ou des propriétés du bruit de fond,
    - le réglage du gain (V) est modifié en fonction du paramètre OVD, en réglant en outre le gain (V) en fonction du bruit de fond, en modifiant en fonction du bruit de fond le réglage du gain qui s'effectue en fonction du paramètre OVD.
  2. Procédé selon la revendication précédente,
    caractérisé en ce que le gain (V) est réglé à l'intérieur d'une plage de valeurs, de telle sorte que dans les situations dans lesquelles l'utilisateur entend sa propre voix, une adaptation dynamique du gain soit réalisée à l'intérieur de la plage de valeurs, et en ce que le gain (V) est réglé en fonction du bruit de fond en réduisant la plage de valeurs de l'adaptation du gain afin de réduire une modulation du bruit de fond sur la base de l'adaptation du gain.
  3. Procédé selon l'une quelconque des revendications précédentes,
    caractérisé en ce que le bruit de fond est un bruit de fond stationnaire.
  4. Procédé selon l'une quelconque des revendications précédentes,
    caractérisé en ce qu'une intensité du bruit de fond est déterminée en tant que deuxième paramètre au moyen d'un estimateur de bruit de fond (22) et en ce que le gain (V) est réglé en fonction de l'intensité.
  5. Procédé selon la revendication précédente, caractérisé en ce que, lors d'une activité vocale propre de l'utilisateur, lorsque l'intensité déterminée est plus élevée, on règle un gain plus élevé que lorsque l'intensité est comparativement plus faible, et lorsque l'intensité déterminée est plus faible, on règle un gain plus faible que lorsque l'intensité est comparativement plus élevée.
  6. Procédé selon l'une des deux revendications précédentes,
    caractérisé en ce que, pour déterminer l'intensité, on utilise un procédé prenant uniquement en compte les parties stationnaires d'un bruit de fond.
  7. Procédé selon l'une quelconque des revendications 4 à 6,
    caractérisé en ce que l'intensité du bruit de fond est déterminée au moyen d'un procédé à base de statistiques des minima.
  8. Procédé selon l'une quelconque des revendications précédentes,
    caractérisé en ce qu'une stationnarité du bruit de fond est déterminée en tant que troisième paramètre au moyen d'un détecteur de stationnarité (24) et en ce que le gain (V) est réglé en fonction de la stationnarité.
  9. Procédé selon la revendication précédente,
    caractérisé en ce que la stationnarité est déterminée par détermination d'une stabilité de fréquence et/ou d'une stabilité d'intensité du bruit de fond.
  10. Procédé selon l'une quelconque des revendications précédentes et au moins l'une des revendications 4 ou 7,
    caractérisé en ce que les paramètres sont respectivement représentés avec un facteur d'échelle (S1, S2, S3) et en ce que le gain (V) est réglé par multiplication par les facteurs d'échelle (S1, S2, S3).
  11. Procédé selon la revendication précédente,
    caractérisé en ce que les facteurs d'échelle (S1, S2, S3) sont initialement regroupés sous la forme d'un facteur d'échelle global (G) et en ce que le gain (V) est réglé par multiplication par le facteur d'échelle global (G).
  12. Procédé selon l'une quelconque des revendications précédentes,
    caractérisé en ce que le gain (V) est réglé en fonction de la fréquence.
  13. Procédé selon la revendication précédente,
    caractérisé en ce qu'un réglage indépendant du gain (V) est respectivement effectué dans différentes plages de fréquences du signal d'entrée (E).
  14. Appareil auditif (2) pouvant être mis en fonctionnement au moyen d'un procédé selon l'une quelconque des revendications précédentes, comportant un microphone (6) destiné à générer un signal d'entrée (E), un amplificateur (10) destiné à amplifier le signal d'entrée (E) avec un gain déterminé (V), un écouteur (12) destiné à délivrer le signal d'entrée amplifié (E), et une unité de commande (8) réalisée de manière à
    - déterminer un paramètre OVD au moyen d'une unité OVD (20) en tant que premier paramètre, dans lequel le paramètre OVD indique si l'utilisateur parle lui-même ou non,
    - régler le gain (V) en fonction du paramètre OVD en tenant compte d'un bruit de fond,
    - le réglage du gain en fonction du paramètre OVD étant lui-même fonction de la présence et/ou des propriétés d'un bruit de fond, et
    - régler en outre le gain (V) en fonction du bruit de fond en modifiant en fonction du bruit de fond le réglage du gain qui s'effectue en fonction du paramètre OVD.
EP16158247.3A 2015-03-13 2016-03-02 Procede de fonctionnement d'un appareil auditif et appareil auditif Revoked EP3068146B1 (fr)

Applications Claiming Priority (1)

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DE102015204639.7A DE102015204639B3 (de) 2015-03-13 2015-03-13 Verfahren zum Betrieb eines Hörgeräts sowie Hörgerät

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EP3068146B1 true EP3068146B1 (fr) 2017-10-11

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EP (1) EP3068146B1 (fr)
JP (1) JP6109985B2 (fr)
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DK (1) DK3068146T3 (fr)

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US20170347183A1 (en) * 2016-05-25 2017-11-30 Smartear, Inc. In-Ear Utility Device Having Dual Microphones
DK3328097T3 (da) 2016-11-24 2020-07-20 Oticon As Høreanordning, der omfatter en egenstemmedetektor
DE102018216667B3 (de) 2018-09-27 2020-01-16 Sivantos Pte. Ltd. Verfahren zur Verarbeitung von Mikrofonsignalen in einem Hörsystem sowie Hörsystem
DK3664470T3 (da) 2018-12-05 2021-04-19 Sonova Ag Fremskaffelse af feedback om lydstyrken af egen stemme for en bruger af et høreapparat
DE102019214220A1 (de) * 2019-09-18 2021-03-18 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
CA3156121C (fr) 2019-10-10 2024-03-19 Shenzhen Shokz Co., Ltd. Dispositif audio
EP4055838A1 (fr) * 2019-11-04 2022-09-14 Sivantos Pte. Ltd. Procédé de fonctionnement d'un système auditif et système auditif
CN111243616A (zh) * 2020-01-09 2020-06-05 广西民族大学 一种基于自动增益的恒定音量输出方法
DE102020201615B3 (de) 2020-02-10 2021-08-12 Sivantos Pte. Ltd. Hörsystem mit mindestens einem im oder am Ohr des Nutzers getragenen Hörinstrument sowie Verfahren zum Betrieb eines solchen Hörsystems
CN113132881B (zh) * 2021-04-16 2022-07-19 深圳木芯科技有限公司 基于多麦克风自适应控制佩戴者声音放大程度的方法

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EP1326479A2 (fr) 1997-04-16 2003-07-09 DSPFactory Ltd. Procédé et dispositif servant à réduire le bruit, en particulier pour des prothèses auditives
US7039195B1 (en) 2000-09-01 2006-05-02 Nacre As Ear terminal
EP1744589A2 (fr) 2005-07-11 2007-01-17 Siemens Audiologische Technik GmbH Appareil auditif et procédé correspondant pour la détection de voix-propres
US7489789B2 (en) 2004-03-02 2009-02-10 Oticon A/S Method for noise reduction in an audio device and hearing aid with means for reducing noise
US20090147966A1 (en) 2007-05-04 2009-06-11 Personics Holdings Inc Method and Apparatus for In-Ear Canal Sound Suppression
US20110137649A1 (en) 2009-12-03 2011-06-09 Rasmussen Crilles Bak method for dynamic suppression of surrounding acoustic noise when listening to electrical inputs
WO2014075195A1 (fr) 2012-11-15 2014-05-22 Phonak Ag Formation de la propre voix d'un utilisateur dans un instrument d'aide auditive
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EP1326479A2 (fr) 1997-04-16 2003-07-09 DSPFactory Ltd. Procédé et dispositif servant à réduire le bruit, en particulier pour des prothèses auditives
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EP1744589A2 (fr) 2005-07-11 2007-01-17 Siemens Audiologische Technik GmbH Appareil auditif et procédé correspondant pour la détection de voix-propres
US20090147966A1 (en) 2007-05-04 2009-06-11 Personics Holdings Inc Method and Apparatus for In-Ear Canal Sound Suppression
US20110137649A1 (en) 2009-12-03 2011-06-09 Rasmussen Crilles Bak method for dynamic suppression of surrounding acoustic noise when listening to electrical inputs
WO2014075195A1 (fr) 2012-11-15 2014-05-22 Phonak Ag Formation de la propre voix d'un utilisateur dans un instrument d'aide auditive
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US20160269834A1 (en) 2016-09-15
JP6109985B2 (ja) 2017-04-05
EP3068146A1 (fr) 2016-09-14
DE102015204639B3 (de) 2016-07-07
US9973861B2 (en) 2018-05-15
DK3068146T3 (da) 2018-01-15
JP2016171569A (ja) 2016-09-23
CN105979460B (zh) 2019-11-12
CN105979460A (zh) 2016-09-28

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