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EP2043388B1 - Mise en marche et arrêt totalement automatique pour appareils auditifs - Google Patents

Mise en marche et arrêt totalement automatique pour appareils auditifs Download PDF

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Publication number
EP2043388B1
EP2043388B1 EP08105226.8A EP08105226A EP2043388B1 EP 2043388 B1 EP2043388 B1 EP 2043388B1 EP 08105226 A EP08105226 A EP 08105226A EP 2043388 B1 EP2043388 B1 EP 2043388B1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
signal
field strength
hearing
received
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.)
Active
Application number
EP08105226.8A
Other languages
German (de)
English (en)
Other versions
EP2043388A2 (fr
EP2043388A3 (fr
Inventor
Jürgen Reithinger
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Original Assignee
Siemens Audioligische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP2043388A2 publication Critical patent/EP2043388A2/fr
Publication of EP2043388A3 publication Critical patent/EP2043388A3/fr
Application granted granted Critical
Publication of EP2043388B1 publication Critical patent/EP2043388B1/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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
    • 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

Definitions

  • the invention relates to a hearing aid device system having a first and a second, in each case in an ear of a user portable hearing aid, each having an input transducer for receiving an input signal and conversion to an electrical input signal, a signal processing unit for processing and amplification of the electrical input signal and delivery of a electrical output signal, an output transducer for converting the electrical output signal into a perceptible by the user as an acoustic signal output signal and means for wireless signal transmission between the hearing aids comprise.
  • the invention relates to a method for operating such a hearing aid device system.
  • Hearing aids usually have to turn on and off a manually operable switch.
  • this switch is integrated into the battery compartment so that the hearing aid is turned off as soon as the user slightly swings the battery compartment out of the normal operating position.
  • the signal processing device of a respective acoustic system comprises a high-frequency detector (HFD) for analyzing an input signal whose output signal is usable for processing one or more input signals by the signal processing. Specifically, this can detect the presence of an active mobile phone that emits electromagnetic radiation in the high frequency range. As a result, it is possible to switch to a telephone mode with high security in accordance with the situation.
  • HFD high-frequency detector
  • Object of the present invention is to realize an automatic on and / or off in a hearing aid device with two head-worn hearing aids.
  • an input signal is received by means of an input transducer and in an electrical input signal transferred.
  • an input transducer usually serves as an input transducer at least one microphone, which receives an acoustic input signal and converts into an electrical 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.
  • telephone coils or antennas for receiving wirelessly transmitted input signals and conversion into electrical input signals are also common as input transducers.
  • 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 user usually in response to the signal frequency of the input signal.
  • the signal processing unit supplies at its output an electrical output signal, which is supplied 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 transducer conventionally earphones 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.
  • controls on / off switch, program switch, volume control, etc. may be present.
  • a hearing aid of a hearing aid device comprises means for wireless signal transmission between the hearing aids, for example, realized by a signal transmission and control unit in conjunction with a transmitting and receiving coil, which are present in both hearing aids.
  • the invention provides for determining the field strength of a received signal transmitted by the other hearing aid device at least in one of the two hearing aid devices, from which an indication of the instantaneous distance between the two hearing aid devices relative to one another can be obtained. If both hearing aids are worn on the head at the same time, the field strength is set so that just a safe data transmission between the hearing aids is possible. On the other hand, if the hearing aid devices are lying next to one another in a storage box, the field strength measured in the hearing aid device is many times higher. From the measured field strength, a hearing aid can thus derive the information whether it is worn on the head or whether it is in the storage box.
  • the field strength measurement may e.g. by the use of a simple Nutzsignalpegelmessers, which is integrated into one of the receiving filter stages or receiving amplifier stages of the signal transmission unit and detects a voltage value.
  • the measured field strength is compared with a threshold value. If the field strength is below the threshold, this is an indication that the two hearing aids are worn on the head. On the other hand, if the measured field strength exceeds the threshold, then this is an indication that the hearing aids are not worn on the head, but for storage close together, for example, in a storage box.
  • the relevant hearing aid device switches off automatically, for example by means of a suitable software control.
  • switched off are essential power consumers of the hearing aid, such as the input transducer, the output transducer and the signal processing processor, disconnected from the power supply.
  • the power consumption in this switched-off state is reduced in comparison to the completely switched-on hearing aid device.
  • sleep mode the hearing aid in question detects when the measured field strength falls below the threshold, whereby the hearing aid automatically and automatically turns on again.
  • the invention offers the advantage that an automatic switching on and off is achieved in the hearing aid device in question in a simple manner. It can thus be completely dispensed with a manually operable control element for switching on and off. This is particularly advantageous in the production of a waterproof hearing aid.
  • both hearing aids of the hearing aid system according to the invention have a corresponding field strength measuring device.
  • only one of the two hearing aids has a field strength measuring device and is transmitted from this hearing aid, a control signal to the other hearing aid, which then causes an automatic on and / or off in the second hearing aid.
  • the signal level of the signal received by the first hearing aid can be determined.
  • FIG. 1 1 shows a hearing aid device system with a first hearing aid device 1 that can be worn on the head of a user and a second hearing aid device 11 that can be worn on the head of a user.
  • the hearing aid devices 1 and 11 each include a microphone 2 or 12 for receiving an acoustic input signal and converting it into an electrical input signal.
  • a signal processing unit 3 or 13 is used for processing and frequency-dependent amplification of the electrical input signal.
  • the electrical output signal generated by the signal processing unit 3 or 13 is converted by an earphone 4 or 14 into an acoustic output signal and supplied to the ear of a user.
  • the signal processing in the signal processing units 3 and 13 can be adapted to different listening environments by setting a plurality of parameters.
  • hearing programs or operating modes "speech at rest”, “speech in noise”, “telephoning” etc.
  • the adjustment of the parameters of the individual hearing programs and the settings for individual compensation of the hearing loss of a user by means of the signal transmission and control units 5 and 15, to which the transmitting and receiving coils 7 and 17 are connected for wireless data transmission, in conjunction with an external programming device (not shown).
  • each have a field strength measuring device 6 and 16 are present, through which the field strength of one of the transmitting and receiving coil. 7 or 17 recorded and emanating from the transmitting and receiving coil of the other hearing aid device electromagnetic signal can be measured.
  • a relatively rough determination of the field strength is sufficient.
  • a level meter is preferably integrated in one of the transmitting and receiving coils 7 and 17 downstream receiving filter stages or receiving amplifier stages. The measured signal levels in the signal transmission and control units 5 and 15 are advantageously compared with a specific threshold value.
  • the two hearing aids 1 and 11 are located at a very small distance from each other.
  • the hearing aids 1 and 11 are therefore, controlled by the signal transmission and control units 5 and 15, switched to a sleep mode and remain in this state until the measured field strength falls below the threshold again.
  • the hearing aid is switched off, ie essential components of the hearing aid such as the microphones 2 and 12, the signal processing units 3 and 13 and the earphones 4 and 14 are separated from the voltage source 8 and 18 respectively.
  • the signal transmission between the hearing aids in sleep mode does not follow permanently but only at certain times, for example in the form of short pulses which are repeated periodically in the second range.
  • a synchronization of the hearing aids 1 and 11 is required.
  • both hearing aids 1 and 11 have a quartz control for this, so that a relatively good synchronization of the two hearing aids anyway 1 and 11 is given.
  • the signals transmitted between the hearing aids can also be used for synchronization and in particular for fine adjustment during synchronization.
  • the invention has the advantage that in the hearing aid devices 1 and 11, which are provided for a wireless signal transmission, an automatic switching on and off of the hearing aid devices is realized with relatively little additional effort. Also, corresponding controls for manually switching on and off the hearing aids can therefore be dispensed with. This allows further miniaturization of the devices and increases the ease of use. Furthermore, the lack of control elements will facilitate the production of a waterproof hearing aid.
  • FIG. 2 shows an example of a flowchart for automatically switching on and off a hearing aid according to the invention.
  • a received from the other hearing aid of the hearing aid device concerned electromagnetic signal is received permanently or at certain times by the hearing aid, which advantageously takes place based on the received signal, a synchronization of the two hearing aids.
  • the field strength of the electromagnetic signal received by the hearing aid is determined and compared with a threshold value. If the measured field strength is lower than the threshold, then the hearing aid is in normal operation and thus in the on state. However, if the measured field strength exceeds the threshold value, then the hearing aid device is in sleep mode, ie in the switched-off state, in which at least substantially only the components required for the wireless signal transmission are operated. This state is maintained until the measured field strength of the received electromagnetic signal falls below the threshold again.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Mobile Radio Communication Systems (AREA)
  • Near-Field Transmission Systems (AREA)

Claims (21)

  1. Système de prothèse auditive comprenant une première et une deuxième prothèses ( 1, 11 ) auditives qui peuvent être portées respectivement dans ou sur une oreille d'un utilisateur, et qui comprennent respectivement un transducteur d'entrée pour la réception d'un signal d'entrée et sa transformation en un signal d'entrée électrique, une unité ( 3, 13 ) de traitement du signal pour le traitement et l'amplification du signal d'entrée électrique et pour l'émission d'un signal de sortie électrique, un transducteur de sortie pour la transformation du signal de sortie électrique en un signal de sortie perceptible par l'utilisateur comme signal acoustique et des moyens ( 5, 7 ; 15, 17 ) pour la transmission sans fil du signal entre les prothèses ( 1, 11 ) auditives, caractérisé en ce qu'au moins la première prothèse ( 1 ) auditive comprend des moyens de branchement et/ou de débranchement automatique de la première prothèse ( 1 ) auditive, en fonction de l'intensité du champ avec laquelle un signal, transmis sans fil de la deuxième prothèse ( 11 ) auditive à la première prothèse ( 1 ) auditive, est reçu dans la première prothèse auditive.
  2. Système de prothèse auditive suivant la revendication 1, dans lequel, pour le branchement et/ou le débranchement automatique, l'intensité du champ du signal reçu dans la première prothèse ( 1 ) auditive ou une grandeur dépendant de l'intensité du champ peut être déterminée au moins approximativement par la première prothèse ( 1 ) auditive.
  3. Système de prothèse auditive suivant la revendication 2, dans lequel l'intensité du champ mesurée ou la grandeur qui dépend de l'intensité du champ peut être comparée dans la première prothèse ( 1 ) auditive à une première valeur de seuil et la première prothèse ( 1 ) auditive se débranche automatiquement, si l'intensité du champ ou si la grandeur qui dépend de l'intensité du champ dépasse la première valeur de seuil.
  4. Système de prothèse auditive suivant la revendication 2, dans lequel l'intensité du champ mesurée ou la grandeur qui en dépend peut être comparée dans la première prothèse ( 1 ) auditive à une deuxième valeur de seuil et la première prothèse ( 1 ) auditive se branche automatiquement, si l'intensité du champ ou la grandeur qui en dépend devient inférieure à la deuxième valeur de seuil.
  5. Système de prothèse auditive suivant l'une des revendications 1 à 4, dans lequel un signal de commande peut être transmis de la première prothèse ( 1 ) auditive à la deuxième prothèse ( 11 ) auditive pour brancher et/ou débrancher automatiquement la deuxième prothèse ( 11 ) auditive, en étant commandé par la première prothèse ( 1 ) auditive.
  6. Système de prothèse auditive suivant l'une des revendications 1 à 5, dans lequel les prothèses ( 1, 11 ) auditives peuvent être synchronisées.
  7. Système de prothèse auditive suivant la revendication 6, dans lequel, dans un mode dormant des prothèses ( 1, 11 ) auditives, un signal peut être transmis de la deuxième prothèse ( 11 ) auditive à la première prothèse ( 1 ) auditive et l'intensité du champ du signal reçu dans la première prothèse ( 1 ) auditive ou une grandeur qui dépend de l'intensité du champ peut être déterminée dans la première prothèse ( 1 ) auditive.
  8. Système de prothèse auditive suivant la revendication 7, dans lequel la deuxième prothèse ( 11 ) auditive envoie, au moins dans le mode dormant, seulement dans des intervalles de temps déterminés, un signal à la première prothèse ( 1 ) auditive et la première prothèse ( 1 ) auditive ne se branche, dans un mode de réception, pour la réception du signal envoyé par la deuxième prothèse ( 11 ) auditive que dans ces intervalles de temps.
  9. Système de prothèse auditive suivant l'une des revendications 3 à 8, dans lequel la première prothèse ( 1 ) auditive comprend un mesureur de niveau pour la détermination du niveau du signal reçu dans la première prothèse ( 1 ) auditive ou d'un signal qui en provient.
  10. Système de prothèse auditive suivant la revendication 9, dans lequel le mesureur de niveau est intégré dans un étage de filtre de réception ou dans un étage d'amplificateur de réception de la première prothèse ( 1 ) auditive.
  11. Système de prothèse auditive suivant l'une des revendications 1 à 10, dans lequel aucune des deux prothèses ( 1, 11 ) auditives ne comprend un dispositif pouvant être actionné manuellement de branchement et/ou de débranchement de la prothèse ( 1, 11 ) auditive respective.
  12. Procédé pour faire fonctionner un système de prothèse auditive, comprenant une première et une deuxième prothèses ( 1, 11 ) auditives, pouvant être portées respectivement sur ou dans une oreille d'un utilisateur, dans lesquelles respectivement un signal d'entrée est reçu et est transformé en un signal d'entrée électrique, le signal d'entrée électrique étant traité et amplifié et un signal de sortie électrique étant produit, le signal de sortie électrique étant transformé en un signal de sortie perceptible par l'utilisateur comme signal acoustique et un signal étant transmis sans fil entre les prothèses ( 1, 11 ) auditives, caractérisé en ce qu'au moins la première prothèse ( 1 ) auditive est branchée et/ou débranchée automatiquement, en fonction de l'intensité du champ avec laquelle un signal transmis sans fil de la deuxième prothèse ( 11 ) auditive à la première ( 1 ) auditive est reçu dans la première prothèse ( 1 ) auditive.
  13. Procédé suivant la revendication 12, dans lequel, pour le branchement et/ou le débranchement automatique, l'intensité du champ du signal reçu dans la première prothèse ( 1 ) auditive ou d'une grandeur qui en dépend est déterminée au moins approximativement dans la première prothèse ( 1 ) auditive.
  14. Procédé suivant la revendication 12 ou 13, dans lequel l'intensité du champ ou la grandeur qui en dépend est comparée à une valeur de seuil et la première prothèse ( 1 ) auditive est débranchée si l'intensité du champ ou si la grandeur dépasse la valeur de seuil.
  15. Procédé suivant la revendication 12 ou 13, dans lequel l'intensité du champ ou la grandeur qui en dépend est comparée à une valeur de seuil et la première prothèse ( 1 ) auditive est branchée si l'intensité du champ ou la grandeur devient inférieure à la valeur du seuil.
  16. Procédé suivant l'une des revendications 12 à 15, dans lequel, en fonction de l'intensité du champ, un signal de commande est produit dans la première prothèse ( 1 ) auditive et est transmis à la deuxième prothèse ( 11 ) auditive pour le branchement et/ou le débranchement automatique de la deuxième prothèse ( 11 ) auditive commandé par la première prothèse ( 1 ) auditive.
  17. Procédé suivant l'une des revendications 12 à 16, dans lequel les prothèses ( 1, 11 ) auditives sont synchronisées par le signal transmis de la deuxième prothèse ( 11 ) auditive à la première prothèse ( 1 ) auditive.
  18. Procédé suivant l'une des revendications 12 à 17, dans lequel, dans un mode dormant des prothèses ( 1, 11 ) auditives, un signal est transmis de la deuxième prothèse ( 11 ) auditive à la première prothèse ( 1 ) auditive et l'intensité du champ du signal reçu dans la première prothèse ( 1 ) auditive ou une grandeur qui en dépend est déterminée dans la première prothèse ( 1 ) auditive.
  19. Procédé suivant la revendication 18, dans lequel la deuxième prothèse ( 11 ) auditive envoie, au moins dans le mode dormant, seulement dans des intervalles de temps déterminés, un signal à la première prothèse ( 1 ) auditive et la première prothèse ( 1 ) auditive n'est mise dans un mode de réception, pour la réception du signal envoyé par la deuxième prothèse ( 11 ) auditive, que pendant ces intervalles de temps.
  20. Procédé suivant la revendication 18 ou 19, dans lequel la première prothèse ( 1 ) auditive n'est mise dans un mode de réception, pour la réception du signal envoyé par la deuxième prothèse ( 11 ) auditive, que pendant des intervalles de temps déterminés.
  21. Procédé suivant l'une des revendications 12 à 20, dans lequel on détermine, dans la première prothèse ( 1 ) auditive, comme grandeur dépendant de l'intensité du champ du signal reçu, le niveau d'un signal provenant du signal reçu.
EP08105226.8A 2007-09-28 2008-09-04 Mise en marche et arrêt totalement automatique pour appareils auditifs Active EP2043388B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007046437A DE102007046437B4 (de) 2007-09-28 2007-09-28 Vollautomatisches Ein-/Ausschalten bei Hörhilfegeräten

Publications (3)

Publication Number Publication Date
EP2043388A2 EP2043388A2 (fr) 2009-04-01
EP2043388A3 EP2043388A3 (fr) 2013-07-31
EP2043388B1 true EP2043388B1 (fr) 2014-12-17

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Country Status (5)

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US (1) US8130990B2 (fr)
EP (1) EP2043388B1 (fr)
CN (1) CN101400014B (fr)
DE (1) DE102007046437B4 (fr)
DK (1) DK2043388T3 (fr)

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SG184255A1 (en) * 2010-05-21 2012-11-29 Widex As Automatic power-off of hearing aid
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DK3306955T3 (da) * 2016-10-10 2019-08-19 Oticon Medical As Høreapparat der omfatter en automatisk afbryder
EP3606100B1 (fr) 2018-07-31 2021-02-17 Starkey Laboratories, Inc. Commande automatique de fonctions binaurales dans des dispositifs portables à l'oreille
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Also Published As

Publication number Publication date
DE102007046437A1 (de) 2009-04-23
EP2043388A2 (fr) 2009-04-01
DK2043388T3 (en) 2015-03-30
CN101400014A (zh) 2009-04-01
US20090087005A1 (en) 2009-04-02
EP2043388A3 (fr) 2013-07-31
US8130990B2 (en) 2012-03-06
CN101400014B (zh) 2016-05-18
DE102007046437B4 (de) 2009-07-30

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