EP1698908A2 - Procédé d'ajustage d'une prothèse auditive, prothèse auditive et unité de commande mobile pour l'ajustage d'une prothèse auditive - Google Patents

Procédé d'ajustage d'une prothèse auditive, prothèse auditive et unité de commande mobile pour l'ajustage d'une prothèse auditive Download PDF

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Publication number
EP1698908A2
EP1698908A2 EP06101317A EP06101317A EP1698908A2 EP 1698908 A2 EP1698908 A2 EP 1698908A2 EP 06101317 A EP06101317 A EP 06101317A EP 06101317 A EP06101317 A EP 06101317A EP 1698908 A2 EP1698908 A2 EP 1698908A2
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EP
European Patent Office
Prior art keywords
hearing aid
signal
control device
mobile control
drive device
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
EP06101317A
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German (de)
English (en)
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EP1698908B1 (fr
EP1698908A3 (fr
Inventor
Felix Grasbon
Gerhard Sporer
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 Audiologische Technik GmbH
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Filing date
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Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1698908A2 publication Critical patent/EP1698908A2/fr
Publication of EP1698908A3 publication Critical patent/EP1698908A3/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids 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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; 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
    • H04R2460/07—Use of position data from wide-area or local-area positioning systems in hearing devices, e.g. program or information selection

Definitions

  • the invention relates to a hearing aid with an input transducer for receiving an input signal and conversion into an electrical signal, a signal processing unit for signal processing of the electrical signal and an output transducer for generating a perceptible by a user of the hearing aid as an acoustic signal output signal. Furthermore, the invention relates to a method for setting such a hearing aid device and a mobile drive unit for the automatic adjustment of operating parameters of a hearing aid.
  • an input signal is received by means of an input transducer and converted into an electrical input signal.
  • an input transducer usually serves as an input transducer at least one microphone which receives an acoustic input signal.
  • Modern hearing aids often comprise a microphone system with a plurality of microphones in order to achieve a direction dependent on the direction of arrival of acoustic signals reception, a directional characteristic.
  • the input transducers may also include a telecoil or antenna for receiving electromagnetic input signals.
  • the input signals converted by the input transducer into electrical input signals are fed to a signal processing unit for further processing and amplification. The further processing and amplification takes place to compensate for the individual hearing loss of a Höragistechnikitatis usually in response to the signal frequency.
  • the signal processing unit outputs an electrical output signal, which is fed via an output transducer to the hearing of the hearing aid wearer, so that the latter perceives the output signal as an acoustic signal.
  • output transducers usually listeners are used, which generate an acoustic output signal.
  • output transducers for generating mechanical vibrations are also known, which directly excite certain parts of the ear, such as the ossicles, to vibrate.
  • output transducers are known which directly stimulate neurons of the ear.
  • EP 0 064 042 B1 discloses a hearing aid device with a microphone, a signal processing unit and a receiver, in which different parameter inserts can be stored in a memory in order to adapt the signal processing unit to different listening situations.
  • the hearing aid is thereby equipped with different hearing programs for different listening situations, which can be switched manually.
  • a hearing aid which has a signal analysis unit for automatic conversion between different hearing programs, which recognizes the current hearing situation and selects a suitable hearing program.
  • a hearing aid with a wirelessly connected remote control is known.
  • the remote control can be connected to a variety of sensors and peripherals to provide requested or unsolicited information.
  • information about the position of a user may be transmitted by specially trained broadcasters at specific points in a retirement home, or a self-contained, user-assisted gyroscope, accelerometer and compass inertial navigation system or GPS (Global Positioning System) receiver may be used.
  • GPS Global Positioning System
  • a hearing aid which detects the automatic selection of a hearing program, whether it is in the vicinity of an external transmitter.
  • the transmitter generates a transmitter-specific signal, so that an assignment of different transmitters can take place.
  • D-GPS Different Satellite Positioning Systems
  • An object of the present invention is to specify a method for setting a hearing aid device and a hearing aid device, in which the adaptation of the signal processing to different hearing ranges is improved.
  • the adaptation of the signal processing of the hearing aid to different spatial hearing areas is carried out by setting at least one parameter influencing the signal processing of the hearing aid.
  • a satellite-supported position determination system for generating a position signal is provided for this purpose. This is generated and evaluated to automatically adjust the parameter depending on the position signal.
  • the method according to the invention has the advantage that the adjustment of the parameter does not occur manually. Furthermore, it has the advantage that the setting does not depend on the particular hearing situation that is recorded by the input transducer. This is particularly advantageous when the automatic detection of a hearing situation is not clear and thus the hearing aid is operated with a wrong parameter. Another advantage is that no external, specially adapted to the hearing aid transmitter are used, but that the worldwide accessible network of satellites for satellite positioning is used. This has a particularly advantageous effect on the structure of the hearing aid, since the Hearing aid either with an integrated satellite positioning system can be formed in a component or operated with an additional external hearing aid module with a satellite positioning system and can exchange information. Depending on the form of training, the position determination system transmits information about the position of the integrated unit or the hearing aid module.
  • the position signal is transmitted continuously or at intervals pulsed.
  • the former has the advantage that position changes can immediately affect the setting of the parameter, the latter procedure consumes less energy.
  • the information about the position from the position signal in the position determination system itself is determined and transmitted, for example in the form of global coordinates to the signal processing unit.
  • This has the advantage that a conventional positioning system can be used.
  • a kind of raw information is transmitted to the signal processing unit and there the information about the position is extracted.
  • the requirements for the position determining system are lower, so that e.g. a more energy-efficient implementation is possible.
  • One advantage is that the essential calculations are performed with only one signal processing unit, namely that of the hearing aid, so that the calculation is efficiently controlled and e.g. can only be done if necessary.
  • the adjustment of the parameter causes a signal processing that is adapted to an acoustic situation in the listening area.
  • the acoustic situation can be determined, for example, by acoustic signals which are to be processed optimally. For example, in a TV room on the TV adapted output signal to be generated in a conference room especially input signals from interlocutors are optimally processed or on a sports field to different hearing programs are set at different locations.
  • the adjustment of the parameter is part of a hearing program setting of a hearing program, which is stored in particular in the signal processing unit of the hearing aid. Accordingly, the method may set a set of parameters that together define the listening program.
  • a hearing program is to be understood as meaning both a permanently set amplification profile and a functional signal processing which continuously adapts to further environmental parameters.
  • At least one of the auditory regions is defined in its two- or three-dimensional extent. That is, a spatial area, such as the living room, or an area, such as a soccer field, is e.g. defined with its boundary coordinates or via a geometry with respect to a reference point. The listening area will then be given an adjustment of the parameter, i. e.g. a value or function.
  • the extent of the hearing range can be entered using global coordinates, for example, by means of a hearing aid programming unit.
  • at least one position of the satellite-supported position-determining system can be stored in order to hold, for example, the corner coordinates of the soccer field.
  • the parameter setting is maintained until the position signal indicates a position outside the listening area. For example, when leaving the listening area, "TV room" can be automatically switched back to a previously used parameter setting. Alternatively, it is possible to switch to a parameter setting based on an automatic analysis of the hearing situation. Alternatively, furthermore, a parameter setting can be maintained so long after leaving a first audible range until a position signal indicates a position within a second audible range, so that when changing into this second audible range, the operation of the hearing aid with at least one new parameter setting.
  • the position determination with the satellite-based positioning system is differential, i. using a reference unit that reports runtime errors in the satellite signal.
  • a delay compensation can be calculated due to different influence of different frequency bands.
  • a higher accuracy can be achieved via a so-called assisted position determination, for example by using signals from the mobile network.
  • information about an orientation of the hearing aid in two or three dimensions is taken into account as additional information when setting the parameter.
  • This can be done for example by a compass and / or a tilt sensor.
  • the parameter setting is made dependent on whether eye contact exists to the acoustic source (for example, high / low gain) or whether the user looks away from the sound source (eg low / high gain).
  • the embodiment of the hearing aid in which the satellite-based position determination system is housed in a hearing aid module, further has, for example, the advantage that the hearing aid module can be stored in a listening area in order to provide the user with the appropriate parameter setting during signal processing despite leaving the listening area , For example, if an audio signal from a TV is used directly as an input signal, then the audio signal can be processed with a parameter adapted to the television also outside the listening area.
  • FIG. 1 shows schematically a hearing aid 1 with an input transducer (microphone) 3 for receiving an input signal and conversion into an electrical signal, a signal processing unit 5 for signal processing of the electrical signal and an output transducer (earphone) 7 for generating a user of the hearing aid 1 as acoustic signal perceptible output signal.
  • the signal processing is adapted with at least one parameter P to different spatial listening areas.
  • a satellite-supported position determination system 9 is provided which generates a position signal S (X, Y, Z) and transmits it to the signal processing unit 5.
  • the signal processing unit 5 evaluates the position signal S (X, Y, Z) and automatically sets the parameter as a function of the position signal S (X, Y, Z).
  • the signal processing for example, a memory in which different listening areas H i , ... are defined in their geometric dimensions and their global locations.
  • the memory unit 11 can also be arranged within the satellite-supported position determination system 9.
  • the positioning system 9 can be integrated as a structural unit 1A in the hearing aid 1 or it can be designed as independently designed Höranges réellemodul, wherein the hearing aid 1 via a cable or wirelessly transmitted the position signal S (X, Y, Z) and / or with the Hearing aid 1 exchanges information.
  • the positioning system 9 receives radio frequency signals from a plurality of satellites 19 and determines from these signals his current position.
  • the information about the position is transmitted as a position signal S (X, Y, Z) to the signal processing 5.
  • Additional information which may influence the setting of the parameter is, for example, the orientation of the head-mounted component of the hearing aid 1. This is measured for example via a compass 13. Additionally or alternatively, the orientation may be determined via a tilt sensor 15 in a vertical plane.
  • Such sensors can be integrated into a hearing aid 1 without much effort.
  • the orientation of the hearing aid and thus, for example, the viewing direction of a user of the hearing aid 1 can now be determined and thus set in relation to a sound source whose spatial position is also known. The thus recognized acoustic situation can be evaluated in such a way that optimum adjustment of the signal processing is ensured by setting the parameter.
  • the dependence of the parameter on the position signal can for example be entered with a programming unit 17.
  • the programming can be carried out, for example, via the normal hearing device programming interface, eg also wirelessly according to the Bluetooth standard.
  • the dependence can also be stored as a functional assignment, so that, for example, with increasing distance from a location, the amplification of the signal processing 5 is increased. This corresponds to a parameter setting due to a relative change in the position of the positioning system to a predetermined coordinate.
  • listening areas can be defined, ie areas or volumes can be defined in which a specific value is to be taken by the parameter. If all parameters of a hearing program are defined for a listening area, then this hearing area is as it were assigned a hearing program. Once the user or the positioning system stops in this listening area, then takes place signal processing according to the hearing program.
  • FIG. 2 illustrates the arrangement of areal auditory regions in a coordinate system of latitudes and longitudes 21.
  • a rectangular area is determined by the coordinates of the corners X1, X2, X3 and X4.
  • the corner coordinates X3 and X4 are also corner coordinates of a second listening area B.
  • a listening area C is defined by a circle around the point (X R , Y R) of radius R, where all points within the circle are not simultaneously in one of the listening areas A or B, are defined as listening area C.
  • FIG 2 illustrates a differential position determination using the satellites 19 and a transmitter 23.
  • the transmitter 23 transmits a hearing aid 25 (carrier not shown) according to the invention within the listening area A in addition an error signal 27, wherein the error signal 27 runtime error of the satellite signals of the satellite 19 includes.
  • the error signal 27 is generated using a satellite-based reference positioning system 29. Due to the fixed position of the external transmitter 23, erroneous transit times can be calculated by matching the known position of the transmitter 23 with the received signals from the satellites 19.
  • the improvement of the accuracy with the aid of a ground station is also referred to as differential position determination.
  • the calculation of such runtime errors can also be achieved by the use of different frequency bands. Alternatively, you can also call a moving receiver as an auxiliary signal.
  • FIG. 3 illustrates the invention by way of example on a soccer field D.
  • the soccer field D itself is expired at the beginning of the game, wherein the position determination system operates in a mode in which the coordinates of the travel path are stored.
  • the area D could be through the four coordinates the corner posts are entered.
  • the player herein is on football field D, his hearing aid is in football mode.
  • a second area E is defined around the exchange banks 31.
  • two sub-listening programs are additionally defined as a function of the orientation of the hearing aid in the room: on the one hand a football observation mode and on the other a conversation mode.
  • the user's angle of vision to the football field (head 33) or to a conversation partner (head 35) can be determined.
  • different hearing programs (or settings of parameters) are made.
  • FIG. 4 clarifies the use of three-dimensional hearing ranges F, G and H. This is particularly advantageous if, within a building 41, hearing areas located spatially one above the other are to be defined.
  • the listening area F corresponds to the parameter setting in a canteen
  • the listening area G to the parameter setting in an office, etc.
  • the angle of inclination affects the setting of a television listening program which extends around a television 51 within a radius of a few meters.
  • the television listening program is set within the listening area only when the user, such as user 51, watches the TV sitting upright with a head tilt angle ⁇ .
  • User 53 on the other hand, lies on a sofa, so that his inclination of the head (head angle ⁇ ') does not lead to the television listening program.
  • the tilt sensor can interact with an electric compass so that an operator lying on the sofa and watching the television also listens in the television listening program.
  • FIG. 5 it is additionally clarified that, for example, user 51 has deposited his satellite-supported position determination system 55 designed as a hearing aid module on a television table. As long as the positioning system 55 remains there, the user's hearing aid 51 is set to the television mode even when the user 51 leaves the room.
  • a bus driver 61 with the position determination system 63 can make the setting of hearing parameters as a function of the speed.
  • the determination of the speed by means of satellite-based positioning systems 63 takes place via the frequency shift of the satellite signals.
  • the gain of the hearing aid to compensate for the wind noise can be increased.
  • FIG. 6 shows a user 65 whose satellite-based positioning system is integrated in a portable mobile telephone 67.
  • the position determination in the mobile phone is preferably supported by the telephone network (supported satellite positioning).
  • the position of the hearing aid is preferably controlled by wireless signal transmission from the mobile phone.
  • FIG. 7 shows, in a simplified block diagram, a driver device 101 that can be carried by a user according to the invention.
  • a driver device 101 As a user interface, a display 102 and a keyboard 103 are provided.
  • the drive device 101 may also have other input or output means.
  • the Control device 101 additionally a microphone 107 and a speaker 108 for voice input and voice output, whereby a voice control of the drive device is possible. For example, this is automatically available anyway when integrated into a mobile telephone.
  • the drive device 101 may also be integrated in a remote control of the hearing aid.
  • this is advantageously equipped with an AGPS receiver 104 (Assisted Global Position System).
  • AGPS receiver 104 Assisted Global Position System
  • This allows the current position to be determined to within one meter.
  • the position determination takes place in real time or at least very promptly, so that the current position of the drive device 101 is always present and also movements of a person carrying the drive device 101 can be detected.
  • Storage device 105 is also present in drive device 101, in which the spatial coordinates of preferred user areas of the user can be stored.
  • the memory 105 the coordinates of various rooms of a building may be stored in which the user preferably resides.
  • data for controlling a hearing aid can be stored in the memory 105, wherein different, stored in the memory 105 spatial areas different data can be assigned.
  • the drive device 101 also has an interface 106 for wireless data exchange with the device in question. The data transmission preferably satisfies the Bluetooth standard.
  • All essential components of the drive device 101 are connected to a signal processing and control unit 109. This controls the signal transmission between the individual components of the drive device 101 and ensures the signal processing of all relevant data. In particular, in the signal processing and control unit 109 the data received from the AGPS receiver 104 processed and evaluated.
  • the control device 101 is generally used to control a controllable hearing aid device 110.
  • the controllable hearing aid device 110 is carried by the user of the drive device 101.
  • the drive device 101 may additionally be configured to control a plurality of different controllable devices. For this purpose, it can be programmed to control the different devices in a suitable manner.
  • the signal transmitted by the control device 101 to the controllable hearing aid device 110 comprises at least one control command for the controllable hearing aid device 110.
  • the control command may cause the controllable hearing aid device 110 to change from a first sequence program to a second sequence program.
  • the transmitted signal may, however, also directly contain parameter settings which are stored in the controllable hearing aid device 110 after the transmission and influence the signal processing in the controllable device 110 from this point in time.
  • controllable hearing aid device 110 it is also possible for a plurality of different sequence programs of the controllable hearing aid device 110 to be stored in the control device 101 and for a specific sequence program to be selected and transmitted to the controllable hearing aid device 110 as a function of the instantaneous spatial position of the control device 101 and subsequently the program sequence in FIG controllable hearing aid 110 determined.
  • the drive device 101 only influences the signal processing of the controllable hearing aid device 110 as long as a signal transmission from the drive device 101 to the controllable hearing aid device 110 takes place continuously or within a certain period of time.
  • This embodiment has the advantage that the controllable hearing aid 110 is operated in a predefined state when the connection between the drive device 101 and the controllable hearing aid 110 is interrupted.
  • the invention has the advantage that between the control device 101 and the controlled hearing aid 110 no further intermediate devices are required.
  • the data transmission takes place directly between the drive device 101 and the controlled hearing aid 110.
  • the function of the hearing aid 110 may be dependent on other parameters in addition to the location of the user. These include e.g. Parameters deriving from an evaluation of the signal received by the AGPS receiver of the driver 101. These include e.g. the determination of a movement of the user, the direction of movement or speed of the user.
  • the control of the controllable hearing aid 110 may also depend on parameters that are independent of the current location of the user. Such parameters are e.g. the time of day, the day of the week, the angle of inclination or the ambient temperature.
  • a drive device 101 can also be used by a plurality of users, wherein advantageously different user profiles can be stored. The control of the controllable hearing aid 110 then also takes place depending on which user is currently wearing the driver 101, that is, which user profile is activated.
  • control parameter in addition to the current location of the user can also serve the orientation of the drive device 101 in space.
  • a vertical carrying position of a drive device 101 fastened to a belt clip can be recognized, wherein in this carrying position the control of the controllable hearing aid device 110 is activated by the drive device 101.
  • the drive device 101 is in a horizontal orientation, this indicates a lying position the user or a set aside control device 101, in which the control of the controllable hearing aid device 110 is deactivated by the drive device 101.
  • Which position-dependent settings for the hearing aid are set by means of the drive device 101 is determined by a corresponding programming of the drive 101.
  • Corresponding inputs to the control device 101 are carried out by means of existing interfaces (keyboard 103, Bluetooth interface 106, etc.).
  • the control operations to be carried out can also be carried out conveniently via an external unit (not shown), e.g. a PC, are input to the driving device 101.
  • the drive device 101 may also comprise wired interfaces for connection to an external device for programming.
  • the signal processing and control unit 109 constantly checks whether operating parameters of the controllable hearing aid device 110 should change as a result of a change of location of the user and thus of the activation device 101. This results in particular by a permanent comparison of the different areas associated with settings with the current position. If a change in at least one operating parameter of the controllable hearing aid device 110 is provided due to a change of location of the drive device 101, a corresponding signal is generated by the drive device 101 and transmitted to the controllable hearing aid device 110 via the Bluetooth interface. This has for this purpose a suitable for wireless reception of the control signal interface, in particular a Bluetooth transmitting and receiving unit 111.
  • the signal processing in the signal processing and control unit 15 can be set via certain parameters, for example are stored in a program memory 113 and determine, for example, the program selection and the volume setting.
  • the hearing aid comprises a button which stores the current coordinate, orientation and / or inclination. These coordinates can be used to offer the user different geometries, which he can then assign to the various coordinates in order to define the listening area. So he can specify a listening area by several coordinates, and assign him a speed interval, a minimum speed and / or a direction in a place.

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Mobile Radio Communication Systems (AREA)
  • Telephone Function (AREA)
  • Control Of Position Or Direction (AREA)
  • Steering Controls (AREA)
EP06101317.3A 2005-02-14 2006-02-06 Procédé d'ajustage d'une prothèse auditive, prothèse auditive et unité de commande mobile pour l'ajustage d'une prothèse auditive Revoked EP1698908B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102005006660A DE102005006660B3 (de) 2005-02-14 2005-02-14 Verfahren zum Einstellen eines Hörhilfsgeräts, Hörhilfsgerät und mobile Ansteuervorrichtung zur Einstellung eines Hörhilfsgeräts sowie Verfahren zur automatischen Einstellung

Publications (3)

Publication Number Publication Date
EP1698908A2 true EP1698908A2 (fr) 2006-09-06
EP1698908A3 EP1698908A3 (fr) 2007-12-26
EP1698908B1 EP1698908B1 (fr) 2013-08-28

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ID=36685965

Family Applications (1)

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EP06101317.3A Revoked EP1698908B1 (fr) 2005-02-14 2006-02-06 Procédé d'ajustage d'une prothèse auditive, prothèse auditive et unité de commande mobile pour l'ajustage d'une prothèse auditive

Country Status (5)

Country Link
US (1) US7853030B2 (fr)
EP (1) EP1698908B1 (fr)
CN (1) CN1822723B (fr)
DE (1) DE102005006660B3 (fr)
DK (1) DK1698908T3 (fr)

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WO2008128563A1 (fr) 2007-04-18 2008-10-30 Phonak Ag Système auditif et son procédé de fonctionnement
WO2009049646A1 (fr) * 2007-10-16 2009-04-23 Phonak Ag Procédé et système pour une assistance auditive sans fil
WO2009049645A1 (fr) * 2007-10-16 2009-04-23 Phonak Ag Procédé et système pour une assistance auditive sans fil
DE102012213160A1 (de) * 2012-07-26 2013-09-26 Siemens Medical Instruments Pte. Ltd. Bestimmung einer Position eines mobilen Endgeräts
EP2830329B1 (fr) 2013-07-19 2017-09-27 Starkey Laboratories, Inc. Système de détection d'environnements spéciaux pour des dispositifs d'assistance auditive
US9883297B2 (en) 2013-08-20 2018-01-30 Widex A/S Hearing aid having an adaptive classifier
US10129662B2 (en) 2013-08-20 2018-11-13 Widex A/S Hearing aid having a classifier for classifying auditory environments and sharing settings
US10206049B2 (en) 2013-08-20 2019-02-12 Widex A/S Hearing aid having a classifier

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EP2227042B1 (fr) 2005-05-03 2011-12-28 Oticon A/S Système et procédé pour partager des ressources réseau entre des prothèses auditives
US7876906B2 (en) 2006-05-30 2011-01-25 Sonitus Medical, Inc. Methods and apparatus for processing audio signals
US7764798B1 (en) * 2006-07-21 2010-07-27 Cingular Wireless Ii, Llc Radio frequency interference reduction in connection with mobile phones
DE102007005861B3 (de) * 2007-02-06 2008-08-21 Siemens Audiologische Technik Gmbh Hörvorrichtung mit automatischer Ausrichtung des Richtmikrofons und entsprechendes Verfahren
US8270638B2 (en) * 2007-05-29 2012-09-18 Sonitus Medical, Inc. Systems and methods to provide communication, positioning and monitoring of user status
JP5252738B2 (ja) * 2007-06-28 2013-07-31 パナソニック株式会社 環境適応型補聴器
EP2224749B1 (fr) 2009-02-27 2011-10-26 Research In Motion Limited Procédé et système pour le contrôle d'une sortie de niveau de signal maximum vers des écouteurs raccordés à un dispositif sans fil
US8189798B2 (en) 2009-02-27 2012-05-29 Research In Motion Limited Method and system for controlling a maximum signal level output to headphones coupled to a wireless device
DE102009015145A1 (de) * 2009-03-26 2010-10-07 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit Fernbedienungseinheit zur Positionsbestimmung und Verfahren
DE102009018811A1 (de) * 2009-04-24 2010-06-17 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit akustischer Menüvorrichtung und Steuerungsverfahren
US8553897B2 (en) 2009-06-09 2013-10-08 Dean Robert Gary Anderson Method and apparatus for directional acoustic fitting of hearing aids
US8879745B2 (en) 2009-07-23 2014-11-04 Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust Method of deriving individualized gain compensation curves for hearing aid fitting
US9101299B2 (en) 2009-07-23 2015-08-11 Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust Hearing aids configured for directional acoustic fitting
DE102009048071A1 (de) * 2009-10-01 2010-11-11 Siemens Medical Instruments Pte. Ltd. Verfahren und Vorrichtung zum Einstellen eines Hörgeräts unter Berücksichtigung einer Raumakustik
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US20060182294A1 (en) 2006-08-17
DK1698908T3 (da) 2013-11-25
EP1698908A3 (fr) 2007-12-26
DE102005006660B3 (de) 2006-11-16
CN1822723B (zh) 2012-08-08
US7853030B2 (en) 2010-12-14
CN1822723A (zh) 2006-08-23

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