EP2012509B1 - Mehrkomponentiges Hörgerätesystem und ein Verfahren zu seinem Betrieb - Google Patents

Mehrkomponentiges Hörgerätesystem und ein Verfahren zu seinem Betrieb Download PDF

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Publication number
EP2012509B1
EP2012509B1 EP08104397A EP08104397A EP2012509B1 EP 2012509 B1 EP2012509 B1 EP 2012509B1 EP 08104397 A EP08104397 A EP 08104397A EP 08104397 A EP08104397 A EP 08104397A EP 2012509 B1 EP2012509 B1 EP 2012509B1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
interference
aid system
component
operating mode
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.)
Revoked
Application number
EP08104397A
Other languages
German (de)
English (en)
French (fr)
Other versions
EP2012509A1 (de
Inventor
Mihail Boguslavskij
Volker Gebhardt
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 Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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
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First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=39816639&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP2012509(B1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2012509A1 publication Critical patent/EP2012509A1/de
Application granted granted Critical
Publication of EP2012509B1 publication Critical patent/EP2012509B1/de
Revoked 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
    • H04R25/55—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
    • 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
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • 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
    • H04R2225/49—Reducing the effects of electromagnetic noise on the functioning of hearing aids, by, e.g. shielding, signal processing adaptation, selective (de)activation of electronic parts in hearing aid
    • 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
    • H04R25/552—Binaural
    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the invention relates to a multi-component hearing aid system and a method for its operation, in particular for data transmission between components of the hearing aid system.
  • Hearing aids are used primarily to allow hearing-impaired patients the most natural hearing and to compensate in this regard usually medically-related disorders of the hearing organs. They have, like most medical aids, to fulfill this functionality, without causing any other adverse effects for their wearer. Such impairments may result, on the one hand, from an inappropriate weight of the hearing aid or from restrictions of movement associated with the wearing of hearing aids.
  • aesthetic aids play a special role in medical aids that have to be arranged in the area of the face or head. This is particularly true since it is often the aim that the environment of a patient equipped in this way should largely remain hidden from the symptoms compensated by the hearing aid.
  • the DE 10 2004 047 759 B3 describes a hearing aid that is intended to improve the transmission and amplification of a useful signal, especially in difficult, ie interference-prone environment.
  • it is proposed to transmit signals between a first hearing aid device carried by a first hearing aid wearer and a second hearing aid device carried by a second hearing aid wearer.
  • the transmitted signal may include control parameters, sound field characteristics or an audio signal.
  • the signal transmission between the first hearing aid device and the second hearing aid device to be transmitted via at least one further hearing aid device, which is carried by at least one further hearing aid device wearer.
  • the third hearing aid fulfills the function of a relay station.
  • the US 5,083,312 discloses a hearing aid system programmable via dual tone multi-frequency (DTMF) signals.
  • the DTMF signals are fed to the hearing aid system via a microphone.
  • a loudspeaker of the hearing aid system can be muted.
  • the EP 1 715 723 A2 describes a binaural hearing aid system with two components to be arranged on each ear, which are interconnected with each other and with a third component via a wireless communication channel. One of the components provides the other components with a shared time signal.
  • the EP 1 463 246 A1 describes a method for data exchange between two transceiver systems via a radio link.
  • Each of the transceiver systems has a transmitter and a receiver. In the case of unidirectional data transmission, the transmitter of one and the receiver of the other transceiver can be switched off.
  • the EP 1 460 769 B1 describes a portable transceiver for transmitting and receiving audio signals having different priority values.
  • the US 2003/0100280 A1 describes a method and a device for suppressing harmonics in a device for wireless data transmission.
  • Hearing aid systems in the sense of the invention are understood below to mean all multi-component hearing aid systems which comprise at least one component to be arranged on or in the ear of a patient, and which comprise a further component which is at least partially and / or temporarily in a communication connection to be worn at the ear Component stands.
  • This further component may be arranged independently of the patient's ear and / or comprise in binaural systems another component to be arranged on or in the other ear of the patient.
  • hearing aids are included, which can be adapted during individual sessions with a hearing care professional with the aid of a suitable programming device to the personal needs of the respective hearing aid wearer and / or have additional equipment, about which the patient himself or another person can make an adjustment or adjustment of certain parameters on the hearing aid itself independently of the hearing care professional.
  • the wireless connection concept entails that, with the exception of systems that can be powered by inductive couplings, each component of a multi-component hearing aid system must have its own power source.
  • each component of a multi-component hearing aid system must have its own power source.
  • it follows from the requirements initially described that such an energy source must be as small and light as possible, but on the other hand must have sufficient capacity to maintain the functionality of the hearing aid system for an extended period of time without requiring frequent maintenance in the meantime.
  • hearing aid systems are generally designed so that at least the components of the hearing aid system worn directly on or in the ear of the patient are characterized by very low energy consumption. This applies to the maintenance of functionality as a medical device as well as to the realization of communication between individual hearing aid components. Standards for an inductive wireless transmission of data between individual components of multi-component hearing device systems have become established for this communication.
  • essential components of a hearing aid system including additional equipment designed for data reception generate electromagnetic emissions during data transmission which act as sources of interference during data transmission between the individual components in the immediate vicinity of the transmission link, in particular of the respective active receiver, ie in inductive systems in the vicinity each active receiving coil, are located.
  • sources of interference are, for example, the inductances of clocked voltage regulators or also the supply and output lines of virtually all clocked electronic circuits.
  • Such circuits are used for example for controlling displays. Devices with displays represent in this connection overall strong emitters.
  • the hearing device handset itself can be added as a further source of interference.
  • a sufficiently large distance of the receiving coil to acting as sources of interference modules can also not be realized in particular in or in the ear to be worn components of hearing aids. Even with additional devices that are not to be worn in the immediate vicinity of the ear, the trend is to integrate a high functionality in the device with minimal dimensions, so that the volume of the assemblies used and their maximum distance from each other should be kept as small as possible.
  • the receiving coil can in principle be placed in a minimum of the expected interference field.
  • orthogonal alignments of interacting coils and / or interfering fields are known. It is also known to make a local interference field compensation by generating defined opposing fields.
  • the object of the invention is to provide a way to securely exchange data between individual components of a multi-component hearing aid system, without having to accept the disadvantages of the prior art in purchasing.
  • a hearing aid system having the features of claim 1 and by a hearing aid component of a multi-component hearing aid system according to claim 11.
  • Claims 2 to 10 indicate advantageous embodiments of a hearing aid system according to the invention.
  • Claims 12 to 15 indicate advantageous embodiments of a hearing aid component according to the invention.
  • Claim 16 gives a method for operating a hearing aid system according to the invention to, and claims 17 to 21 relate to advantageous embodiments of this method.
  • the invention is essentially based on putting identified sources of interference into an operating mode at least during the transmission of data in which a coupling of interference signals into one or all receivers involved in the data transmission is at least attenuated compared with the normal operating mode of these interference sources.
  • This change in the operation mode of sources of interference may include their momentary shutdown, but may also consist in a change in the operating mode of the identified source of interference in which only the emission characteristics of the source of interference change but the functions of the components acting as sources of interference are preserved during data transmission.
  • Such a change may include reducing the noise power by reducing the power injected into the noise source or changing the noise spectrum, which may be associated with a clock change in clocked devices.
  • Typical methods for wireless, in particular an inductive data transmission between the components of the hearing aid system can be advantageously adapted in accordance with the invention so that the time at which at least one transmitter operates, is known exactly. At this time, at least one interference source is then placed in another operating mode to facilitate the reception of the transmitted signals or the data transmission.
  • a minimal configuration for use of the invention thus comprises a multi-component hearing aid system with at least one first component to be arranged on or in the ear of a patient for generating and / or amplifying a hearing stimulus and at least one further component, at least partially and / or temporarily in a wireless communication connection the data transmission can take place, to be worn on or in the ear component, with circuitry Means are included, which can put at least one interference source contained in the hearing aid at least during the transmission of data in an operating mode in which at least one interference source over the normal operating mode at least attenuated coupling of interference takes place in a participating in the data transmission receiver.
  • the reception situation in a receiving component of the hearing aid system ie, for example, an accessory, can be significantly improved at precisely defined times, without significantly increasing the performance of the individual components during normal operation impair if the change in the operating mode of the sources of interference takes place only in short windows in which occurring deviations from the normal operation of the hearing aid system are imperceptible.
  • means may also be included which at least temporarily compensate for the loss of function of a switched-off source of interference. For example, with switching regulators the bridging of downtime by adequately sized backup capacitors done.
  • the change in the operating mode of the identified sources of interference if necessary their shutdown, during the transmission of data in all components of the hearing aid system, which are located during the existence of the wireless communication link in the vicinity of participating recipients.
  • the shutdown or change of the operating mode of the interference sources in both the receiving component, and in the transmitting component has the advantage that the influence of sources of interference in the transmitting component, at a relatively short distance between the transmitter and receiver in the near field interference or Interference in the receiver of the receiving component can cause, reduce or exclude it. An impairment of the transmission of data with design-related very small distances between the individual components of the hearing aid system is thus prevented.
  • Fig. 1 shows a schematic diagram of a hearing aid system according to the invention, consisting of two components.
  • the two components of the hearing aid system are a hearing aid component 1 for sound pressure amplification to be worn on the ear of a patient, as well as an additional device 2 with which the individual acoustic signal is transmitted Parameters of the hearing aid component to be worn on the ear can be set, as can be done for example by means of a remote control of the patient himself.
  • the additional device may also be a programming device of a hearing device acoustician.
  • a communication for data transmission between the hearing aid component 1 and the auxiliary device 2 is required.
  • the attachment 2 is brought close to the hearing aid component 1 worn on the ear, so that it is within the range of the data transmission means located on the hearing aid component 1.
  • the data transmission takes place wirelessly via an inductive data transmission path.
  • at least one coil 3, 4, which can be used as a transmitter and receiver, is located in the hearing device component 1 to be worn on the ear and in the additional device 2.
  • the hearing aid component 1 to be worn on the ear furthermore comprises a receiver module 5, a control unit 6 and a transmitter module 7.
  • Signals arriving at the receiving coil 3 are first fed to the receiver module 5 where they are processed accordingly and supplied to the control unit 6 in the form of usable output signals.
  • Various forms of signal processing take place in the control unit 6 in order to be able to use the received signals in a meaningful manner for the functionality of the hearing aid system.
  • the control unit 6 has means to change the respective operating mode of individual identified sources of interference 8,9,10.
  • sources of interference in particular clocked electronic components, such as switching regulator or other to harmonic emissions prone components, but also components that are directly part of the acoustic transmission path of the hearing aid, act.
  • the acoustic transmission path comprises a microphone 11, an amplifier 12 and a loudspeaker 13 in the form of a receiver to be placed in the ear.
  • the accessory 2 also includes a receiver assembly 14, a control unit 15, a transmitter assembly 16 and other sources of interference 17, 18, including a display 19.
  • the illustrated hearing aid system is designed so that the time at which the coil 3 in the hearing aid component 1 operates as a transmitter, in the auxiliary device 2 is known exactly.
  • a communication protocol is designed so that the hearing aid component 1 always transmits data only upon request by the auxiliary device 2 and never independently initiates a transmission.
  • the additional device 2 which has a powerful power supply and correspondingly a relatively high transmission power, thus sends to the hearing aid component 1 a request in the form of a request to transmit desired data.
  • the relatively high transmission power of the transmitter module 16 of the auxiliary device 2 guarantees that this request can be reliably identified by the hearing device component 1, even if the interference sources 8,9,10,13 in the hearing aid component 1 and the interference sources 17, 18, 19 in the Attachment 2 are unchanged in operation.
  • the control units 6, 15 cause a change in the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19, in this case, a shutdown.
  • a change in the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19, in this case, a shutdown During the transmission of the data from the hearing aid component 1 to the auxiliary device 2, all sources of interference 8, 9, 10, 13, 17, 18, 19 which are not directly for transmission or reception now remain both in the transmitting hearing device component 1 and in the receiving auxiliary device 2
  • the data needed for the duration of the transmission so for example 50ms, disabled.
  • the hearing aid component 1 responds exclusively to the request by the attachment 2 with the transmission of the requested data. In this way, an event-controlled change of the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19 ensures that interference is reduced during the transmission of data between the components 1, 2 of the hearing aid system.
  • suitable sources of interference instead of a shutdown can also be briefly put into an operating state which is possibly less favorable in terms of energy, ie briefly increases the energy consumption of the battery-operated hearing aid component 1, but in which the spurious emissions lie in a frequency range which is uncritical for the receiver.
  • the quality of the communication connection can be improved by the fact that the interference sources 8, 9, 10, 13, 17, 18, 19 are also placed in a low-noise operating condition when the auxiliary device 2 transmits data to the hearing aid component 1.
  • Fig. 2 shows a schematic diagram of a binaural hearing aid system with inventive data transmission.
  • a binaural hearing aid system has two separate hearing device components 1, 21 for amplifying the sound pressure, which are each arranged on an ear of the hearing device wearer. Between these hearing aid components, a communication for data exchange is also required. This results, on the one hand, from the need for parameter adjustment and various status inquiries, which must be carried out regularly, and, on the other hand, from physical circumstances which, for the realization of certain hearing aid functions, arrange the interaction of at least two spaced-apart ones Require microphones.
  • the communication between such hearing aid components usually has to take place at a much shorter time interval than is the case, for example, for setting parameters by means of external accessories.
  • each of the hearing aid components has only a very small battery with limited capacity.
  • each of the two hearing aid components 1, 21 has the same means for maintaining or establishing a communication connection for data exchange, and the communication protocol required for its operation is likewise symmetrical designed.
  • Each of the hearing aid components 1, 21 has a coil 3, 23, which can be used as transmitter and receiver.
  • Each of the hearing aid components 1, 21 further includes a receiver assembly 5, 25, a control unit 6, 26 and a transmitter assembly 7, 27.
  • the linkage of the individual modules can be made analogous to the previous embodiment.
  • the control units 6, 26 in turn have means to change the respective operating mode of individual identified sources of interference 8, 28, 9, 29, 10, 30.
  • Each hearing aid component 1, 21 further includes an acoustic transmission path with a microphone 11, 31, an amplifier 12, 32 and a speaker 13, 33 as a sound pressure generating output unit.
  • control units 6, 26 additionally have means for generating time information, for example via a timer circuit 20, 40, which transmits a time signal to the control unit 6, 26 at least at regular intervals.
  • a communication connection for transmitting different data can be established at precisely the same time by the two hearing aid components 1, 21, whereby a change of the operating mode is again known in the inventive manner during the duration of the existence of this communication connection
  • Noise sources 8, 28, 9, 29, 10, 30 and 13, 33 takes place, as a result of which these interference sources 8, 28, 9, 29, 10, 30, 13, 33 are in an operating mode in which at least one attenuated coupling-in of interference signals takes place in each participating in the data transfer recipients.
  • the communication between the two hearing aid components 1, 21 can thus be largely free from interference, i. even with low transmission power there is a high transmission reliability of the data to be transmitted.
  • Fig. 3 shows a schematic diagram of a binaural hearing aid system according to the invention with an appropriate for data communication additional device.
  • this hearing device system comprises two separate hearing device components 1, 21, which are each arranged on one ear of the hearing aid wearer, and on the other hand, the illustrated hearing aid system comprises an additional device 2, which can establish a communication connection with one of the hearing aid components 21.
  • the communication connection between the two hearing aid components 1, 21 is cyclically produced time-dependent. A change of the operating mode of identified sources of interference 8, 9, 10, 13, 28, 29, 30, 33 takes place in a correspondingly time-dependent manner.
  • the communication between the additional unit 2 and the hearing aid component 21 is event-controlled by a request-response system, whereby at least the request always occurs from the additional device 2 and transmitted with much higher transmission power. Depending on the event, the request changes the operating mode of the identified interference sources 17, 18, 19, 28, 29, 30, 33.
  • the initiation of a communication connection by a request, which is transmitted with high transmission power, is always useful if the querying component of the hearing aid system, in this case the accessory 2, has sufficient energy reserves and the production of this communication connection is not made regularly and / or very often got to.
  • the time-dependent production of a communication connection with simultaneous change of the operating mode relevant sources of interference is always useful when the production of this communication connection must be very frequent and / or regularly and the emission of a relatively much energy consuming request signal to the energy budget of the communicating hearing aid components 1, 21 too much burden would.
  • the hearing aid component 21 has an additional transmitting and receiving coil 41, via which the communication with the auxiliary device 2 can proceed.
  • the communication with the auxiliary device 2 and the other ear-worn hearing aid component 1 via one and the same coil 23.
  • the hearing device components 1, 21 can be adapted directly to the needs of the hearing device wearer without the need for a parameter transfer via the communication connection existing between the hearing aid components 1, 21.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Signal Processing (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Small-Scale Networks (AREA)
  • Headphones And Earphones (AREA)
  • Stereophonic System (AREA)
  • Noise Elimination (AREA)
  • Selective Calling Equipment (AREA)
  • Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)
  • Mobile Radio Communication Systems (AREA)
EP08104397A 2007-07-02 2008-06-13 Mehrkomponentiges Hörgerätesystem und ein Verfahren zu seinem Betrieb Revoked EP2012509B1 (de)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007030745A DE102007030745A1 (de) 2007-07-02 2007-07-02 Mehrkomponentiges Hörgerätesystem und ein Verfahren zu seinem Betrieb

Publications (2)

Publication Number Publication Date
EP2012509A1 EP2012509A1 (de) 2009-01-07
EP2012509B1 true EP2012509B1 (de) 2010-04-07

Family

ID=39816639

Family Applications (1)

Application Number Title Priority Date Filing Date
EP08104397A Revoked EP2012509B1 (de) 2007-07-02 2008-06-13 Mehrkomponentiges Hörgerätesystem und ein Verfahren zu seinem Betrieb

Country Status (6)

Country Link
EP (1) EP2012509B1 (ja)
JP (1) JP5021577B2 (ja)
AT (1) ATE463935T1 (ja)
AU (1) AU2008202727B2 (ja)
DE (2) DE102007030745A1 (ja)
DK (1) DK2012509T3 (ja)

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009019842B3 (de) 2009-05-04 2010-10-07 Siemens Medical Instruments Pte. Ltd. Anordnung und Verfahren zur drahtlosen Datenübertragung zwischen Hörgeräten
JP4530109B1 (ja) * 2009-05-25 2010-08-25 パナソニック株式会社 補聴器システム
EP2472908A4 (en) 2009-10-13 2013-10-16 Panasonic Corp HEARING PROSTHESIS DEVICE
JP5580946B2 (ja) * 2011-02-28 2014-08-27 ヴェーデクス・アクティーセルスカプ 補聴器および出力段を駆動する方法
DE102012217497A1 (de) 2012-09-26 2014-03-27 Airbus Operations Gmbh Verfahren zum Erkennen eines Störsignale erzeugenden Geräts in einem elektrischen Netz, ein elektrisches System und ein Flugzeug

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JPS6331700U (ja) * 1986-08-14 1988-03-01
US5083312A (en) 1989-08-01 1992-01-21 Argosy Electronics, Inc. Programmable multichannel hearing aid with adaptive filter
JP3049679B2 (ja) * 1993-01-20 2000-06-05 キヤノン株式会社 携帯型電子機器
JPH0683616A (ja) * 1992-09-02 1994-03-25 Mitsubishi Denki Enjiniriangu Kk 半導体集積回路
JPH0715390A (ja) * 1993-06-16 1995-01-17 Hitachi Ltd 無線通信手段を備える情報処理装置
JP2837639B2 (ja) * 1995-03-31 1998-12-16 リオン株式会社 リモートコントローラ
DE10048354A1 (de) * 2000-09-29 2002-05-08 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörgerätesystems sowie Hörgerätesystem
AUPR551301A0 (en) * 2001-06-06 2001-07-12 Cochlear Limited Monitor for auditory prosthesis
US6999723B2 (en) 2001-11-29 2006-02-14 Kyocera Wireless Corp. System and method for reducing the effects of clock harmonic frequencies
DE10304648B3 (de) * 2003-02-05 2004-08-19 Siemens Audiologische Technik Gmbh Vorrichtung und Verfahren zur Kommunikation von Hörgeräten
US7062223B2 (en) * 2003-03-18 2006-06-13 Phonak Communications Ag Mobile transceiver and electronic module for controlling the transceiver
EP1463246A1 (en) 2003-03-27 2004-09-29 Motorola Inc. Communication of conversational data between terminals over a radio link
DE102004047759B3 (de) * 2004-09-30 2006-06-01 Siemens Audiologische Technik Gmbh Verwendung eines Hörhilfegerätesystems mit wenigstens zwei Hörhilfegeräten
JP5024740B2 (ja) * 2004-09-30 2012-09-12 学校法人慶應義塾 Ｌｓｉチップ試験装置
JP2006217063A (ja) * 2005-02-01 2006-08-17 Nec Access Technica Ltd テレビ機能付き移動情報端末およびその制御方法
JP2007088787A (ja) * 2005-09-21 2007-04-05 Sony Ericsson Mobilecommunications Japan Inc 無線通信装置及び不要輻射の低減方法
EP1715723B2 (en) 2006-05-16 2012-12-05 Phonak AG Hearing system with network time

Also Published As

Publication number Publication date
DE502008000514D1 (de) 2010-05-20
AU2008202727A1 (en) 2009-01-22
DE102007030745A1 (de) 2009-01-08
ATE463935T1 (de) 2010-04-15
AU2008202727B2 (en) 2010-07-22
JP5021577B2 (ja) 2012-09-12
JP2009017557A (ja) 2009-01-22
EP2012509A1 (de) 2009-01-07
DK2012509T3 (da) 2010-08-02

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