EP1389035A2 - Prothèse auditive programmable sans fils - Google Patents

Prothèse auditive programmable sans fils Download PDF

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Publication number
EP1389035A2
EP1389035A2 EP03017093A EP03017093A EP1389035A2 EP 1389035 A2 EP1389035 A2 EP 1389035A2 EP 03017093 A EP03017093 A EP 03017093A EP 03017093 A EP03017093 A EP 03017093A EP 1389035 A2 EP1389035 A2 EP 1389035A2
Authority
EP
European Patent Office
Prior art keywords
hearing aid
coil
programming
coil structure
transponder
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Withdrawn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
EP03017093A
Other languages
German (de)
English (en)
Other versions
EP1389035A3 (fr
Inventor
Torsten Dr. Niederdränk
Gottfried Rückerl
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 EP1389035A2 publication Critical patent/EP1389035A2/fr
Publication of EP1389035A3 publication Critical patent/EP1389035A3/fr
Withdrawn legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/27—Adaptation for use in or on movable bodies
    • H01Q1/273—Adaptation for carrying or wearing by persons or animals
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q7/00—Loop antennas with a substantially uniform current distribution around the loop and having a directional radiation pattern in a plane perpendicular to the plane of the loop
    • 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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • 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
    • H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids

Definitions

  • the invention relates to a hearing aid with a chip and with a coil for wireless transmission of electromagnetic Signals between the hearing aid and an external one Sending and / or receiving unit.
  • a programmable hearing aid enables an optimal Hearing aid function adapted to the wearer's hearing loss and versatile use of the hearing aid in various environments. Programming the hearing aid is advantageously carried out when worn. This requires a programming interface on the hearing aid, which is easily accessible and a programming device, its influence on the acoustics during the adjustment of the hearing aid is as low as possible. Wirelessly programmable Hearing aids offer such an interface, usually on a pair of transmitting and / or receiving units in the hearing aid and in the programming device.
  • EP 0 448 764 B1 is a wirelessly programmable electrical Hearing aid known, in which there is a transmission and / or Receiver unit in the hearing aid and in the programming device located.
  • the programming signals are transmitted with electromagnetic signals with a coil the transmitter and / or receiver unit of the programming device and with a coil of the transmitting and / or receiving unit of the hearing aid are received.
  • the response signals of the Hearing aids are in the same way only in a different direction transfer.
  • To optimize bidirectional data transmission can the two coils spatially with maximum Flooding of the generated electromagnetic fields the coils are arranged.
  • the difficulty now is the sending and / or receiving unit to accommodate in the hearing aid because the Components of the transmitting and / or receiving unit, for example Antenna and battery, take up a lot of space.
  • a hearing aid which has an ear piece and has a remote processor unit (RPU).
  • RPU remote processor unit
  • the earpiece includes a transponder to to receive the amplified signals from the RPU and to the speaker forward.
  • EP 0706732 is a short range wireless communication system known for transmitting an audio frequency input signal.
  • One is made using thick film technology Transfer loop attached to a printed circuit board
  • the invention has for its object to build a to simplify wirelessly programmable hearing aids and to enable a more compact design.
  • the chip can be made of a silicon substrate, for example be built in and / or on which one or more Semiconductor levels and / or conductor tracks are located. This Semiconductor levels and / or traces are as follows referred to as the coating level of the chip.
  • the integrated coil structure has the advantage that it is almost takes up no additional space in the hearing aid and thus enables a very compact structure of the hearing aid.
  • the use of a realized in this way wireless transmission route thus avoids the disadvantage of one Hearing aid according to the prior art, in which the transmitting and / or Receiver unit for wireless transmission in Generally occupies essential space in the hearing aid.
  • Adverse effects of the generally short range of wireless exchange using an integrated There is a coil structure when used in the hearing aid not because the coil of the external transmitter and / or receiver unit can be brought close to the hearing aid. Also for the integrated coil structure is advantageous for the manufacturing process, because it allows a simpler structure.
  • the programming of a hearing aid according to the invention with the delivery parameters is simplified and accelerated, as compared to a mobile transceiver module according to DE 195 41 648 A1 the establishment of a connection with the hearing aid is omitted. In addition, protection from a Damage due to external influences improved.
  • wireless transmission path are in the already mentioned Programming and transmission of control data as well as in the Transmission of original or compressed audio data.
  • the coil is an antenna of a Transponder.
  • the transponder can also be integrated in the chip his.
  • the antenna of the transponder is, for example designed as a coil structure, which is also in the Chip is integrated. This way it is a very compact one Transponder structure implemented.
  • the transponder is used for receiving and sending data on slightly shifted frequency bands.
  • the transponder enables energy to gain from an irradiated electromagnetic field.
  • the hearing aid device comprises a programmable one Signal processing unit, in the example the hearing aid parameters are processed by the hearing aid adapt to the user's hearing loss.
  • the Signal processing unit can include other parameters such as a Identification code or parameters for the different Functional modes of the hearing aid can be stored.
  • the coil structure is preferably connected to the programmable signal processing unit of the hearing aid and thus forms a programming interface which enables wireless transmission, for example, of the parameters mentioned above between the external transmitting and / or receiving unit and the hearing aid.
  • a further preferred embodiment of the external transmitting and / or receiving unit comprises a coil made of an electrical conductor, which during the programming is advantageously spatially oriented in such a way that the generated electromagnetic fields maximally flow through the coil structure of the hearing aid chip.
  • the external one Sending and / or receiving unit with a device for Programming the signal processing unit connected with for example a hearing care professional the hearing aid can adapt to the respective hearing damage.
  • the coil structure is for bidirectional transmission, i.e. as broadcast and formed as a receiving coil, so that both signals of external transmitting and / or receiving unit from the hearing aid can be received as well as response signals that e.g. confirm successful programming to the external Sending and / or receiving unit are returned can.
  • the integrated coil structure can be part of a Transponder system. This has the advantage that the coil structure is made for contactless energy generation can serve the incident electromagnetic field. there supplies the external sending and / or receiving unit Transponder system over the electromagnetic field continuously with energy based on the principle of inductive coupling. The energy can then be used to program the signal processing unit or used for sending response signals become. The battery of the hearing aid is thus during the Programming only slightly loaded.
  • the energy supply can come from the external electromagnetic field based on the principle of inductive Coupling take place.
  • the coil structure is integrated in the form of a spiral in the circuit board or the chip. This has the advantage that the structure can be carried out in one coating level. In a further embodiment, the coil structure runs within several coating levels. This has the advantage that only very little space is required in each coating level.
  • the external transmission and / or Receiver unit Part of a device for transmission of acoustic signals, with electromagnetic fields of the external transmitter and / or receiver unit and are received by the coil structure in the hearing aid.
  • This embodiment also has the advantage that the coil structure in the hearing aid as a receiving coil of electromagnetic Can serve fields that e.g. of speaker coils, such as from a coil in the handset become.
  • the invention can be used with all known hearing aid types can be used, for example, behind the ear wearable Hearing aids, hearing aids portable in the ear, implantable hearing aids, hearing aid systems or Taschenbuchakun.
  • FIG. 1 gives an overview of the wireless programming of a hearing aid 1.
  • the hearing-impaired person wears a hearing aid 1 with a coil 5 in the ear 3.
  • a transmitting and receiving unit 7 with a programming coil 11 connected via a line 9 is used to program the hearing aid 1.
  • the transmitting and receiving unit 7 is part of a programming device 13.
  • the programming coil 11 is attached to the head 17 of the hearing aid wearer with the aid of a holding bracket 15.
  • the programming device 13 sends a programming signal to the programming coil 11, which is converted there into an electromagnetic signal.
  • the electromagnetic signal induces a voltage in the coil 5 of the hearing aid 1, which is used to program the hearing aid 1.
  • the programming coil 11 hardly influences the acoustics in the vicinity of the hearing aid 1 worn in the ear 3.
  • FIG. 2 shows a first embodiment of a hearing aid device 18 according to the invention. It comprises a battery 19 and a microphone arrangement 21 and a loudspeaker 23.
  • the acoustic signals recorded with the microphone arrangement 21 are processed with the aid of signal processing 25 in accordance with the respective hearing damage and are forwarded to the hearing impaired person via the loudspeaker 23.
  • the signal processing 25 is located on a circuit board 27.
  • a coil structure 29 in the form of a spiral is integrated in a coating plane of the circuit board 27.
  • the coil structure 29 receives an electromagnetic signal emitted by a programming coil 11, converts it inductively into an electronic signal and then forwards it to the signal processor 25, which is programmed by means of the electronic signals.
  • Electronic response signals from the signal processing 25 to the programming device 13 are likewise converted into electromagnetic signals via the coil structure 29 and transmitted to the programming coil 11.
  • the energy required for programming is largely covered by the energy obtained inductively via the coil structure 29, and only a small part of the energy required is taken from the hearing aid battery 19.
  • FIG. 3 shows a chip 31 of a hearing aid according to the invention shown with an integrated coil structure 29.
  • Several coating levels are located on the chip substrate 33 34, which are shown here greatly enlarged.
  • the coil structure is three-dimensional integrated.
  • the coil structure can also in be integrated into this hybrid.
  • the integration is in the chip or the circuit board of the hybrid possible. This can be done also on the integration of a transponder into one Transmit hybrids.
  • FIG. 4 shows an embodiment of a hearing aid worn in the ear 35 with a transponder 36, which is in a chip 31 of the hearing aid 35 is integrated.
  • a transponder 36 which is in a chip 31 of the hearing aid 35 is integrated.
  • the transponder 36 is a signal processing 25 of the hearing aid 35 in the same chip integrated.
  • There is no modification for programming of the hearing aid for example the connection an additional battery, necessary, and the acoustics will during programming is not restricted. How it works of the transponder 36 is described below.
  • FIG. 5 is a block diagram of the operation of a Transponders 36 shown.
  • Programming signals 37 cause programming one or more memory elements 39, either directly in the transponder 36 or in the signal processing 25 are installed.
  • One or more response signals 41 are sent back from the transponder 36 to the programming device 13.
  • the data exchange, the operation of the Transponders 36 and for writing and reading memory elements 39 necessary energy becomes from the incident electromagnetic Alternating field won, which in the coil 5 of Transponders 36 builds up a voltage which acts as a power supply is used and an additional battery for programming makes redundant.
  • FIG. 6 shows the use of the coil structure 29 in one Hearing aid 1 for receiving electromagnetic signals shown by a modified telephone coil 47 a Telephone receiver 49 are emitted.
  • the conversion of electronic signals in acoustic signals in the speaker takes place with the help of the telephone coil 47.
  • the control of the Telephone coil 47 and the telephone coil 47 itself are of this type modified that at the same time with the acoustic signals leading fields also emit electromagnetic fields are received with the help of the coil structure 29 and a subsequent one that takes hearing damage into account
  • Signal processing 25 again in the loudspeaker 23 of the hearing aid 1 can be converted into acoustic signals.
  • the telephone coil 47 can be caused by high-frequency Signals are driven, the acoustic data contained in modulated form.
  • the modulated high-frequency Signals are then integrated, for example Coil structure 29 or an integrated transponder 36 in Hearing aid 1 received.
  • audio data transmission is an interesting area of application.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Near-Field Transmission Systems (AREA)
EP03017093A 2002-08-08 2003-07-28 Prothèse auditive programmable sans fils Withdrawn EP1389035A3 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10236469A DE10236469B3 (de) 2002-08-08 2002-08-08 Drahtlos programmierbares Hörhilfsgerät
DE10236469 2002-08-08

Publications (2)

Publication Number Publication Date
EP1389035A2 true EP1389035A2 (fr) 2004-02-11
EP1389035A3 EP1389035A3 (fr) 2008-02-13

Family

ID=30128783

Family Applications (1)

Application Number Title Priority Date Filing Date
EP03017093A Withdrawn EP1389035A3 (fr) 2002-08-08 2003-07-28 Prothèse auditive programmable sans fils

Country Status (3)

Country Link
US (1) US20080095387A1 (fr)
EP (1) EP1389035A3 (fr)
DE (1) DE10236469B3 (fr)

Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005081583A1 (fr) 2004-02-19 2005-09-01 Oticon A/S Appareil auditif equipe d'une antenne destinee a l'emission et a la reception de signaux electromagnetiques
EP1587343A2 (fr) * 2004-04-13 2005-10-19 Siemens Audiologische Technik GmbH Prothèse auditive
WO2006089666A1 (fr) * 2005-02-22 2006-08-31 Siemens Audiologische Technik Gmbh Antenne helicoidale double
EP1708306A1 (fr) * 2005-03-28 2006-10-04 Starkey Laboratories, Inc. Antennes pour prothèses auditives
EP1821571A1 (fr) * 2006-02-15 2007-08-22 Oticon A/S Antenne à boucle pour dispositif d'écouteur intra-auriculaire
DE102006035011A1 (de) * 2006-07-28 2008-01-31 Siemens Audiologische Technik Gmbh Programmiersystem für eine Hörhilfe und Verfahren
EP1933592A1 (fr) 2006-12-11 2008-06-18 Siemens Audiologische Technik GmbH Dispositif auditif auto-programmable et procédé correspondant
EP1933594A1 (fr) 2006-12-11 2008-06-18 Siemens Audiologische Technik GmbH Dispositif auditif doté d'une détection de transpondeur et procédé de commande correspondant
DE102006061176A1 (de) * 2006-12-22 2008-07-03 Siemens Audiologische Technik Gmbh Verfahren zum Einstellen eines Hörgeräts mit Ergänzungsparametern
EP2053878A2 (fr) * 2007-10-26 2009-04-29 Siemens Medical Instruments Pte. Ltd. Dispositif d'écoute en utilisant un régulateur de commutation inductif en tant qu'émetteur radio
US8483416B2 (en) 2006-07-12 2013-07-09 Phonak Ag Methods for manufacturing audible signals
US8494197B2 (en) 2008-12-19 2013-07-23 Starkey Laboratories, Inc. Antennas for custom fit hearing assistance devices
US8565457B2 (en) 2008-12-19 2013-10-22 Starkey Laboratories, Inc. Antennas for standard fit hearing assistance devices
US8605924B2 (en) 2006-12-11 2013-12-10 Siemens Audiologische Technik Gmbh Hearing apparatus including transponder detection and corresponding control method
US8699733B2 (en) 2008-12-19 2014-04-15 Starkey Laboratories, Inc. Parallel antennas for standard fit hearing assistance devices
US8737658B2 (en) 2008-12-19 2014-05-27 Starkey Laboratories, Inc. Three dimensional substrate for hearing assistance devices
US10142747B2 (en) 2008-12-19 2018-11-27 Starkey Laboratories, Inc. Three dimensional substrate for hearing assistance devices
EP3661231A1 (fr) * 2018-11-30 2020-06-03 GN Hearing A/S Dispositif auditif comportant une antenne

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DE10261682B4 (de) * 2002-12-31 2014-07-17 Gabriele Lisa Trinkel System, Verfahren zur kontaktlosen Kommunikation mittels passiver, elektromechanischer Wandler
DE102005041355A1 (de) * 2005-08-31 2007-03-01 Siemens Audiologische Technik Gmbh Hörvorrichtung mit Transpondereinrichtung und entsprechendes Datenübertragungsverfahren
DE102005042327B4 (de) * 2005-09-06 2008-07-10 Siemens Audiologische Technik Gmbh Anpassvorrichtung zum akustischen Anpassen einer Hörvorrichtung
EP2026406A1 (fr) * 2007-08-14 2009-02-18 Oticon A/S Unité d'antenne multifonction
DK2327015T3 (en) * 2008-09-26 2018-12-03 Sonova Ag WIRELESS UPDATE OF HEARING DEVICES
US8363872B2 (en) * 2009-04-14 2013-01-29 Dan Wiggins Magnetic earpiece coupling
US8340335B1 (en) * 2009-08-18 2012-12-25 iHear Medical, Inc. Hearing device with semipermanent canal receiver module
US9432780B2 (en) * 2010-07-03 2016-08-30 Starkey Laboratories, Inc. Multi-mode radio for hearing assistance devices
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US8878735B2 (en) * 2012-06-25 2014-11-04 Gn Resound A/S Antenna system for a wearable computing device
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US10985447B2 (en) 2013-08-02 2021-04-20 Gn Hearing A/S Antenna device
CN106797522B (zh) 2014-08-15 2020-08-07 智听医疗公司 耳道内助听器和无线遥控器使用方法
US9769577B2 (en) 2014-08-22 2017-09-19 iHear Medical, Inc. Hearing device and methods for wireless remote control of an appliance
US20160134742A1 (en) 2014-11-11 2016-05-12 iHear Medical, Inc. Subscription-based wireless service for a canal hearing device
US10165376B2 (en) * 2015-03-31 2018-12-25 Starkey Laboratories, Inc. Non-contact antenna feed
US10051388B2 (en) * 2016-09-21 2018-08-14 Starkey Laboratories, Inc. Radio frequency antenna for an in-the-ear hearing device
DK3471201T3 (da) * 2017-10-16 2021-03-15 Widex As Antenne til en høreunderstøttelsesindretning
DE102018209189A1 (de) * 2018-06-08 2019-12-12 Sivantos Pte. Ltd. Antenne sowie Gerät mit einer solchen Antenne
RU194685U1 (ru) * 2019-08-21 2019-12-19 Общество с ограниченной ответственностью «Аурика Лабс» Формирователь индукционного поля
WO2022038534A1 (fr) * 2020-08-19 2022-02-24 Cochlear Limited Protection de dispositif pouvant être porté avec bobine de communication

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WO1998037639A1 (fr) * 1997-02-20 1998-08-27 Telefonaktiebolaget Lm Ericsson (Publ) Emetteur-recepteur radio sur une puce
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Cited By (52)

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Publication number Priority date Publication date Assignee Title
WO2005081583A1 (fr) 2004-02-19 2005-09-01 Oticon A/S Appareil auditif equipe d'une antenne destinee a l'emission et a la reception de signaux electromagnetiques
US8675902B2 (en) 2004-02-19 2014-03-18 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
US9602933B2 (en) 2004-02-19 2017-03-21 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
CN1934902B (zh) * 2004-02-19 2012-05-30 奥迪康有限公司 具有用于接收和发射电磁信号的天线的助听器
US8995699B2 (en) 2004-02-19 2015-03-31 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
EP2285138A1 (fr) * 2004-02-19 2011-02-16 Oticon A/S Appareil auditif equipé d'une antenne destinée à l'emission et à la reception de signaux électromagnétiques
US7742614B2 (en) 2004-02-19 2010-06-22 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
US10257627B2 (en) 2004-02-19 2019-04-09 Oticon A/S Hearing aid with antenna for reception and transmission of electromagnetic signals
EP1587343A2 (fr) * 2004-04-13 2005-10-19 Siemens Audiologische Technik GmbH Prothèse auditive
EP1587343A3 (fr) * 2004-04-13 2006-01-18 Siemens Audiologische Technik GmbH Prothèse auditive
WO2006089666A1 (fr) * 2005-02-22 2006-08-31 Siemens Audiologische Technik Gmbh Antenne helicoidale double
US7646356B2 (en) 2005-02-22 2010-01-12 Siemens Audiologische Technik Gmbh Double spiral antenna
US8180080B2 (en) 2005-03-28 2012-05-15 Starkey Laboratories, Inc. Antennas for hearing aids
EP1708306A1 (fr) * 2005-03-28 2006-10-04 Starkey Laboratories, Inc. Antennes pour prothèses auditives
US7593538B2 (en) 2005-03-28 2009-09-22 Starkey Laboratories, Inc. Antennas for hearing aids
US9451371B2 (en) 2005-03-28 2016-09-20 Starkey Laboratories, Inc. Antennas for hearing aids
US10194253B2 (en) 2005-03-28 2019-01-29 Starkey Laboratories, Inc. Antennas for hearing aids
US7450078B2 (en) 2006-02-15 2008-11-11 Oticon A/S Loop antenna for in the ear audio device
EP1821571A1 (fr) * 2006-02-15 2007-08-22 Oticon A/S Antenne à boucle pour dispositif d'écouteur intra-auriculaire
US8483416B2 (en) 2006-07-12 2013-07-09 Phonak Ag Methods for manufacturing audible signals
DE102006035011A1 (de) * 2006-07-28 2008-01-31 Siemens Audiologische Technik Gmbh Programmiersystem für eine Hörhilfe und Verfahren
DE102006035011B4 (de) * 2006-07-28 2010-11-25 Siemens Audiologische Technik Gmbh Programmiersystem für eine Hörhilfe und Verfahren
DE102006058317A1 (de) * 2006-12-11 2008-06-19 Siemens Audiologische Technik Gmbh Selbstprogrammierende Hörvorrichtung und entsprechendes Verfahren
DE102006058317B4 (de) * 2006-12-11 2012-07-19 Siemens Audiologische Technik Gmbh Selbstprogrammierendes Hörsystem mit einem Hörgerät und entsprechendes Verfahren
EP1933592A1 (fr) 2006-12-11 2008-06-18 Siemens Audiologische Technik GmbH Dispositif auditif auto-programmable et procédé correspondant
DE102006058318B4 (de) * 2006-12-11 2011-06-16 Siemens Audiologische Technik Gmbh Steuerverfahren für eine Hörvorrichtung mit Transpondererkennung
EP1933594A1 (fr) 2006-12-11 2008-06-18 Siemens Audiologische Technik GmbH Dispositif auditif doté d'une détection de transpondeur et procédé de commande correspondant
DE102006058318A1 (de) * 2006-12-11 2008-06-19 Siemens Audiologische Technik Gmbh Hörvorrichtung mit Transpondererkennung und entsprechendes Steuerverfahren
US8605924B2 (en) 2006-12-11 2013-12-10 Siemens Audiologische Technik Gmbh Hearing apparatus including transponder detection and corresponding control method
US8630432B2 (en) 2006-12-11 2014-01-14 Siemens Audiologische Technik Gmbh Self-programming hearing apparatus and corresponding method
JP2008148317A (ja) * 2006-12-11 2008-06-26 Siemens Audiologische Technik Gmbh 自動プログラミング式聴取装置及びそのプログラミング方法
DE102006061176A1 (de) * 2006-12-22 2008-07-03 Siemens Audiologische Technik Gmbh Verfahren zum Einstellen eines Hörgeräts mit Ergänzungsparametern
EP2053878A3 (fr) * 2007-10-26 2013-03-27 Siemens Medical Instruments Pte. Ltd. Prothèse auditive utilisant un régulateur de commutation inductif en tant qu'émetteur radio
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EP1389035A3 (fr) 2008-02-13
DE10236469B3 (de) 2004-02-12

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