EP0676909A1 - Prothèse auditive programmable - Google Patents
Prothèse auditive programmable Download PDFInfo
- Publication number
- EP0676909A1 EP0676909A1 EP94105192A EP94105192A EP0676909A1 EP 0676909 A1 EP0676909 A1 EP 0676909A1 EP 94105192 A EP94105192 A EP 94105192A EP 94105192 A EP94105192 A EP 94105192A EP 0676909 A1 EP0676909 A1 EP 0676909A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- hearing aid
- aid according
- hearing
- memory
- voltage
- 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- Withdrawn
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Classifications
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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
- H04R25/35—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
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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
- H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
- H04R2460/03—Aspects of the reduction of energy consumption in hearing devices
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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
- H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
- H04R25/502—Customised settings for obtaining desired overall acoustical characteristics using analog signal processing
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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
- H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
- H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
Definitions
- the invention relates to a programmable hearing aid, with an analog part for sound signal processing, comprising a microphone, a preamplifier, means for automatic gain control, filter means, means for gain adjustment, a Class-D power amplifier stage and a receiver, and with a digital part consisting of a serial interface and a Storage part and with a supply part to generate the required voltages and control signals.
- the invention has for its object to provide a hearing aid of this type, which is characterized in particular by a comprehensive functionality, versatile adaptability and low power consumption in a small size.
- this is achieved in a programmable hearing aid of the type mentioned at the outset in that the preamplifier has at least two separate inputs, the signals of the inputs being able to be amplified individually or together, amplifying means being provided in the signal inputs and the amplification of the amplifying means being selectable or programmable is.
- the amplifier circuit for a hearing aid which is designed as an integrated circuit 41 or a single IC, comprises an analog part 1, a digital part 9 and a supply part 12.
- the hearing aid is supplemented by a microphone 2 and a receiver 8 and by a battery or Voltage source 35.
- a serial interface 10 a telephone or induction coil 19 and a switch 40, for example, are also provided in the hearing aid a switching means for switching the hearing aid from microphone to telephone coil operation (MT switch) or a so-called MTO switch (for switching the hearing aid to microphone operation, for switching to telephone operation / induction coil operation and for switching off the hearing aid / O position) is provided.
- MT switch telephone coil operation
- MTO switch for switching the hearing aid to microphone operation, for switching to telephone operation / induction coil operation and for switching off the hearing aid / O position
- the hearing aid function block shown in the exemplary embodiment according to FIG. 2, namely the analog part 1, is characterized by a preamplifier 3, means for automatic gain control 4, filter means 5, means for gain adjustment 6 and a class D power amplifier stage 7.
- the preamplifier 3 in particular two separate inputs 13, 14 are provided.
- the signal input 13 is assigned to the microphone 2 and the signal input 14 is assigned to the telephone coil 19.
- a further signal input could also be provided as an audio input. It is possible to amplify the signals of the inputs 13, 14 individually or together.
- the signal inputs 13, 14 are associated with amplifying means 15 and 16, respectively, and a summing circuit with summing point 17 and downstream amplifying means 18 is provided so that the signal inputs are superimposed and can be amplified together.
- the preamplifier with a separate preamplifier part is followed by a means 4 for automatic gain control, which comprises at least one adjustable compression circuit 20 for syllable compression and / or for automatic volume control, e.g. with a decay time of more than 10 seconds.
- An automatic gain control AGC which responds to an input signal from a certain signal level can be provided.
- the means for automatic gain control 4 are adjustable with regard to compression ratio and / or settling / decay time. For example, the settling / decay time can be influenced by changing the charging current of a capacitor that determines the time constant.
- the filter means 5 of the analog part 1 form a filter stage consisting of high-pass filters 21, 22, which are provided for the simulation / generation of different microphone frequency responses. It is also possible to implement frequency responses that do not occur with conventional microphones.
- the filter stage implemented in SC technology enables the use of a simple standard microphone 2 and can simulate or generate different microphone characteristics.
- further filters 23, 24 are designed, which are provided for lowering or lowering and forming an NH or NL sound screen.
- the filter means 5 of the analog part 1 further includes an anti-aliasing filter 25 at the entrance and a smoothing filter 26 at the exit.
- the means 6 for gain adjustment adjoining the signal path comprise an amplification stage / gain control 27 which can be programmed by the manufacturer for a hearing aid-specific basic adjustment of the maximum gain.
- additional setting means can be provided which the hearing care professional can use when adapting the hearing aid to the hearing damage of the hearing aid wearer enable the acoustician to further reduce the maximum gain specified by the manufacturer.
- Such setting means can also be replaced by the software of a programming device that can be used to adapt the hearing aid.
- An additional peak clipping block 29 limits the input signal symmetrically according to the programmed PC level and thus serves to limit the maximum output power.
- a filter 30 (anti-heterodyne filter) is arranged in the signal path in front of the energy-saving class D output stage in order to avoid distortions of the class D output stage 7 and to limit the band of the input signal.
- the analog part 1 is also designed so that its functional blocks are switched by switching means, e.g. Analog switches, are only activated as far as they are required for the special hearing aid type or for the special hearing damage or for a special selected operating mode, i.e. Function blocks of the analog part that are not required can be bridged and switched off by switching means. The ineffective function blocks do not require any energy and the hearing aid is operated in a battery-saving manner.
- switching means e.g. Analog switches
- the hearing aid is programmed via the serial interface 10, with programming data being able to be stored in one or more memories of the memory part 11 of the digital part 9. Based on this programming data, the digital part 9 acts as a control part on the analog part 1, it also providing adjustment values for the supply part 12.
- the memory part 11 comprises at least one non-volatile memory (EEPROM), part of the memory being provided for the adjustment values or calibration values which Ensure compliance with the hearing aid data in accordance with the data sheet, a second part of the memory being provided for basic settings, which contain values for the permissible maximum gain setting (peak clipping) or the like, for example, and a third part of the memory for storing parameters or parameter sets for different hearing situations in adaptation to hearing damage is provided.
- EEPROM non-volatile memory
- the digital part 9 of the hearing device circuit 41 thus also contains a data memory 31, in which readable data relating to the manufacturer, the hearing device type, the circuit type used or the like can be stored. In order to protect certain programming data from undesired changes, special protection means / programming locks can be assigned to the data memory 31.
- the MTO switch 40 is not arranged in the battery circuit as usual, but rather gives digital information about the desired hearing aid operation to the digital part 9, which then triggers the desired circuit.
- a simple MTO switch 40 can be provided which also works less disruptively.
- the cyclical selection of the program data from different stored listening situations is possible.
- the hearing device circuit 41 finally comprises the supply part 12.
- the supply part 12 supplies the programming voltage of approximately 15 V required for programming the memory part 11, which is generated from the battery voltage by means of so-called charge pumps (a cascade of voltage doublers 32). Furthermore, the supply part 12 supplies a supply voltage for the analog part 1 which is increased from the battery voltage by approximately 1.3 V.
- the supply voltage for the analog part which is preferably doubled to approximately 2.6 V, is obtained from the battery voltage by means of a capacitive voltage doubler circuit.
- the supply part 12 generates a very low-interference voltage of approximately 1.0 V for supplying the microphone 2. This low-interference voltage is obtained, for example, by means of a filter circuit.
- the supply part 12 uses a clock generator 34 to generate clock signals for the analog part 1, such as for its class D power amplifier stage 7, for the filter means 5 and / or for a voltage doubler 32 or a voltage multiplier 33 of the supply part 12 . Furthermore, the supply part 12 has a unit 36 for the central supply of the analog part 1 with reference currents.
- the hearing aid circuit 41 For simple and low-interference design of the hearing aid circuit 41, it remains connected to the battery 35 with the class-D power amplifier stage 7 of the analog part 1, with the digital part 9 and the supply part 12, even in the switched-off state, but a docoder 37 is provided in the supply part 12, which controls the operating state of the hearing aid circuit. So in the so-called stand by operating state, except for the decoder 37, all functional blocks of the hearing aid circuit can be switched off. Therefore, almost no energy is consumed in this standby mode. In the active operating state, the decoder 37 as a function of input signals 38, 39 the respective operating states are recognized and the functional blocks of the hearing aid circuit corresponding to these operating states are activated.
- the input signals 38, 39 which characterize the operating states of the decoder 37 can be the switching signals of a switching means, for example the MTO switch 40 or a situation key 42 or the control signals of a remote control receiver of the hearing aid, if the hearing aid is a remote-controllable one.
- a switching means for example the MTO switch 40 or a situation key 42 or the control signals of a remote control receiver of the hearing aid, if the hearing aid is a remote-controllable one.
- the switches are not arranged in the battery circuit, can be made simpler and are less disruptive. Since the MTO switch 40 is not arranged in the battery circuit, interference injections to other parts of the hearing aid are reduced.
- switching means for voltage monitoring of the battery 35 are preferably provided. For example, in the event of a voltage drop in the battery in the signal path to the receiver 8, changes in the amplification can be brought about, which serve as a request to change the battery.
- the digital part 9 controls function blocks of the analog part 1, functional blocks which are not required for the selected operating state being switched off and bridged, so that only the current required for the active function blocks is taken from the battery 35.
Landscapes
- 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)
- Control Of Amplification And Gain Control (AREA)
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP94105192A EP0676909A1 (fr) | 1994-03-31 | 1994-03-31 | Prothèse auditive programmable |
US08/407,953 US5710820A (en) | 1994-03-31 | 1995-03-22 | Programmable hearing aid |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP94105192A EP0676909A1 (fr) | 1994-03-31 | 1994-03-31 | Prothèse auditive programmable |
Publications (1)
Publication Number | Publication Date |
---|---|
EP0676909A1 true EP0676909A1 (fr) | 1995-10-11 |
Family
ID=8215832
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP94105192A Withdrawn EP0676909A1 (fr) | 1994-03-31 | 1994-03-31 | Prothèse auditive programmable |
Country Status (2)
Country | Link |
---|---|
US (1) | US5710820A (fr) |
EP (1) | EP0676909A1 (fr) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE19847683A1 (de) * | 1998-10-15 | 2000-06-15 | Siemens Audiologische Technik | Hörhilfegerät |
US6130950A (en) * | 1996-06-26 | 2000-10-10 | Siemans Augiologische Technik Gmbh | Hearing aid which allows non-computerized individual adjustment of signal processing stages |
WO2008049453A1 (fr) * | 2006-09-27 | 2008-05-02 | Oticon A/S | Prothèse auditive avec espace mémoire pour réglages fonctionnels et réglages d'apprentissage, et procédé de programmation de celle-ci |
EP2012557A3 (fr) * | 2007-07-04 | 2011-03-09 | Siemens Medical Instruments Pte. Ltd. | Appareil auditif avec circuit d'activation multi-niveaux et son procédé de fonctionnement |
EP4135345A3 (fr) * | 2021-08-09 | 2023-02-22 | Sivantos Pte. Ltd. | Procédé d'ajustement d'un appareil auditif numérique, appareil auditif et produit programme informatique |
Families Citing this family (61)
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US8085959B2 (en) * | 1994-07-08 | 2011-12-27 | Brigham Young University | Hearing compensation system incorporating signal processing techniques |
US6885752B1 (en) | 1994-07-08 | 2005-04-26 | Brigham Young University | Hearing aid device incorporating signal processing techniques |
DE59609754D1 (de) * | 1996-06-21 | 2002-11-07 | Siemens Audiologische Technik | Programmierbares Hörgerätesystem und Verfahren zum Ermitteln optimaler Parametersätze bei einem Hörhilfegerät |
FR2754663A1 (fr) * | 1996-10-10 | 1998-04-17 | Philips Electronics Nv | Appareil telephonique muni de moyens de controle automatique de gain |
US6449662B1 (en) * | 1997-01-13 | 2002-09-10 | Micro Ear Technology, Inc. | System for programming hearing aids |
US6424722B1 (en) * | 1997-01-13 | 2002-07-23 | Micro Ear Technology, Inc. | Portable system for programming hearing aids |
US7787647B2 (en) * | 1997-01-13 | 2010-08-31 | Micro Ear Technology, Inc. | Portable system for programming hearing aids |
US6028944A (en) * | 1997-03-04 | 2000-02-22 | Compaq Computer Corporation | Signal processing apparatus with selective power amplification |
US6366863B1 (en) * | 1998-01-09 | 2002-04-02 | Micro Ear Technology Inc. | Portable hearing-related analysis system |
CA2337250C (fr) * | 1999-01-25 | 2007-04-03 | Topholm & Westermann Aps | Systeme de correction auditive et appareil de correction auditive destine a etre assemble in situ |
US7010136B1 (en) * | 1999-02-17 | 2006-03-07 | Micro Ear Technology, Inc. | Resonant response matching circuit for hearing aid |
US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
US6480610B1 (en) * | 1999-09-21 | 2002-11-12 | Sonic Innovations, Inc. | Subband acoustic feedback cancellation in hearing aids |
US6694034B2 (en) * | 2000-01-07 | 2004-02-17 | Etymotic Research, Inc. | Transmission detection and switch system for hearing improvement applications |
US6757395B1 (en) | 2000-01-12 | 2004-06-29 | Sonic Innovations, Inc. | Noise reduction apparatus and method |
EP1252799B2 (fr) | 2000-01-20 | 2022-11-02 | Starkey Laboratories, Inc. | Procédé et appareil pour l'adaptation des prothèses auditives |
US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
US20020015506A1 (en) * | 2000-03-13 | 2002-02-07 | Songbird Hearing, Inc. | Remote programming and control means for a hearing aid |
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US6937738B2 (en) | 2001-04-12 | 2005-08-30 | Gennum Corporation | Digital hearing aid system |
DE60223869D1 (de) * | 2001-04-18 | 2008-01-17 | Gennum Corp | Digitaler Quasi-Mittelwertdetektor |
EP1251715B2 (fr) * | 2001-04-18 | 2010-12-01 | Sound Design Technologies Ltd. | Prothèse auditive multicanaux avec communication entre les canaux |
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EP1472786A2 (fr) * | 2002-01-24 | 2004-11-03 | Koninklijke Philips Electronics N.V. | Technique permettant de reduire la plage dynamique d'un signal et circuit electronique a cet effet |
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DE10211364B4 (de) * | 2002-03-14 | 2004-02-05 | Siemens Audiologische Technik Gmbh | Abschalten von Signalverarbeitungsvorrichtungen eines Hörgeräts |
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US7602928B2 (en) † | 2002-07-01 | 2009-10-13 | Avaya Inc. | Telephone with integrated hearing aid |
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US8284970B2 (en) | 2002-09-16 | 2012-10-09 | Starkey Laboratories Inc. | Switching structures for hearing aid |
US7369671B2 (en) * | 2002-09-16 | 2008-05-06 | Starkey, Laboratories, Inc. | Switching structures for hearing aid |
EP1680781B1 (fr) * | 2003-07-07 | 2007-03-07 | Koninklijke Philips Electronics N.V. | Systeme et procede pour le traitement des signaux audio |
US7324652B2 (en) * | 2003-12-30 | 2008-01-29 | Starkey Laboratories, Inc. | Hearing aid having a supply source providing multiple supply voltages |
US7826627B2 (en) * | 2005-02-25 | 2010-11-02 | Wms Gaming, Inc. | Wagering game with user volume control |
DE102005019149B3 (de) * | 2005-04-25 | 2006-08-31 | Siemens Audiologische Technik Gmbh | Hörhilfevorrichtung mit Kompensation von akustischen und elektromagnetischen Rückkopplungssignalen |
US8041066B2 (en) | 2007-01-03 | 2011-10-18 | Starkey Laboratories, Inc. | Wireless system for hearing communication devices providing wireless stereo reception modes |
US9774961B2 (en) | 2005-06-05 | 2017-09-26 | Starkey Laboratories, Inc. | Hearing assistance device ear-to-ear communication using an intermediate device |
WO2007045253A1 (fr) * | 2005-10-17 | 2007-04-26 | Widex A/S | Aide auditive a programmes selectionnables, et procede de modification de programme dans une aide auditive |
US8208642B2 (en) | 2006-07-10 | 2012-06-26 | Starkey Laboratories, Inc. | Method and apparatus for a binaural hearing assistance system using monaural audio signals |
CA2601662A1 (fr) | 2006-09-18 | 2008-03-18 | Matthias Mullenborn | Interface sans fil pour programmer des dispositifs d'aide auditive |
EP1995992A3 (fr) * | 2007-05-24 | 2009-12-02 | Starkey Laboratories, Inc. | Prothèse auditive avec commutateur capacitif |
US20090074203A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Method of enhancing sound for hearing impaired individuals |
US20090074216A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Assistive listening system with programmable hearing aid and wireless handheld programmable digital signal processing device |
US20090076825A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Method of enhancing sound for hearing impaired individuals |
US20090074206A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Method of enhancing sound for hearing impaired individuals |
US20090076816A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Assistive listening system with display and selective visual indicators for sound sources |
US20090076804A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Assistive listening system with memory buffer for instant replay and speech to text conversion |
US20090076636A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Method of enhancing sound for hearing impaired individuals |
US20090074214A1 (en) * | 2007-09-13 | 2009-03-19 | Bionica Corporation | Assistive listening system with plug in enhancement platform and communication port to download user preferred processing algorithms |
US8391522B2 (en) * | 2007-10-16 | 2013-03-05 | Phonak Ag | Method and system for wireless hearing assistance |
US9635477B2 (en) * | 2008-06-23 | 2017-04-25 | Zounds Hearing, Inc. | Hearing aid with capacitive switch |
US20110091058A1 (en) * | 2009-10-16 | 2011-04-21 | Starkey Laboratories, Inc. | Method and apparatus for in-the-ear hearing aid with capacitive sensor |
US8824712B2 (en) | 2009-10-17 | 2014-09-02 | Starkey Laboratories, Inc. | Method and apparatus for behind-the-ear hearing aid with capacitive sensor |
DK2352312T3 (da) * | 2009-12-03 | 2013-10-21 | Oticon As | Fremgangsmåde til dynamisk undertrykkelse af omgivende akustisk støj, når der lyttes til elektriske input |
US9420385B2 (en) | 2009-12-21 | 2016-08-16 | Starkey Laboratories, Inc. | Low power intermittent messaging for hearing assistance devices |
US10003379B2 (en) | 2014-05-06 | 2018-06-19 | Starkey Laboratories, Inc. | Wireless communication with probing bandwidth |
US11070929B2 (en) * | 2018-04-03 | 2021-07-20 | Georgia Tech Research Corporation | Low-cost hearing aid platforms and methods of use |
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1994
- 1994-03-31 EP EP94105192A patent/EP0676909A1/fr not_active Withdrawn
-
1995
- 1995-03-22 US US08/407,953 patent/US5710820A/en not_active Expired - Lifetime
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Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6130950A (en) * | 1996-06-26 | 2000-10-10 | Siemans Augiologische Technik Gmbh | Hearing aid which allows non-computerized individual adjustment of signal processing stages |
DE19625639C2 (de) * | 1996-06-26 | 2002-07-18 | Siemens Audiologische Technik | Hörgerät |
DE19847683A1 (de) * | 1998-10-15 | 2000-06-15 | Siemens Audiologische Technik | Hörhilfegerät |
DE19847683B4 (de) * | 1998-10-15 | 2005-09-29 | Siemens Audiologische Technik Gmbh | Hörhilfegerät |
WO2008049453A1 (fr) * | 2006-09-27 | 2008-05-02 | Oticon A/S | Prothèse auditive avec espace mémoire pour réglages fonctionnels et réglages d'apprentissage, et procédé de programmation de celle-ci |
AU2006349527B2 (en) * | 2006-09-27 | 2011-03-10 | Oticon A/S | Hearing aid with memory space for functional settings and learned settings, and programming method thereof |
EP2012557A3 (fr) * | 2007-07-04 | 2011-03-09 | Siemens Medical Instruments Pte. Ltd. | Appareil auditif avec circuit d'activation multi-niveaux et son procédé de fonctionnement |
US8126174B2 (en) | 2007-07-04 | 2012-02-28 | Siemens Medical Instruments Pte. Ltd | Hearing device with a multi-stage activation circuit and method for operating it |
EP4135345A3 (fr) * | 2021-08-09 | 2023-02-22 | Sivantos Pte. Ltd. | Procédé d'ajustement d'un appareil auditif numérique, appareil auditif et produit programme informatique |
Also Published As
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US5710820A (en) | 1998-01-20 |
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