EP1489882A2 - Procédé pour l'opération d'une prothèse auditive aussi qu'une prothèse auditive avec un système de microphone dans lequel des diagrammes de rayonnement différents sont sélectionnables. - Google Patents

Procédé pour l'opération d'une prothèse auditive aussi qu'une prothèse auditive avec un système de microphone dans lequel des diagrammes de rayonnement différents sont sélectionnables. Download PDF

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Publication number
EP1489882A2
EP1489882A2 EP04010127A EP04010127A EP1489882A2 EP 1489882 A2 EP1489882 A2 EP 1489882A2 EP 04010127 A EP04010127 A EP 04010127A EP 04010127 A EP04010127 A EP 04010127A EP 1489882 A2 EP1489882 A2 EP 1489882A2
Authority
EP
European Patent Office
Prior art keywords
microphone
signal
hearing aid
signals
microphone signals
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP04010127A
Other languages
German (de)
English (en)
Other versions
EP1489882A3 (fr
Inventor
Torsten Dr. Niedertränk
Tom Weidner
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 GmbH
Original Assignee
Siemens Audioligische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP1489882A2 publication Critical patent/EP1489882A2/fr
Publication of EP1489882A3 publication Critical patent/EP1489882A3/fr
Withdrawn legal-status Critical Current

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Classifications

    • 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
    • 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

Definitions

  • the invention relates to a method for operating a hearing aid with a microphone system, a signal processing unit and an output converter, the microphone system comprises at least two microphone units, of which Microphone signals go out and the directional characteristics different Show order.
  • the invention further relates to a hearing aid for performing the method.
  • Classification devices are found in modern hearing aids of listening situations use. Depending on the listening situation the transmission parameters of the hearing aid are automatic varied.
  • the classification can include influence have on the mode of operation of noise suppression algorithms as well as the microphone system. For example selected depending on the recognized hearing situation (switched discretely or continuously blended) between one omnidirectional polar pattern (polar pattern zero order) and a clear directivity of the microphone system (Polar pattern of first or higher order).
  • Gradient microphones are used to generate the directional characteristic used or multiple omnidirectional microphones electrically interconnected. Such microphone systems show a frequency-dependent transmission behavior in which a there is a clear drop to low frequencies. In contrast, the noise behavior of the microphones is frequency-independent and slightly compared to an omnidirectional microphone strengthened.
  • the high-pass frequency response of the microphone system can be compensated for by amplifying the low frequencies.
  • the noise present in the low frequency range is thereby also reinforced and, under certain circumstances, clear and disturbing audible, while soft noises are masked by the noise become.
  • a hearing aid with a Signal processing unit and at least two microphones the different to form directional microphone systems Order can be interconnected, the directional microphone systems in turn in the frequency of that of the Microphones emitted microphone signals depending on the weighting are interconnectable. Depending on the result the cutoff frequency between adjacent Frequency bands where a different Weighting of the microphone signals is provided become.
  • DE 197 03 228 A1 describes a method for reinforcement known from input signals of a hearing aid, in which under Using an AGC (Automatic Gain Control) circuit a compression the signals picked up by the hearing aid depending of the detectable signal level.
  • AGC Automatic Gain Control
  • the compression varies adaptively.
  • the signal analysis as well as the compression can also be in parallel in different Frequency bands are carried out.
  • a hearing aid with directional microphone system is known from EP 0 942 627 A2 with a signal processing device, a handset and several microphones known, the output signals for Generation of an individual directional microphone characteristic via Delay devices and the signal processing device Can be interconnected in different weightings are.
  • the preferred one Reception direction (main direction) in adaptation to one present hearing situation can be adjusted individually.
  • a hearing aid with an omnidirectional Microphone and a directional microphone First or higher order known.
  • the directional microphone signal Microphones will be in the range of low signal frequencies Amplitude amplified and the microphone signal of the omnidirectional Microphones adjusted.
  • Both the microphone signal from the omnidirectional microphone as well as the microphone signal of the Directional microphones are fed to a switchover unit. In a first switch position of the switchover unit, this is omnidirectional microphone and in a second switch position the switching unit the directional microphone with a hearing aid amplifier connected.
  • the switching unit can be dependent the signal level of a microphone signal automatically switch.
  • a disadvantage of the known hearing aids with a directional microphone system is that in certain listening situations either the directionality of the microphone system is not used optimally or that a high degree of directivity becomes a clearly audible deterioration in sound quality results.
  • the object of the present invention is the sound quality to improve a hearing aid with directional microphone system.
  • the task is also carried out with a hearing aid of the method with a microphone system, a signal processing unit and an output converter
  • the Microphone system comprises at least two microphone units, from which emit microphone signals and the directional characteristics of different order, solved by means of Splitting the microphone signals of the microphone units with Polar patterns of different order in several Frequency bands, means for performing signal analysis at least one of the microphone signals and means for different Weighting of the microphone signals in the individual Frequency bands depending on the result of the signal analysis.
  • the hearing aid according to the invention comprises a microphone system with at least two microphones for directional characteristics zero and first order. Preferably however, there are more than two microphones, so that directional characteristics of second and higher order possible are.
  • the hearing aid device further comprises a signal processing unit for processing and frequency dependent Amplification of the microphone signal generated by the microphone system.
  • the signal is usually output by an acoustic signal Output signal using a handset. But there are also others, e.g. Output transducers generating vibrations are known.
  • a microphone unit with a directional characteristic first order can for example through a single gradient microphone or the electrical Connection of two omnidirectional microphones implemented become.
  • first order directional microphones is a theoretical one achievable maximum value of the directive index (DI) of 6 dB (hypercardioid).
  • DI directive index
  • Directional microphones second and higher order have DI values of 10 dB and more, for example for better speech intelligibility are advantageous.
  • a hearing aid contains a microphone system with three omnidirectional microphones, for example can be based on this by suitable connection of the microphones at the same time microphone units with directional characteristics zero to second order can be realized.
  • a single omnidirectional microphone provides one Microphone unit represents zero order. Is with two omnidirectional Microphones delay the microphone signal of a microphone, inverted and to the microphone signal of the other microphone added, this creates a first-order microphone unit. Again, with two first order microphone units the microphone signal of a microphone unit is delayed, inverted and the microphone signal of the second microphone unit added first order, this results in a microphone unit with second order polar pattern. Leave this way itself - depending on the number of omnidirectional microphones - Realize microphone units of any order.
  • a microphone system comprises different microphone units Order, so there can be between different directional characteristics can be switched, e.g. by switching on or off one or more microphones. Furthermore, a suitable electrical connection of the microphone units also any mixed forms between the directional characteristics different order are generated. For this, the Microphone signals of the microphone units weighted differently and added before being in the signal processing unit of the hearing aid are processed and amplified. So a continuous, smooth transition between different directional characteristics can be realized, thereby avoiding annoying artifacts when switching to let.
  • the hearing aid according to the invention advantageously takes place with at least one microphone signal, a signal analysis, with of certain properties of the microphone signal become.
  • a signal analysis in connection with the Invention is dependent on these signal properties the signal frequency can be determined. This makes it possible the weighting of microphone signals by microphone units go out with different directivity, depending the result of the signal analysis adaptively to the respective Adapt hearing situation. So in every frequency range one optimized for the respective frequency range Directivity can be set. In particular, it can as much directivity as possible are allowed without the proportion of the noise caused by the microphone system in the output signal of the hearing aid as disturbing is felt.
  • This effect produced by the invention is achieved in that a directivity only in the frequency ranges of the useful signal is generated, in which an increased Microphone noise at most a slight deterioration in sound caused for the hearing aid wearer. Becomes e.g. in the "conversation" listening situation, only a high signal level found in the frequency range between 1 kHz and 3 kHz, so gets the microphone signal in this frequency range from the microphone unit with the highest order that greatest weight. In the other frequency ranges with lower ones Signal levels are advantageous by an appropriate Weighting of the microphone signals on a directivity at least largely dispensed with.
  • the signal level of the Microphone signal determined depending on the signal frequency.
  • the following rough settings of the microphone system can then be made from this derive: With a high signal level of the microphone signal the microphone noise from the input signal covered and not perceived as disturbing. So in one such a high hearing situation with the microphone system achievable order of directivity can be set. Different however with a very quiet input signal. Here can that caused by the directivity of the microphone system Microphone noise can be perceived as annoying. Is expedient it, at least largely in such a listening situation to forego the directivity and only the omnidirectional Processing the microphone signal or that Weight of the microphone signals from higher microphone units Reduce order.
  • the microphone system advantageously assigned a measuring and control unit directly.
  • a measuring and control unit In addition to direct level measurement, others can also Measurements are carried out, e.g. Measurement of the quadratic Mean RMS (Root Mean Square), which is directly related stand with the signal level of the input signal and Allow conclusions on this. Starting from what is measured Value, the measuring and control unit controls the directional characteristic of the microphone system.
  • quadratic Mean RMS Root Mean Square
  • the invention offers the advantage that at low signal levels the directivity of the acoustic input signal Microphone system is automatically reduced. In particular an omnidirectional at low input signal levels Directional characteristics of the microphone system set. tiresome Microphone noise, especially at low signal levels can be prevented.
  • Signal properties are measured, e.g. the modulation frequency or the modulation depth. Other examples are the Slope of the envelope or the characteristic of the zero crossing. According to the invention, this is determined Signal properties depending on the signal frequency.
  • the signal to be analyzed is divided into several Frequency bands divided. Then in the frequency domain or the directivity in the frequency ranges of the input signal increased according to the result of the signal analysis for the hearing aid wearer is of particular importance. This can for example be a frequency range where the result the modulation analysis indicates a speech signal.
  • the weighting of the microphone signals also on a combinatorial evaluation of several signal properties based, e.g. the signal level and the modulation frequency.
  • this is from the omnidirectional Microphone unit generated microphone signal analyzed.
  • This has the advantage that when analyzing signals different directions in the microphone system Sound signals are taken into account equally.
  • the microphone signal directional microphone This can e.g. "Conversation” can be an advantage in the listening situation the conversation partner of the hearing aid wearer in the direction of view is suspected and therefore advantageously the microphone signal microphone unit oriented in this direction is analyzed becomes. The best results when analyzing the current However, the sound field is obtained when the microphone signals of several microphone units evaluated simultaneously become.
  • the microphone signal to be processed is used usually first divided into frequency bands.
  • the output signals of each Microphones divided into individual frequency bands.
  • the microphone signals in the individual frequency bands for the generation of microphone units with directional characteristics different order interconnected.
  • Another Embodiment of the invention provides that initially Microphone units are provided that are related differentiate their directional characteristics to subsequently the output signals of these microphone units in frequency bands to divide. Also the different ones depending on the frequency Weighting the microphone signals of the microphone units different order is then advantageous in these frequency bands, preferably both the weights the microphone signals of different microphone units in a frequency band as well as the weights of one Microphone unit outgoing microphone signals in different Frequency bands can be set independently of one another.
  • the analysis is preferably also carried out in the invention of the microphone signal or signals in parallel in the individual Frequency bands.
  • This is particularly advantageous because because achieving directivity in the low frequency range is problematic anyway.
  • the microphone system can be set so that this in the low-frequency bands only at very high signal levels acts as a directional microphone and at lower signal levels is only set to omnidirectional reception. In Frequency bands with higher frequencies, however, can already a directivity of the microphone system at lower signal levels be activated.
  • the invention can be used with all known hearing aid types be used with a directional microphone system, for example hearing aids worn behind the ear, in which Ear portable hearing aids, implantable hearing aids or pocket hearing aids.
  • the hearing aid according to the invention also part of a plurality of devices for Care of a hearing aid system that is comprehensive for the hearing impaired be, e.g. Part of a hearing aid system with two worn on the head Hearing aids for binaural care or part a hearing aid system consisting of a wearable on the head Device and a processor unit that can be worn on the body.
  • FIG. 1 shows the simplified block diagram of a hearing aid with a directional microphone system.
  • the directional microphone system includes three omnidirectional microphones 1A, 1B and 1C.
  • the omnidirectional microphones are 1A, 1B and 1C, respectively directly a signal preprocessing unit 2A, 2B or 2C downstream. In this e.g. an A / D conversion as well signal pre-amplification takes place.
  • the two microphones 1A and 1B are electrical to a microphone unit with directional characteristic first order interconnected.
  • the omnidirectional microphone 1B outgoing microphone signal in a circuit unit 3B delayed and inverted and so on like the microphone signal emanating from the microphone 1A Totalizer 4B supplied.
  • the two omnidirectional microphones also form the same 1B and 1C by delaying and inverting that of the Microphone 1C outgoing microphone signal and addition of the the microphone signal 1B outgoing microphone signal in the summer 4C, a microphone unit with a first-order directional characteristic.
  • the microphone signal coming from the summer 4C delayed and inverted in the circuit unit 5C and added to the microphone signal R1, it is thereby a second-order directional microphone unit educated. This goes at the output of the summer 6C Microphone signal R2 emerges.
  • the output signal of the omnidirectional Microphones 1A with directional characteristic of zero order is called R0.
  • the microphone signal R0 of a filter bank 7A Microphone signal R1 of a filter bank 7B and the microphone signal R2 fed to a filter bank 7C.
  • the three filter banks 7A, 7B and 7C in the exemplary embodiment lead to a splitting of the respective microphone signal in three adjacent frequency bands. A division is made in each filter bank of the respective microphone signal in the same frequency bands.
  • the microphone signals K1A are at the output of the filter bank 7A, K2A and K3A.
  • the microphone signals at the output are analog the filter bank 7B with K1B, K2B, K3B and the microphone signals labeled K1C, K2C and K3C at the output of the filter bank 7C.
  • the output signals of the filter banks 7A, 7B and 7C are for Evaluation of a signal analysis and control unit 8 supplied. This is where the microphone signals from the microphone units with directional characteristics of different order in the different frequency bands analyzed.
  • the signal analysis includes in particular the determination of the signal level of the respective microphone signals. However, others can characteristic signal quantities, such as the modulation frequency, the depth of modulation, the slope of the envelope or the characteristic of the zero crossing is determined and be evaluated.
  • control parameters are in the signal analysis and control unit calculated by means of which the directional characteristic in the individual frequency bands can be set.
  • the output signals of the filter banks 7A, 7B and 7C respectively an amplifier V1A, V1B, V1C or V2A, V2B, V2C or V3A, V3B, V3C supplied.
  • the respective reinforcement by the Amplifier is through the signal analysis and control unit 8th set using the calculated parameters. This will optimizes the directional characteristic in the individual frequency bands.
  • the directional characteristic is preferably so set that the highest possible directivity exists without, however, an increase that is perceived as disturbing cause the microphone noise.
  • the microphone signals of the directional microphones can be used with a hearing aid with the shown Microphone system any order between the zeroth and the second order, so any one "Interim Order".
  • the degree of directivity can thus be between of the highest order and no directionality arbitrarily vary, including all intermediate stages are. This means that the optimum level can be set for each input signal Directivity set with the relevant microphone system become. It should be taken into account that the optimal dimension in directionality also from the individual's hearing loss Hearing aid wearer may be dependent.
  • the individual course the directional characteristic curves result in particular from taking audiological parameters into account, e.g. the Resting hearing threshold of a hearing aid wearer in the individual frequency ranges, or taking hearing aid settings into account, such as. an automatic device that is common in hearing aids Gain control AGC (Automatic Gain Control) or the cross section of a ventilation opening.
  • Gain control AGC Automatic Gain Control
  • the microphone system according to the invention enables in particular the setting of an individual course of the directivity depending on the input signal. A hard “switch" between different directives and the associated switching artifacts when changing the This prevents listening situations.
  • Amplifiers V1A to V3C added amplified microphone signals and for further processing of a signal processing unit 9 fed.
  • the signal processing unit 9 the frequency-dependent amplification of the microphone signal M to compensate the individual hearing loss of the hearing aid wearer instead of.
  • This signal processing is also preferably carried out in different frequency bands (channels) of the signal processing unit 9. These frequency bands can be advantageous with regard to number and channel limits also independent of the division generated by the filter banks 7A to 7C his. Alternatively, however, the different gain individual frequency bands to compensate for hearing loss as well already taken over by the amplifiers V1A to V3C become.
  • the signal analysis and control unit 8 is for this to program accordingly.
  • the signal processing unit 9 in this case there is only signal postprocessing, e.g. Final amplification and D / A conversion.
  • Figure 2 illustrates examples of different directional effects R in a frequency band depending on the signal level P in this frequency band.
  • the directionality R can any values between an omnidirectional (nonexistent) Directivity and the maximum, with the microphone system reachable directivity.
  • the characteristic A is at a very low signal level in that Frequency band no directivity available.
  • the directivity however increases with increasing level in the frequency band almost linearly, until the maximum at a certain level Directivity is reached.
  • the characteristic curve B shows with increasing Signal level in the respective frequency band initially only a slight increase in directivity. Only with a lot at high signal levels there is a steep increase in directivity.
  • Such a non-linear characteristic should in particular be set in a low frequency frequency band since directional microphones act as low passes and therefore a quiet one low-frequency input signal requires high amplification, which leads to increased noise. Therefore, in the low frequency range the directivity is advantageously only used, when a high signal level of the input signal in this frequency range is present and therefore only a slight gain is required.
  • a directivity according to the third characteristic curve C is already a proportionate at a low signal level high directivity set. For that is the increase in Directionality with increasing input level smaller than in two previous examples.
  • Such a directivity depending on the signal level is especially for one higher frequency range advantageous because in this by High pass characteristic of the directional microphone system also with low signal level of the input signal and a high one Amplification by the hearing aid only a slight increase microphone noise caused by the high directivity becomes.

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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)
EP04010127A 2003-06-20 2004-04-28 Procédé pour l'opération d'une prothèse auditive aussi qu'une prothèse auditive avec un système de microphone dans lequel des diagrammes de rayonnement différents sont sélectionnables. Withdrawn EP1489882A3 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10327891 2003-06-20
DE10327891 2003-06-20

Publications (2)

Publication Number Publication Date
EP1489882A2 true EP1489882A2 (fr) 2004-12-22
EP1489882A3 EP1489882A3 (fr) 2009-07-29

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EP04010127A Withdrawn EP1489882A3 (fr) 2003-06-20 2004-04-28 Procédé pour l'opération d'une prothèse auditive aussi qu'une prothèse auditive avec un système de microphone dans lequel des diagrammes de rayonnement différents sont sélectionnables.

Country Status (3)

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US (1) US20040258249A1 (fr)
EP (1) EP1489882A3 (fr)
AU (1) AU2004202682B2 (fr)

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DE102008023370A1 (de) * 2008-05-13 2009-11-19 Siemens Medical Instruments Pte. Ltd. Verfahren zum Betreiben eines Hörgeräts und Hörgerät
EP2230860A1 (fr) * 2009-03-19 2010-09-22 Siemens Medical Instruments Pte. Ltd. Procédé de réglage d'une caractéristique de guidage d'un dispositif auditif
EP2373065A1 (fr) 2010-03-17 2011-10-05 Siemens Medical Instruments Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
EP2169984A3 (fr) * 2008-09-26 2012-05-30 Siemens Medical Instruments Pte. Ltd. Prothèse auditive avec système de microphone directif et procédé de fonctionnement d'une telle prothèse auditive
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DE102008023370A1 (de) * 2008-05-13 2009-11-19 Siemens Medical Instruments Pte. Ltd. Verfahren zum Betreiben eines Hörgeräts und Hörgerät
EP2120484A3 (fr) * 2008-05-13 2010-05-26 Siemens Medical Instruments Pte. Ltd. Procédé destiné au fonctionnement d'un appareil auditif et appareil auditif
US8737652B2 (en) 2008-05-13 2014-05-27 Siemens Medical Instruments Pte. Ltd. Method for operating a hearing device and hearing device with selectively adjusted signal weighing values
DE102008023370B4 (de) * 2008-05-13 2013-08-01 Siemens Medical Instruments Pte. Ltd. Verfahren zum Betreiben eines Hörgeräts und Hörgerät
EP2169984A3 (fr) * 2008-09-26 2012-05-30 Siemens Medical Instruments Pte. Ltd. Prothèse auditive avec système de microphone directif et procédé de fonctionnement d'une telle prothèse auditive
EP2230860A1 (fr) * 2009-03-19 2010-09-22 Siemens Medical Instruments Pte. Ltd. Procédé de réglage d'une caractéristique de guidage d'un dispositif auditif
DE102009014053A1 (de) * 2009-03-19 2010-09-30 Siemens Medical Instruments Pte. Ltd. Verfahren zum Einstellen einer Richtcharakteristik und Hörvorrichtung
DE102009014053B4 (de) * 2009-03-19 2012-11-22 Siemens Medical Instruments Pte. Ltd. Verfahren zum Einstellen einer Richtcharakteristik und Hörvorrichtungen
US8477974B2 (en) 2010-03-17 2013-07-02 Siemens Medical Instruments Pte. Ltd. Hearing device and method for producing an omnidirectional directional characteristic
DE102010011730A1 (de) * 2010-03-17 2011-11-17 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung und Verfahren zum Erzeugen einer omnidirektionalen Richtcharakteristik
EP2373065A1 (fr) 2010-03-17 2011-10-05 Siemens Medical Instruments Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
EP2373065B1 (fr) 2010-03-17 2016-01-13 Sivantos Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
EP2373065B2 (fr) † 2010-03-17 2018-10-03 Sivantos Pte. Ltd. Dispositif auditif et procédé de production d'une caractéristique de direction omnidirectionnelle
CN107396270A (zh) * 2016-04-10 2017-11-24 奥迪康有限公司 用于听力装置的无失真滤波器组
CN107396270B (zh) * 2016-04-10 2021-01-19 奥迪康有限公司 用于听力装置的无失真滤波器组
WO2018129086A1 (fr) * 2017-01-03 2018-07-12 Dolby Laboratories Licensing Corporation Mise à niveau sonore dans un système de capture sonore multicanal
US10701483B2 (en) 2017-01-03 2020-06-30 Dolby Laboratories Licensing Corporation Sound leveling in multi-channel sound capture system

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EP1489882A3 (fr) 2009-07-29
AU2004202682A1 (en) 2005-01-13
US20040258249A1 (en) 2004-12-23
AU2004202682B2 (en) 2007-01-11

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