EP2908557A1 - Détection de configuration d'appareil d'aide auditive - Google Patents

Détection de configuration d'appareil d'aide auditive Download PDF

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Publication number
EP2908557A1
EP2908557A1 EP14155375.0A EP14155375A EP2908557A1 EP 2908557 A1 EP2908557 A1 EP 2908557A1 EP 14155375 A EP14155375 A EP 14155375A EP 2908557 A1 EP2908557 A1 EP 2908557A1
Authority
EP
European Patent Office
Prior art keywords
circuitry
hearing aid
signal
configuration information
line
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.)
Granted
Application number
EP14155375.0A
Other languages
German (de)
English (en)
Other versions
EP2908557B1 (fr
Inventor
Flemming Schmidt
Ebbe Skammelsen
Andreas Schousboe
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.)
GN Hearing AS
Original Assignee
GN Resound AS
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 GN Resound AS filed Critical GN Resound AS
Priority to EP18188194.7A priority Critical patent/EP3422742B1/fr
Priority to EP14155375.0A priority patent/EP2908557B1/fr
Priority to DK14155375.0T priority patent/DK2908557T3/en
Priority to DK18188194.7T priority patent/DK3422742T3/da
Priority to US14/185,632 priority patent/US10051392B2/en
Publication of EP2908557A1 publication Critical patent/EP2908557A1/fr
Application granted granted Critical
Publication of EP2908557B1 publication Critical patent/EP2908557B1/fr
Active legal-status Critical Current
Anticipated expiration legal-status Critical

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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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2420/00—Details of connection covered by H04R, not provided for in its groups
    • H04R2420/05—Detection of connection of loudspeakers or headphones to amplifiers

Definitions

  • the present disclosure relates to a new method for providing configuration information of a hearing aid, a hearing aid adapted to perform the method, and a system for fitting a hearing aid utilizing the configuration information.
  • a BTE hearing aid has a BTE housing that is shaped to be worn behind the pinna of a user.
  • the BTE housing accommodates components for hearing loss compensation.
  • a sound signal transmission member i.e. a sound tube or an electrical conductor, transmits a signal representing the hearing loss compensated sound from the BTE housing into the ear canal of the user.
  • the output transducer may be a receiver positioned in an ear canal of the user of the hearing aid, a so-called R eceiver- I n-the- E ar.
  • a hearing aid with a R eceiver- I n-the- E ar is denoted a RIE hearing aid.
  • the sound signal transmission member comprises electrical conductors for propagation of hearing loss compensated audio sound signals from the hearing aid circuitry in the BTE hearing aid housing through the conductors to the receiver positioned in the ear canal of the user for emission of sound towards the eardrum of the user.
  • an in-the-ear housing, earpiece, shell, or earmould may be provided for insertion into the ear canal of the user.
  • in-the-ear housing earpiece, shell, and earmould are used interchangeably.
  • hearing aid manufacturers provide a number of different earpieces with receivers having different output power specifications, e.g. 5 different output power levels.
  • earpieces are also provided having sound signal transmission members of different lengths, e.g. 8 different lengths, to suit the individual anatomy of the intended user.
  • the earpiece, shell, or earmould may be individually custom manufactured or may be manufactured in a number of standard sizes, which further multiplies the number of earpieces that may be used together with a specific BTE-housing.
  • the earpiece may further accommodate one or more microphones, e.g. a microphone used for suppressing the occlusion effect and/or one or more microphones for recording directional cues further multiplying the number of earpieces that may be used together with a specific BTE-housing.
  • one or more microphones e.g. a microphone used for suppressing the occlusion effect and/or one or more microphones for recording directional cues further multiplying the number of earpieces that may be used together with a specific BTE-housing.
  • the new hearing aid may be configured for adjusting its operation in accordance with the configuration information.
  • the second circuitry with the transmitter may be configured for transmission of the second signal with configuration information to the first circuitry at power up of the hearing aid; and/or upon the hearing aid receiving a user request for transmission of the second signal, from a user interface of the hearing aid; and/or upon the hearing aid receiving a request for transmission of the second signal, from external equipment, such as a fitting instrument.
  • a new method is also provided of identifying a component, or a combination of components, that is connected to a circuit with a connector, comprising transmitting configuration information on the identity of the component, or combination of components, on a line coupled with the connector and provided for transmission of other information than the configuration information.
  • a new method is provided of configuring a hearing aid having a connector that interconnects first circuitry of the hearing aid with second circuitry of the hearing aid, the connector having a line configured to transmit a first signal between the first circuitry and the second circuitry, the method comprising transmitting a second signal containing configuration information relating to the second circuitry to the first circuitry using the line, wherein the first signal does not contain the configuration information.
  • a new fitting instrument for a hearing aid is also provided, which is configured for reception of the configuration information.
  • the new fitting instrument may be configured for fitting the hearing aid in accordance with the configuration information.
  • the new fitting instrument may be configured for displaying a message in response to the configuration information.
  • the new fitting instrument may be a dedicated instrument, or a PC with suitable fitting software, a hand-held device, e.g. a tablet computer, a smartphone, etc., with suitable apps, etc.
  • the dispenser For example, faster and safer initial fitting can be performed by the dispenser due to the automatic identification of component(s), e.g. a receiver type, during the initial fitting of the hearing aid to the intended user, e.g. inadvertently exchanged left and right in-the-ear housings may be automatically detected.
  • component(s) e.g. a receiver type
  • the dispenser is also relieved of the task of manually entering configuration information during fitting, and incorrect gain calibrations and output levels due to erroneously manually entered component information are avoided.
  • a boot process of the hearing aid may be stopped when an undesired combination of components is detected, and/or certain functions of the hearing aid may only be enabled if a combination of components suitable for performing the functions is detected.
  • correct replacement part numbers may be easily identified for the hearing aid in question.
  • a user of the hearing may be warned of an incorrect combination of components, such as when left ear and right ear components are unintentionally exchanged, e.g. when an in-the-ear housing intended for the right ear is inadvertently connected to the BTE-housing fitted for the left ear.
  • a user may also be warned if wrong replacement parts are inadvertently delivered to the user and used with the hearing aid, whereby the user may be saved annoyance and possible extra visits to the dispenser's office.
  • the automatic identification is provided without increasing the number of conductors interconnecting the first and second circuitry, since the line used for transmission of the configuration information is already present for another purpose.
  • existing hearing aid parts may be configured to perform the new method without hardware modification, such as modification of the connector. Also, complexity and cost of the connector is kept at a minimum.
  • the first signal may be an audio signal representing sound, for example an audio signal transmitted to a receiver for emission of the sound towards an eardrum of the user.
  • the second circuitry may include a power supply.
  • the power supply may be energized through the line.
  • the power supply may be charged by transmitting a high frequency signal f > 20 kHz on the line
  • the power supply may be a capacitor.
  • the second circuitry may include a receiver.
  • the line may be an input line of the receiver.
  • the transmitter may be configured for transmitting a signal with at least one varying signal parameter, such as amplitude, frequency, phase, pulse width, etc.
  • the transmitter may be configured for modulation of the line, such as by amplitude modulation, frequency modulation, phase modulation, etc.
  • the transmitter may be configured for digital modulation of the line, such as by phase-shift keying, frequency-shift keying, amplitude-shift keying, quadrature amplitude modulation, etc.
  • the configuration information may include information identifying the particular arrangement of parts or components interconnected with the first and/or second circuitry.
  • the configuration information may include an identifier of a component, and/or a combination of components, of the second circuitry.
  • the type and fitting parameters of the hearing aid may be strongly dependent on the component, or combination of components, of the second circuitry.
  • the transmitter may be configured for transmitting the configuration information by short-circuiting the line.
  • the short-circuiting may cause corresponding voltage drops of the battery supply voltage that may be detected and decoded by the first circuitry, for example by a signal processor, e.g. a signal processor configured for performing hearing loss compensation, of the first circuitry, whereby the one component, or the combination of components, of the second circuitry is identified in the first circuitry.
  • a signal processor e.g. a signal processor configured for performing hearing loss compensation
  • the first housing may be a behind-the-ear housing and the second housing may be an earpiece.
  • the second circuitry may have a microcontroller programmed to short-circuit the line in accordance with an encoded time sequence for identification of the one component, or the combination of components, of the second circuitry.
  • RIE hearing aids may be provided with a connector for easy connection and disconnection of the second circuitry of second housing, such as an earpiece, to the first circuitry of the first housing, such as a BTE housing.
  • a connector for easy connection and disconnection of the second circuitry of second housing, such as an earpiece, to the first circuitry of the first housing, such as a BTE housing.
  • various types of receivers in earpieces may easily be connected to a BTE housing thereby providing different hearing aids with different receivers.
  • the new fitting instrument may automatically respond to received configuration information, e.g., by selecting hearing aid parameters in accordance with the received configuration information, e.g. a specific model of receiver identified. In this way, the receiver, the hearing aid and the hearing aid fitting parameters are combined correctly.
  • the operator of the new fitting instrument may take appropriate action in response to a display of the configuration information, e.g., by adjusting hearing aid parameters in accordance with the configuration information, e.g. a specific model of receiver identified. In this way, the receiver, the hearing aid and the hearing aid fitting parameters are combined correctly.
  • the operator of the new fitting instrument may take appropriate action in response to a display of the configuration information, e.g., by replacing the receiver, which is appropriate in case adjustment of the hearing aid to the specific model of receiver identified is not possible. In this way, undesired combinations of receiver, hearing aid and hearing aid fitting parameters can be discovered and corrected.
  • Adjustment of the hearing aid and hearing aid parameters may be controlled internally by said hearing aid.
  • the "audio signal” may be used to identify any analogue or digital signal forming part of a signal path from an input to an output of the hearing aid.
  • Signal processing in the new hearing aid and in the new fitting instrument may be performed by dedicated hardware or may be performed in a signal processor, or performed in a combination of dedicated hardware and one or more signal processors.
  • processor As used herein, the terms "processor”, “signal processor”, “controller”, “system”, etc., are intended to refer to CPU-related entities, either hardware, a combination of hardware and software, software, or software in execution.
  • a "processor”, “signal processor”, “controller”, “system”, etc. may be, but is not limited to being, a process running on a processor, a processor, an object, an executable file, a thread of execution, and/or a program.
  • processor designate both an application running on a processor and a hardware processor.
  • processors may reside within a process and/or thread of execution, and one or more "processors”, “signal processors”, “controllers”, “systems”, etc., or any combination hereof, may be localized on one hardware processor, possibly in combination with other hardware circuitry, and/or distributed between two or more hardware processors, possibly in combination with other hardware circuitry.
  • a processor may be any component or any combination of components that is capable of performing signal processing.
  • the signal processor may be an ASIC processor, a FPGA processor, a general purpose processor, a microprocessor, a circuit component, or an integrated circuit.
  • Figs. 1 - 3 schematically illustrates a RIE hearing aid 10 comprising a first housing, namely a BTE hearing aid housing (not shown - outer walls have been removed to make internal parts visible), to be worn behind the pinna 100 of a user.
  • a BTE hearing aid housing not shown - outer walls have been removed to make internal parts visible
  • the BTE housing accommodates first circuitry 12 with at least one BTE sound input transducer 14, 16, namely a front microphone 14 and a rear microphone 16 for conversion of an acoustic sound signal into respective microphone audio sound signals, optional pre-filters (not shown) for filtering the respective microphone audio sound signals, A/D converters (not shown) for conversion of the microphone audio sound signals into respective digital microphone audio sound signals that are input to a processor 18 configured to generate a hearing loss compensated output signal based on the input digital audio sound signals.
  • the hearing loss compensated output signal is transmitted through a line 44 (not visible) with electrical wires contained in a sound signal transmission member 20 to a receiver 22 of second circuitry 24 accommodated in a second housing (not shown - outer walls have been removed to make internal parts visible).
  • the receiver 22 provides an acoustic output signal for transmission towards the eardrum of the user, based on the hearing loss compensated output signal.
  • the second housing constitutes an earpiece 62 with an outer shape that is configured to be comfortably positioned in the ear canal of the user for fastening and retaining the receiver 22 and the sound signal transmission member 20 in their intended positions in the ear canal of the user as is well-known in the art of BTE hearing aids.
  • the earpiece 62 with the sound transmission member 20 is connected to the BTE housing with a connector 30 for easy connection and removal of the earpiece 62.
  • the earpiece 62 comprises the sound transmission member 20.
  • a large number of different earpieces may be connected to the BTE housing with the connector 30, such as with earpieces accommodating
  • the above-mentioned earpieces may further have receivers with different power ratings, e.g. 4 different ratings, and may further have sound tube members 20 of different lengths, e.g. 5 different standard lengths.
  • earpieces are provided configured for the left ear and earpieces are provided configured for the right ear.
  • some earpieces may be provided with other sensors, such as temperature sensors, pressure sensors, directional sensors, etc.
  • the earpiece 62 shown in the figures accommodates one In-the-Ear (ITE) microphone 26 that is positioned at the entrance to the ear canal when the earpiece 62 is positioned in its intended position in the ear canal of the user.
  • the ITE microphone 26 is connected to an A/D converter (not shown) and optionally to a pre-filter (not shown) in the BTE housing, with interconnecting electrical wires (not visible) contained in the sound transmission member 20.
  • the BTE hearing aid 10 is powered by battery 28.
  • the battery 28 may be rechargeable.
  • the ITE microphone 26 is positioned at an entrance to an ear canal of the user.
  • the output signal of the ITE microphone in the following denoted the ITE audio sound signal, generated by the ITE microphone 26 in response to acoustic sound received by the ITE microphone 26, preserves spatial cues of the received acoustic sound signal; or, in other words, the ITE microphone 26 is positioned so that its transfer function constitutes a good approximation to the Head Related Transfer Functions of the user.
  • the processor 18 conveys the directional information contained in the ITE audio sound signal to the hearing loss compensated output signal thereby also preserving spatial cues so that the user maintains his or her localization capability.
  • the ITE microphone 26 operates proximate the receiver 22 so that risk of feedback is high, which limits the maximum stable gain available with the hearing aid 10.
  • output signals of the microphones 14, 16 and the ITE microphone 26 are subjected to signal processing, e.g. adaptive filtering as for example explained in more detail in European patent application No.: 12199761.3 , in such a way that spatial cues are preserved and conveyed to the user of the hearing aid while feedback is simultaneously suppressed.
  • signal processing e.g. adaptive filtering as for example explained in more detail in European patent application No.: 12199761.3
  • a microphone may be accommodated in the second housing, i.e. in the earpiece 62, for suppressing occlusion.
  • the microphone is positioned inside the ear canal proximate the ear drum when the earpiece 62 is positioned in its intended position in the ear canal of the user.
  • occlusion of the ear canal by the second housing (earpiece) leads to an altered user perception of the user's own voice.
  • Hearing aid users do not adapt to occlusion and the occlusion effect has been cited by as many as 27% of hearing aid wearers as a reason for dissatisfaction with their hearing aids. This emphasizes the need for alleviating or, even better, eliminating the occlusion effect.
  • the receiver may compensate for the body conducted sound based on an output signal of the microphone positioned proximate the ear drum when the earpiece is positioned in its intended position in the ear canal of the user, so that the user perceives to listen to the hearing loss compensated signal only, whereby the occlusion effect is suppressed.
  • Fig. 2 shows the new hearing aid 10 in its operating position with the BTE housing 60 behind the ear, i.e. behind the pinna 100, of the user.
  • the new hearing aid 10 may have an arm 64 that is flexible and intended to be positioned inside the pinna 100, e.g. around the circumference of the conchae behind the tragus and antitragus and abutting the antihelix and at least partly covered by the antihelix for retaining the earpiece 62 in its intended position inside the outer ear of the user.
  • the arm may be pre-formed during manufacture, preferably into an arched shape with a curvature slightly larger than the curvature of the antihelix, for easy fitting of the arm into its intended position in the pinna 100.
  • Fig. 2 also schematically illustrates a new fitting instrument 70 and its wireless interconnections with the Internet 200 and the new BTE hearing aid 10 shown in its operating position with the BTE housing 60 behind the ear, i.e. behind the pinna 100, of the user.
  • Configuration information may be transmitted wirelessly 80 to the fitting instrument 70, e.g. to be displayed on a display of the fitting instrument 70 for verification by the operator of the fitting instrument 70, and possible corrective action in the event that the detected type of earpiece is not of the desired type.
  • the fitting instrument 70 is configured for fitting the hearing aid 10 in accordance with the configuration information.
  • the fitting instrument 70 has a processor 72 that is configured for responding to the configuration information received from the hearing aid 10.
  • the fitting instrument may be configured to access a remote server through the Internet 200, e.g. to access a data base for further information on the hearing aid 10, e.g. based on the received configuration information, e.g. with new values of fitting parameters relating to a new type of earpiece 62.
  • Fig. 3 shows a block diagram of the hearing aid circuitry 12, 24 for automatic configuration detection.
  • the second circuitry 24 is accommodated in the second housing, i.e. the earpiece 62; however, in another example, the second circuitry 24 may be accommodated in the connector 30.
  • the second circuitry 24 comprises the receiver 22 and a transmitter 40 in the form of a microcontroller 40 configured for transmission of a code that uniquely identifies the type of ear piece 62 with the second circuitry 24, e.g. the transmitted code contains the configuration information, e.g. the power rating of the receiver 22, whether the ear piece 62 is for the left ear or the right ear, and possibly the length of the sound transmission member 20, and possibly the number and types (occlusion and/or spatial cue) of microphones 26, and possibly the number and types of other sensors, etc.
  • the transmitted code contains the configuration information, e.g. the power rating of the receiver 22, whether the ear piece 62 is for the left ear or the right ear, and possibly the length of the sound transmission member 20, and possibly the number and types (occlusion and/or spatial cue) of microphones 26, and possibly the number and types of other sensors, etc.
  • the receiver 22 is driven by receiver driver 42 accommodated in the first housing, namely the BTE-housing 60.
  • the receiver driver 42 transmits the hearing loss compensated sound signal to the receiver on line 44 in the sound transmission member 20.
  • the receiver driver 42 transmits a high frequency signal, preferably of a frequency above 20 kHz, on line 44.
  • the high frequency signal charges capacitor 46 through diode 48, and the charged capacitor 46 subsequently supplies power to the transmitter (microcontroller) 40 during transmission of the code on line 44.
  • the high frequency signal is further low pass filtered in low pass filter 50 and input to the microcontroller 40 that is configured for detection of presence of the high frequency signal.
  • the microcontroller 40 is further configured for transmission of the code on line 44 upon seizure of the high frequency signal.
  • the microcontroller 40 is configured for transmission of the code by intermittently short-circuiting line 44 thereby generating a series of voltage drops of the supply voltage of the circuitry in the BTE housing that is detected by a comparator 52 of the first circuitry 12 in the BTE housing 60 already present for monitoring the voltage supply of the circuitry.
  • the code is transmitted and decoded using signal lines for transmission of an audio signal to the receiver, always present in a hearing aid, and without adding circuitry in the BTE housing.
  • the second circuitry 24 may be configured to transmit the configuration information repeatedly until power is no longer available from the power supply of the second circuitry, e.g. charged capacitor 46, or, the second circuitry 24 may be configured to transmit the configuration information repeatedly until receipt of an acknowledge signal from the first circuitry that the configuration information has been successfully received, e.g. by emission of the high frequency signal for a predetermined time period.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP14155375.0A 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive Active EP2908557B1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
EP18188194.7A EP3422742B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive
EP14155375.0A EP2908557B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive
DK14155375.0T DK2908557T3 (en) 2014-02-17 2014-02-17 Hearing aid configuration detection
DK18188194.7T DK3422742T3 (da) 2014-02-17 2014-02-17 Høreapparatkonfigurationsdetektering
US14/185,632 US10051392B2 (en) 2014-02-17 2014-02-20 Hearing aid configuration detection

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
EP14155375.0A EP2908557B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive

Related Child Applications (2)

Application Number Title Priority Date Filing Date
EP18188194.7A Division EP3422742B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive
EP18188194.7A Previously-Filed-Application EP3422742B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive

Publications (2)

Publication Number Publication Date
EP2908557A1 true EP2908557A1 (fr) 2015-08-19
EP2908557B1 EP2908557B1 (fr) 2018-08-15

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EP14155375.0A Active EP2908557B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive
EP18188194.7A Active EP3422742B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive

Family Applications After (1)

Application Number Title Priority Date Filing Date
EP18188194.7A Active EP3422742B1 (fr) 2014-02-17 2014-02-17 Détection de configuration d'appareil d'aide auditive

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DK (2) DK2908557T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP4266704A1 (fr) * 2022-04-21 2023-10-25 GN Hearing A/S Unité cros pour un système de dispositif auditif cros

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Publication number Priority date Publication date Assignee Title
US20090052706A1 (en) * 2007-08-21 2009-02-26 Siemens Audiologische Technik Gmbh Automatic identification of receiver type in hearing aid devices
DE102008030551A1 (de) * 2008-06-27 2009-08-27 Siemens Medical Instruments Pte. Ltd. Hörgerät zur Aufnahme von zumindest einer austauschbaren Komponente, austauschbare Komponente und Hörgerätesystem aus dem Hörgerät und der Komponente
EP2434780A1 (fr) 2010-09-22 2012-03-28 GN ReSound A/S Appareil d'aide auditive avec suppression d'occlusion et contrôle d'énergie subsonique

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DE4114921A1 (de) 1991-05-07 1992-11-12 Ahlborn Mess Und Regelungstech Elektrische steckverbindung
CA2352346C (fr) 1998-11-24 2011-01-11 Phonak Ag Prothese auditive
US6859538B1 (en) 1999-03-17 2005-02-22 Hewlett-Packard Development Company, L.P. Plug and play compatible speakers
US7292876B2 (en) 2002-10-08 2007-11-06 Sonion Nederland B.V. Digital system bus for use in low power instruments such as hearing aids and listening devices
DE102006031401A1 (de) 2006-07-05 2008-01-10 Neutrik Aktiengesellschaft Einrichtung, mittels der am Ende eines Kabels ein mit dem Anfang des Kabels in elektrischer Verbindung stehender elektrischer Steckverbinder identifizierbar ist
DE102007031488A1 (de) 2007-07-06 2009-01-08 Siemens Audiologische Technik Gmbh Verfahren und Anordnung zum Datenaustausch mit einem Hörgerät
EP2061274A1 (fr) 2007-11-19 2009-05-20 Oticon A/S Instrument d'aide auditive utilisant des récepteurs dotés de propriétés de performance différents
ES2443918T5 (es) 2007-12-27 2017-06-06 Oticon A/S Dispositivo de audición y procedimiento para la recepción y / o el envío inalámbricos de datos
WO2011110218A1 (fr) * 2010-03-09 2011-09-15 Widex A/S Prothèse auditive en deux parties comprenant un bus de données et procédé de communication entre les parties
DK2663095T3 (da) 2012-05-07 2016-02-01 Starkey Lab Inc Høreapparat med fordelt bearbejdning i øreprop

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090052706A1 (en) * 2007-08-21 2009-02-26 Siemens Audiologische Technik Gmbh Automatic identification of receiver type in hearing aid devices
DE102008030551A1 (de) * 2008-06-27 2009-08-27 Siemens Medical Instruments Pte. Ltd. Hörgerät zur Aufnahme von zumindest einer austauschbaren Komponente, austauschbare Komponente und Hörgerätesystem aus dem Hörgerät und der Komponente
EP2434780A1 (fr) 2010-09-22 2012-03-28 GN ReSound A/S Appareil d'aide auditive avec suppression d'occlusion et contrôle d'énergie subsonique

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP4266704A1 (fr) * 2022-04-21 2023-10-25 GN Hearing A/S Unité cros pour un système de dispositif auditif cros
US12108217B2 (en) 2022-04-21 2024-10-01 Gn Hearing A/S CROS unit for a CROS hearing device system

Also Published As

Publication number Publication date
EP2908557B1 (fr) 2018-08-15
EP3422742A1 (fr) 2019-01-02
EP3422742B1 (fr) 2021-05-26
DK3422742T3 (da) 2021-08-30
DK2908557T3 (en) 2018-11-26

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