EP2012557A2 - Appareil auditif avec circuit d'activation multi-niveaux et son procédé de fonctionnement - Google Patents

Appareil auditif avec circuit d'activation multi-niveaux et son procédé de fonctionnement Download PDF

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Publication number
EP2012557A2
EP2012557A2 EP08104589A EP08104589A EP2012557A2 EP 2012557 A2 EP2012557 A2 EP 2012557A2 EP 08104589 A EP08104589 A EP 08104589A EP 08104589 A EP08104589 A EP 08104589A EP 2012557 A2 EP2012557 A2 EP 2012557A2
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EP
European Patent Office
Prior art keywords
activation
hearing aid
unit
signal
evaluation unit
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
EP08104589A
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German (de)
English (en)
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EP2012557A3 (fr
EP2012557B1 (fr
Inventor
Ulrich Kornagel
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Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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Publication date
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Publication of EP2012557A2 publication Critical patent/EP2012557A2/fr
Publication of EP2012557A3 publication Critical patent/EP2012557A3/fr
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Publication of EP2012557B1 publication Critical patent/EP2012557B1/fr
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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
    • 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
    • H04R2225/41—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; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/03—Aspects of the reduction of energy consumption in hearing devices
    • 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

Definitions

  • the invention relates to a hearing aid with multi-stage activation circuit and a method for its operation.
  • Hearing aids are primarily medical aids for the compensation of a wide variety of hearing impairments.
  • they form an important link for communication, in particular for the perception of ambient noise by the hearing aid wearer.
  • they should as comfortable as possible allow a largely natural hearing and on the other hand, regardless of any equipment variants ensure that at least certain important ambient noise can be safely and classifiable perceived by the hearing aid wearer.
  • a hearing aid wearer it is advantageous for a hearing aid wearer to wear his hearing aid or his hearing aids as permanently as possible and to keep them ready for operation so as not to be completely acoustically decoupled from his environment at any time.
  • this would unnecessarily be consumed in a regular operation power, since in particular the microphone, electronic circuits for signal processing or evaluation and a repeater strand with optionally connected loudspeaker would be kept permanently on standby, although signal processing and / or amplification would not be required. Exemplary situations can be found especially during the night's sleep of the hearing aid wearer.
  • the time span between sounds that are necessarily to be amplified and relevant to the hearing aid wearer can amount to several hours, which is associated with considerable energy consumption, which is caused only by the provision of the functionality of the hearing aid.
  • a complete shutdown of the hearing aid without assistance of the hearing aid wearer is regarded as not advantageous in such cases, since the hearing aid wearer would be acoustically more or less, in severe cases completely disconnected from the environment depending on his individual hearing loss. For example, he could no longer hear warning signals, alarm rings, telephone rings and similar key noises and did not react to these noises. Even in phases of complete rest of the hearing aid wearer such unconditional acoustic decoupling is often not desirable.
  • WO 01/20965 A2 is a method for determining a current acoustic environment situation and the application of the method in a hearing aid known.
  • the hearing aid in addition to microphones and a handset on a transmission unit.
  • the signals recorded by the microphones are classified by means of a signal analysis unit and a signal identification unit, and the hearing program corresponding to the current environment situation is activated.
  • the object of the invention is to specify a possibility of being able to operate a hearing aid as energy-efficiently and comfortably as possible, without acoustically decoupling the hearing aid wearer from the environment.
  • the invention is based on the use of a multi-stage circuit for activating a hearing aid.
  • the hearing aid In a normal operating mode, the hearing aid is used as in conventional embodiments to record ambient sound via a microphone, convert it into electrical signals, adapt and / or amplify them if necessary and for a corresponding stimulus generation in the ear of the hearing aid by emitting sound waves in the ear the hearing aid wearer or otherwise provide prosthetic stimulus introduction. If a situation is detected that obviously does not require sound amplification, the hearing aid automatically switches to a sleep mode. This can advantageously be done when over a certain time a minimum sound level was not exceeded. Thus, in situations where power is to be saved or the hearing aid should not amplify sound, the hearing aid is switched to a sleep mode.
  • the invention can be implemented with a hearing aid having a multi-stage activation circuit comprising a microphone, a signal processing and amplification circuit and an output unit, wherein a primary activation unit as the first stage of the activation circuit, an evaluation unit as the second stage of the activation circuit and a main activation unit as the third stage the activation circuit is included, wherein the primary activation unit is designed so that they monitor at least one sound-induced input level and on exceeding a threshold value of this input level can forward incoming signals to the evaluation unit, the evaluation unit is designed so that it exceeds at least one threshold value a sound-induced input level can be activated and determine at least one incoming signal feature suitable for detecting and / or classifying a sound causing the incoming signals, and the main activating unit is adapted to be activated when the at least one of the Evaluation unit has certain feature close to a sound that is to be perceived by the wearer of the hearing aid, wherein the main activation unit for activating further components of the hearing aid including the circuit for signal processing and amplification
  • the automatic switching process to change to the sleep mode can be supplemented by a possibility of manual shutdown or switching to a sleep mode, which is useful, for example, if a hearing aid wearer knows that in the near future no relevant sound events will be expected. In this way, he saves the longer phase of the device readiness, in which would be permanently waiting for a sound event, until after a minimum time without exceeding a threshold value of the sound level, the automatic switching would be in the sleep mode.
  • a manual switch to a sleep mode may also be useful if the hearing aid wearer does not want to be distracted by ambient noise, as may be the case, for example, in undisturbed work, reading a book or other activities, but still not completely audible of the Environment wants to be decoupled or may, for example, to be able to perceive warning signals, telephone rings and similar sounds.
  • these requirements are realized in a very energy-efficient manner by only activating a primary activation unit during the phase in which the hearing aid is in sleep mode, which checks whether an applied sound pressure via the microphone is sufficient to generate a minimum input level or not. If a minimum input level is exceeded, it does not immediately activate the entire hearing aid including the amplifier section, but it is merely connected to another activation unit, which makes a more detailed analysis of the incoming signal and provides depending on the result of this signal analysis for a complete activation of the hearing aid or, if the signal analysis indicates that the incoming signal is merely a noise not relevant to the hearing aid wearer or a noise causing the hearing aid to return to the sleep mode in which only the first or primary activation unit is active is.
  • the invention thus also consists in any method for activating a hearing aid with multi-stage activation circuit comprising a microphone, a signal processing and amplification circuit and an output unit in which first a primary activation unit as the first stage of the activation circuit monitors at least one sound-induced input level and when exceeded a threshold value of this input level then activates an evaluation unit as the second stage of the activation circuit and forwards incoming signals to the evaluation unit, the evaluation unit at least one characteristic, in particular a physical parameter, the forwarded incoming signals determines that for detecting and / or classification of the incoming signals causing Sound is suitable, and in the case of the detection and / or classification of a sound that is to be perceived by the wearer of the hearing aid, then a Hau Activated pt2011technik as a third stage of the activation circuit, which then for activating further components of the hearing aid including the signal processing and amplification circuit and the Output unit ensures.
  • This method according to the invention can advantageously be supplemented by alternative activation algorithms.
  • Fig.1 shows a schematic representation of the essential components of a hearing aid according to the invention.
  • These modules include a microphone 1, a circuit for signal processing and amplification 2, a speaker to be worn in the ear as output unit 3 and in hearing aids according to the invention a primary activation unit 4 as the first stage of the activation circuit, an evaluation unit 5 as the second stage of the activation circuit and a Main activation unit 6 as the third stage of the activation circuit.
  • a fourth stage 7 is included in the activation circuit, which does not need to be directly involved in the signal flow during activation, but serves to realize certain comfort functions through manual queries and the like.
  • the course of an activation according to the invention of a hearing aid is traced. While the hearing aid is in a sleep mode, only the primary activation unit 4 is active, which is advantageously equipped with a signal buffer 8.
  • This primary activation unit 4 as a first stage of the activation circuit is permanently active and thus in the event that the hearing aid is in sleep mode, next to the microphone 1, the only active and thus power consuming unit. Is due to this primary activation unit 4 for a certain time a certain minimum input level, which is generated by the microphone 1, the evaluation unit 5 is connected as the next stage of the activation circuit, which represents a first activation process.
  • the primary activation unit is designed such that it can monitor at least one sound-induced input level and, when a threshold value of this input level is exceeded, forward incoming signals to the evaluation unit and activate the evaluation unit.
  • the primary activation unit 4 is provided with an input signal buffer 8 which is permanently written, it is advantageous if this input signal buffer 8 is dimensioned such that it can record just as many samples of the input signal as permanently written, that the time which the primary Activation unit 4 required for detection and execution of the first activation process is bridged.
  • the second stage of the activation circuit in the form of the evaluation unit 5 no signal components are lost, but can be fully included in the signal evaluation within the evaluation unit 5, so the second stage of the activation circuit.
  • the input signal applied after the first activation process is evaluated, preferably taking into account signals to be provided from the signal buffer 8.
  • the evaluation advantageously comprises a time-dependent analysis of the frequency response of the signals applied to the evaluation unit 5. From this frequency analysis decision criteria can be derived, on which the further procedure for the activation of the hearing device depends.
  • the incoming signals contained frequencies or the time course of their occurrence thus form as time-dependent physical parameters features that are suitable for the purposes of the invention for the detection and / or classification of the incoming signals causing noise.
  • the signal processing and / or signal evaluation in the evaluation unit 5 can also be designed such that other signal parameters that permit detection and / or classification of hearing situations are derived from the input signal of the evaluation unit 5.
  • the evaluation unit 5 is designed so that it can determine at least one parameter of incoming signals, which is suitable for detecting and / or classification of the incoming signal causing noise and if the at least one of the evaluation 5 suggests certain parameters to be audible to the wearer of the hearing aid who can activate the main activation unit 6.
  • implementation of the invention does not depend on the type of parameter or characteristic to be determined, but on its suitability for the most unambiguous recognition and / or classification of a sound causing the incoming signals, although in particular physical parameters are particularly well suited.
  • the frequency-analytical evaluation of the signals by the evaluation unit 5 enables a comparison of the tf pattern (time-frequency pattern) obtained from the evaluated signals with prototypes of tf patterns stored locally in a memory 9 of the evaluation unit 5. Similar to speech recognition systems, for this purpose known acoustic situations are analyzed and the obtained tf patterns are stored so as to be retrievable for comparison with tf patterns which are later obtained in acoustic situations to be analyzed.
  • the prototype tf patterns stored in the memory 9 of the evaluation unit 5 in the present invention characterize acoustic situations in which the activation of the hearing aid is to be initiated.
  • the amount of the stored prototype t-f patterns can be composed here of patterns specified by the manufacturer, which can be supplemented by t-f patterns to be supplemented or trained individually by the hearing aid wearer.
  • manufacturer-specified t-f pattern may include a typical telephone ringing, typical Weckererklingelge Hursche, typical speech patterns and / or music patterns that may be caused for example by a clock radio, human voices and the like.
  • the recognition accuracy is to be improved in the respective environment of the hearing aid wearer by supplementing or replacing the manufacturer-defined t-f patterns with their own t-f patterns that can be recorded in the real environment of the hearing aid wearer.
  • a voice recognition is particularly advantageous if it is provided that by briefly responding to the hearing aid this is to be put on the recognition of one's own voice immediately in the active operating mode.
  • Other typical sounds are advantageously included in the tf pattern for activation if they are to entail certain actions of the hearing aid wearer.
  • the recognition of a tf pattern caused by the snoring of the hearing aid wearer may cause the snorer to suddenly perceive his snoring after the activation of the hearing aid and thereby wake up and / or consciously or unconsciously changed his sleeping posture so that snoring stops in the future.
  • the targeted reinforcement of the dog's bark can cause the hearing aid wearer to wake up and execute his dog accordingly to avoid hygienically precarious situations, which is analogously applicable to communication with other domestic animals living in the household of the hearing aid wearer, in particular cats.
  • An advantage over speech recognition systems is the relatively limited number of t-f patterns to be stored, which is why a relatively small memory 9 within the evaluation unit 5 is sufficient, which in turn is associated with a low energy requirement of the evaluation unit 5. It is particularly advantageous if the hearing device wearer can select the desired activation pattern from the sample reservoir. Then t-f patterns held by the manufacturer can be deselected if the hearing device wearer judges their relevance for his personal situation to be low. This provides additional space for recording individually favored t-f patterns.
  • the evaluation unit 5 of the hearing aid generally causes an activation when a predetermined minimum level is applied for a certain minimum time.
  • This minimum level may be specified by the manufacturer or adjusted by the respective user of the hearing aid. This is always important when a relatively high level is applied for a long time, without a stored tf pattern having a sufficient similarity to the non-analyzable tf pattern of the input signal at the evaluation unit 5, but necessary for the activation.
  • the integral of the input signal over time thus forms, in this case, a further threshold value, at which an unconditional activation of the hearing aid takes place.
  • the determination of this threshold takes place in a way that at least a sufficient time elapses, in which a detection of stored tf pattern can be done by a performed in the evaluation unit 5 comparison operation.
  • the integral of the input signal will be determined over a much longer period of time than is necessary to identify a noise. This is only deviated if a very high level of the input signal is present and an immediate activation is required.
  • the activation of the hearing device which depends on the exceeding of a first threshold value of a sound-induced input level thus always forms, in this exemplary embodiment, a form of activation which is also dependent on identified t-f patterns or a further threshold value.
  • fulfillment of the activation criteria and a successful activation of the operation of the hearing aid is not necessarily bound to a permanent presence of the activation criteria. For example, it is sufficient merely to cyclically initiate a check as to whether predetermined activation criteria are still fulfilled. A fluttering activation can thus be excluded.
  • the hearing aid wearer can possibly even clarify the cause of the longer-lasting noise and remedy the situation or store a typical tf pattern in the memory 9 of the activation unit 5 which is not yet taken into consideration Include the menu for testing the need for full activation of the hearing aid.
  • the evaluation unit 5 deactivates again as the second stage of the activation circuit.
  • An exemplary signal for the latter case is clothing, bedding and / or hair scrubbing during a movement of the hearing aid wearer during sleep, if this noise does not continue for the predetermined minimum time, since no tf pattern is preferably stored in memory 9 of the evaluation unit for such noises ,
  • the main activation unit 6 forms the third stage of the activation circuit according to the invention. If the evaluation unit 5 recognizes a reason for activation in the manner described, a noise is detected or at least classified via a high degree of correspondence between tf patterns stored in the memory 9 and the time-dependent frequency profile of the respective incoming signal, which noise can be perceived by the wearer of the hearing aid should, the main activation unit 6 is activated itself.
  • the hearing aid is turned on hard.
  • the hearing aid is raised slowly, d. H. the amplification of incoming acoustic signals is raised to a set point over a period of time, for example within a few seconds. This allows the hearing aid wearer to gradually get used to the environmental level then acting on him. This is particularly important if the activation of the hearing aid is carried out in rest periods of the hearing aid wearer in order to avoid frightening situations.
  • the main activation unit 6 represents the actual switching element in the activation of the hearing aid.
  • the decision on the operation, ie the activation, this Switching element is prepared in two stages in the upstream modules, namely in the primary activation unit 4 by a constantly available relatively non-specific but power-saving level monitoring and in the evaluation by the operated with higher energy demand signal analysis and case distinction, but only temporarily must be active.
  • the primary activation unit 4, the evaluation unit 5 and the main activation unit 6 thus form a three-stage activation circuit, with the aid of which it is possible to operate a hearing aid in a power-saving and comfortable manner without ever acoustically decoupling the hearing aid wearer from the environment.
  • the inventive three-stage activation circuit is supplemented by a fourth stage 7 of the activation circuit, can be implemented via the parallel activation requirements or certain comfort functions, in particular by manual intervention of the hearing aid wearer.
  • a manually effected activation process can be realized by direct connection of the fourth stage 7 of the activation circuit to the signal processing and amplification circuit 2 or by activation of the main activation stage 6 by the fourth stage 7 of the activation circuit.
  • a repeat request can be realized via this fourth stage.
  • the sound event can be interrogated, which is why the hearing device has been activated.
  • This is particularly advantageous if a leading to the activation of the hearing aid signal is applied only briefly and so would escape the attention of a hearing aid wearer despite activation according to the invention.
  • the signal leading to the activation is stored in the signal buffer 8, which is realized in the present case in the form of a digital memory, this signal can also be subsequently retrieved by the hearing device wearer.
  • this signal can also be subsequently retrieved by the hearing device wearer.
  • the actual signal is not played again, but only the category into which the sound event obviously classified by the evaluation unit 5 has fallen is disclosed.
  • This information can be transmitted as an abstract output. For example, the number of a stored prototype t-f pattern that has been classified by the evaluation unit 5 can be output.
  • the output itself can be done, for example, optically via a remote control or acoustically via an announcement text that is recorded by the hearing aid.
  • the activation according to the invention can be used particularly advantageously in hearing aid systems in which both ears of a hearing aid wearer are equipped with a hearing aid.
  • This coupling is preferably realized wirelessly.
  • the other device receives the activation request via the coupling. This is advantageous, for example, if the hearing aid wearer is lying on an ear and thus the associated hearing aid is acoustically shielded, which makes the monitoring of the input level according to the invention more difficult. Activation would not be possible or very unreliable in this situation for this hearing aid without binaural coupling.
  • both hearing aids of the binaurally coupled hearing aid system are equipped with the activation circuit according to the invention, at least one of the two hearing aids can be activated when corresponding noises occur.
  • the other hearing aid is then directly by an activation signal that is received and / or evaluated by the fourth stage 7 of the activation circuit activated.
  • the fourth stages 7 of the activation circuits can advantageously each have a transmitting and receiving unit 10, which can receive or send corresponding activation signals.
  • the signal paths shown by arrows between and to the individual components of the hearing aid can advantageously also comprise wireless communication links.
  • individual stages of the activation circuit according to the invention can also be accommodated in external auxiliary devices which in the context of the invention are to be regarded as part of a hearing device or hearing aid system, as is the case, for example, with remote controls.
  • Fig. 2 shows a schematic representation of a multi-component embodiment of a hearing aid according to the invention. It includes a component 11 to be arranged on or in the ear of a hearing aid wearer and an external auxiliary device 12 in the form of a remote control.
  • the multi-stage activation circuit according to the invention is distributed in this case to the two components 11 and 12. This provides an additional relief of the power supply of the ear near-carrying component 11, since external accessories have their own and less critical designed power supply. It is crucial that all components in analogy to the illustrated embodiment in Fig. 1 can communicate with each other in terms of circuitry, which may require consideration of the range of comprehensive wireless communication links for externally placed components.
  • the primary activation unit 4, the evaluation unit 5 and the fourth stage 7 of the activation circuit are components of the remote control.
  • the main activation unit 6 must be firmly connected to the actual hearing device, that is to say a component 11 to be worn on or in the ear.
  • the external accessory 12 in the form of a remote control also has its own microphone 13. This allows the signal analysis according to the invention, so make the first two activation steps completely in the remote control. Only upon fulfillment of the activation criteria is the establishment of a communication connection to the third stage of the activation circuit, ie the main activation unit 6 on the component 11 at the ear of the hearing aid wearer, after which the complete activation of the hearing aid is made.
  • the external microphone 13 also realize a particularly high activation security, which is otherwise only in binaural hearing aid systems.
  • each component 11 comprises at least means, for example in the form of a transmitting and receiving unit 10, which, in the case of activation, emit an activation signal and / or can receive an activation signal and, in the case of a received activation signal, can effect the activation of the hearing aid, thus providing a coupled activation of the components 11.
  • Activation of at least individual hearing device components can thus be initiated via the reception of such an activation signal without a noise having to be detected or classified, since an activation signal is received which indicates the activation of a further hearing device or a further hearing device component.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Telephone Function (AREA)
EP08104589A 2007-07-04 2008-07-04 Appareil auditif avec circuit d'activation multi-niveaux et son procédé de fonctionnement Active EP2012557B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007030961A DE102007030961B3 (de) 2007-07-04 2007-07-04 Hörgerät mit mehrstufiger Aktivierungsschaltung und Verfahren zu seinem Betrieb

Publications (3)

Publication Number Publication Date
EP2012557A2 true EP2012557A2 (fr) 2009-01-07
EP2012557A3 EP2012557A3 (fr) 2011-03-09
EP2012557B1 EP2012557B1 (fr) 2012-12-26

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US (1) US8126174B2 (fr)
EP (1) EP2012557B1 (fr)
DE (1) DE102007030961B3 (fr)
DK (1) DK2012557T3 (fr)

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WO2014049455A1 (fr) * 2012-09-27 2014-04-03 Siemens Medical Instruments Pte. Ltd. Système auditif ainsi que procédé de transmission
US8891793B1 (en) 2009-06-26 2014-11-18 Starkey Laboratories, Inc. Remote control for a hearing assistance device
EP2894881A1 (fr) * 2014-01-10 2015-07-15 Samsung Electronics Co., Ltd Appareil et procédé permettant de réduire la consommation d'énergie dans un dispositif auditif
US9161139B2 (en) 2009-05-08 2015-10-13 Starkey Laboratories, Inc. Method and apparatus for detecting cellular telephones for hearing assistance devices
US9402142B2 (en) 2010-04-13 2016-07-26 Starkey Laboratories, Inc. Range control for wireless hearing assistance device systems
US9420387B2 (en) 2009-12-21 2016-08-16 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US9420385B2 (en) 2009-12-21 2016-08-16 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US9774961B2 (en) 2005-06-05 2017-09-26 Starkey Laboratories, Inc. Hearing assistance device ear-to-ear communication using an intermediate device
US9854369B2 (en) 2007-01-03 2017-12-26 Starkey Laboratories, Inc. Wireless system for hearing communication devices providing wireless stereo reception modes
US10003379B2 (en) 2014-05-06 2018-06-19 Starkey Laboratories, Inc. Wireless communication with probing bandwidth
US10051385B2 (en) 2006-07-10 2018-08-14 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals

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DE102009019594A1 (de) * 2009-04-30 2010-07-22 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit Hinweissignalausgabe und Verfahren zum Betreiben einer Hörvorrichtung
DE102011087569A1 (de) * 2011-12-01 2013-06-06 Siemens Medical Instruments Pte. Ltd. Verfahren zum Anpassen einer Hörvorrichtung durch eine formale Sprache
US10231056B2 (en) 2014-12-27 2019-03-12 Intel Corporation Binaural recording for processing audio signals to enable alerts
US9949878B2 (en) 2015-03-11 2018-04-24 Honeywell International Inc. System and method to automatically switch on and switch off device for accurate recording of personal sound exposure measurements
US20160345088A1 (en) * 2015-05-21 2016-11-24 Nokia Technologies Oy Controllably actuable fabric and associated method and apparatus for controlling the fabric
GB201510032D0 (en) * 2015-06-09 2015-07-22 Kp Acoustics Ltd Integrated sensor system
TWI612820B (zh) * 2016-02-03 2018-01-21 元鼎音訊股份有限公司 助聽器通訊系統及其助聽器通訊之方法

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WO2001020965A2 (fr) 2001-01-05 2001-03-29 Phonak Ag Procede de determination d'une situation d'environnement acoustique momentanee, utilisation de ce procede, et prothese auditive
US20040131214A1 (en) 2002-08-21 2004-07-08 Galler Bernard A. Digital hearing aid battery conservation method and apparatus
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US8169938B2 (en) 2005-06-05 2012-05-01 Starkey Laboratories, Inc. Communication system for wireless audio devices
US9774961B2 (en) 2005-06-05 2017-09-26 Starkey Laboratories, Inc. Hearing assistance device ear-to-ear communication using an intermediate device
US11064302B2 (en) 2006-07-10 2021-07-13 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals
US11678128B2 (en) 2006-07-10 2023-06-13 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals
US10051385B2 (en) 2006-07-10 2018-08-14 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals
US10469960B2 (en) 2006-07-10 2019-11-05 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals
US10728678B2 (en) 2006-07-10 2020-07-28 Starkey Laboratories, Inc. Method and apparatus for a binaural hearing assistance system using monaural audio signals
US10511918B2 (en) 2007-01-03 2019-12-17 Starkey Laboratories, Inc. Wireless system for hearing communication devices providing wireless stereo reception modes
US9854369B2 (en) 2007-01-03 2017-12-26 Starkey Laboratories, Inc. Wireless system for hearing communication devices providing wireless stereo reception modes
US11218815B2 (en) 2007-01-03 2022-01-04 Starkey Laboratories, Inc. Wireless system for hearing communication devices providing wireless stereo reception modes
US11765526B2 (en) 2007-01-03 2023-09-19 Starkey Laboratories, Inc. Wireless system for hearing communication devices providing wireless stereo reception modes
US9161139B2 (en) 2009-05-08 2015-10-13 Starkey Laboratories, Inc. Method and apparatus for detecting cellular telephones for hearing assistance devices
US9439006B2 (en) 2009-06-26 2016-09-06 Starkey Laboratories, Inc. Remote control for a hearing assistance device
US8891793B1 (en) 2009-06-26 2014-11-18 Starkey Laboratories, Inc. Remote control for a hearing assistance device
US10212682B2 (en) 2009-12-21 2019-02-19 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US9426586B2 (en) 2009-12-21 2016-08-23 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US9420385B2 (en) 2009-12-21 2016-08-16 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US9420387B2 (en) 2009-12-21 2016-08-16 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
US11019589B2 (en) 2009-12-21 2021-05-25 Starkey Laboratories, Inc. Low power intermittent messaging for hearing assistance devices
EP2378794A1 (fr) * 2010-04-13 2011-10-19 Starkey Laboratories, Inc. Contrôle de modes basse consommation ou veille d'un dispositif d'aide auditive
US9402142B2 (en) 2010-04-13 2016-07-26 Starkey Laboratories, Inc. Range control for wireless hearing assistance device systems
US8804988B2 (en) 2010-04-13 2014-08-12 Starkey Laboratories, Inc. Control of low power or standby modes of a hearing assistance device
US9570089B2 (en) 2012-09-27 2017-02-14 Sivantos Pte. Ltd. Hearing system and transmission method
WO2014049455A1 (fr) * 2012-09-27 2014-04-03 Siemens Medical Instruments Pte. Ltd. Système auditif ainsi que procédé de transmission
US9820060B2 (en) 2014-01-10 2017-11-14 Samsung Electronics Co., Ltd. Apparatus and method for reducing power consumption in hearing aid
EP2894881A1 (fr) * 2014-01-10 2015-07-15 Samsung Electronics Co., Ltd Appareil et procédé permettant de réduire la consommation d'énergie dans un dispositif auditif
US10003379B2 (en) 2014-05-06 2018-06-19 Starkey Laboratories, Inc. Wireless communication with probing bandwidth

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US8126174B2 (en) 2012-02-28
US20090010464A1 (en) 2009-01-08
DK2012557T3 (da) 2013-04-08
EP2012557A3 (fr) 2011-03-09
EP2012557B1 (fr) 2012-12-26

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