EP0712263B1 - Prothèse auditive programmable - Google Patents

Prothèse auditive programmable Download PDF

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Publication number
EP0712263B1
EP0712263B1 EP19940117797 EP94117797A EP0712263B1 EP 0712263 B1 EP0712263 B1 EP 0712263B1 EP 19940117797 EP19940117797 EP 19940117797 EP 94117797 A EP94117797 A EP 94117797A EP 0712263 B1 EP0712263 B1 EP 0712263B1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
signals
aid according
neural structure
hearing
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Revoked
Application number
EP19940117797
Other languages
German (de)
English (en)
Other versions
EP0712263A1 (fr
Inventor
Oliver Dipl.-Ing. Weinfurtner
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
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Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Priority to DE59410236T priority Critical patent/DE59410236D1/de
Priority to DK94117797T priority patent/DK0712263T3/da
Priority to EP19940117797 priority patent/EP0712263B1/fr
Publication of EP0712263A1 publication Critical patent/EP0712263A1/fr
Application granted granted Critical
Publication of EP0712263B1 publication Critical patent/EP0712263B1/fr
Anticipated expiration legal-status Critical
Revoked legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H04R25/507—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing implemented by neural network or fuzzy logic
    • 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
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the invention relates to a programmable hearing aid with an amplifier and transmission part which can be adjusted in terms of its transmission properties between the microphone and the listener to different transmission characteristics.
  • a programmable hearing aid is known with an amplifier and transmission part which can be adjusted in terms of its transmission properties between the microphone and the listener to different transmission characteristics.
  • Several different transmission functions are stored in a memory of a control unit and can be selected by a user to adapt the hearing aid to an acoustic environment.
  • a simulator is known from EP 0 540 168 A2 in which the properties of a device to be controlled, e.g. for water supply, are modeled.
  • the simulator comprises a neural network which can be learned in relation to a real control parameter of the simulated device. This improves the quality of the simulation of the real device.
  • a solar-powered battery charger for rechargeable hearing aid batteries is known from US Pat. No. 5,253,300. Contacts on the charger and on the housing of the hearing aid allow recharging without removing the batteries from the hearing aid housing possible.
  • One embodiment of the charger comprises a device that monitors the state of charge of the battery.
  • EP-A-0 064 042 eight parameter sets for different transmission characteristics for different environmental situations are stored in a hearing device memory.
  • the various parameter sets for the eight stored programs can be called up one after the other by pressing a switch.
  • a control unit controls a signal processor connected between the microphone and the handset, which then sets a first transmission function intended for an intended environmental situation.
  • the stored signal transmission programs can only be called up one after the other via the switch until, in the opinion of the hearing device wearer, the transmission function that is just right for the given environmental situation has been found.
  • EP-B-0 064 042 an automatic switchover to another transfer function should also be provided if the user comes from a noisy environment to a quiet environment, for example, or vice versa.
  • this switchover should take place cyclically like the manual switchover. If you want to set other than the stored transfer functions, the non-volatile memory must be erased by an external programming unit and re-programmed by this. In this way, it is also possible to adapt the programmable hearing aid to changing hearing damage.
  • a plurality of parameter sets so-called hearing situations, which can be selected by the user, are generally stored.
  • Each of these parameter sets represents the sensibly coordinated setting of all signal processing parameters for a specific acoustic situation, e.g. at rest, i.e. without disturbing background noise or a conversation situation with low-frequency noise, etc.
  • the hearing aid wearer selects the desired situation by pressing a button on the hearing aid.
  • the object of the invention is to provide a hearing aid which is characterized by a control system which enables the desired automatic or largely automatic adaptation dependent on input or measurement signals.
  • this object is achieved in a programmable hearing device of the type mentioned at the outset by a neural structure which is associated with the signal path from the microphone to the listener and to which a data carrier is assigned, signals being tapped from the signal path from one or more tapping points and fed to a module for signal processing and the processed signals can be fed to the neural structure, which generates control signals for the automatic signal-dependent selection of hearing situations stored in the data memory.
  • the neural structure forms a controller for the automatic signal-dependent selection of hearing situations stored in the data memory.
  • An essential feature of the hearing device according to the invention is therefore a controller based on the principle of the neural structures for the automatic signal-dependent selection of hearing situations or for setting individual signal processing parameters in the hearing device. This basic principle allows any selection behavior to be set. Analog circuit technology lends itself to the implementation of the principle of neural structures in terms of circuitry.
  • the hearing aid 1 shown schematically in FIG. 1, records 2 sound signals via a microphone. This acoustic information is converted into electrical signals in the microphone. After signal processing in an amplification and transmission part 4, the electrical signal is fed to a receiver 3 as an output converter.
  • signals 8 are tapped from the signal path of the hearing device 1 between its microphone 2 and its receiver 3 at certain, desired tapping points. These signals 8 are fed to a neural structure 5 arranged next to the signal path in the hearing aid.
  • the signals 8 first arrive at a module 9 for signal processing and from its outputs processed signals 10, 10 ', 10 '' of the neural structure 5.
  • a data carrier 6 is assigned to the neural structure 5, in which configuration information of the neural structure is stored. Taking into account the configuration information of the data carrier 6, the neural structure 5 generates control signals 11 from the processed signals 10, 10 ′, 10 ′′, which can be fed to the amplifier and transmission part 4 in order to adapt its transmission characteristics.
  • These control signals 11 can be used to select parameters of the amplifier and transmission part stored in a data memory 12 assigned to the signal path of the hearing aid or to change the amplifier and transmission characteristics to the amplifier and transmission part 4.
  • 7 signals are tapped from the signal path of the hearing aid at all relevant points or tapping points and processed in a suitable manner. These processed signals and any other system information, e.g. whether microphone or telephone operation is desired are added to the "Neural Structure" block.
  • the outputs of the controller are signals which effect the setting of the listening situations or which represent the setting variables of individual signal processing parameters.
  • the behavior of the controller does not necessarily have to be unchangeable (i.e. completely described by the hardware structure), but can be configurable (e.g. by programming). Configuration information of the controller can be stored in a memory in the hearing aid.
  • the neural structure 5 forms a controller for the automatic setting of individual signal processing parameters of the amplifier and transmission part 4.
  • means 13 are provided for detecting system states of the hearing aid 1, the output signals 14 of which can be fed to the module 9 for signal processing and / or the neural structure 5, these output signals being able to be taken into account when generating the control signals 11.
  • Control elements which can be actuated by the hearing aid wearer such as switches, buttons, potentiometers or the like, can be provided as means 13 for detecting system states of the hearing aid 1.
  • the hearing aid can e.g. be equipped with a situation switch which enables the hearing aid wearer - as described at the beginning of EP-B-0 064 042 - to choose a stored transmission function which he thinks is suitable for the given environmental situation.
  • the hearing aid can e.g. have a switch for switching from microphone operation to telephone coil operation.
  • the hearing aid regularly has a volume control with which the hearing impaired influences the volume.
  • the hearing device can also be characterized in that a device 15 which monitors the state of charge of the hearing device battery, not shown, is additionally provided as a means for detecting system states of the hearing device 1. Thereafter, it is possible that the respective state of charge of the hearing aid battery is also taken into account when generating the output signals 11 of the neural structure 5 or the controller, which can also be determined for individual hearing situations and / or signal processing parameters.
  • the signals 8 are tapped from the signal paths formed by the individual channels.
  • the signals 8 from the signal paths and the output signals 14 of the means 13, 13 'for detecting system states of the hearing aid e.g. by rectification, the formation of suitable temporal averages, and possibly prepared from their derivatives.
  • signal processing - module 9 at least one input variable, e.g.
  • the signals 14 can also be fed directly to the neural structure (FIG. 2).
  • Neural structures consist of many similar elements or neurons 19. The function of the neural structure as a whole essentially depends on the way in which these neurons are interconnected.
  • the course of the output function W represents a step function at the threshold value s.
  • the output function W has a continuous course around the threshold value s.
  • FIG. 5b shows a continuous, so-called sigmoid curve of the output variable with limitation to a maximum and a minimum output value.
  • FIG. 5c shows a linear course in the transition area.
  • the signals which are processed by the neural structure can be designed as voltage signals, current signals or as frequency-variable pulse signals.
  • the signal may have to be converted into a continuous current or voltage signal and back again at some points in the neural structure with the aid of suitable circuits.
  • FIG. 6 shows the exemplary connection of three neurons 19 to the typical structure of a single-layer feedback network with the inputs e i (t) and the outputs a j (t + ⁇ T).
  • Figure 7 shows an example of the structure of a multilayer feedback-free network.
  • the function of the neural structure is to use one or the other network structure. Mixed forms of both structures are also possible.
  • the function of a neural structure as a whole is essentially determined by the network structure and by the weighting functions of the input signals on each neuron 19. These parameters can be permanently set through the implementation in terms of circuitry if constant behavior is desired. If, on the other hand, a change in behavior should be possible, some or all of these parameters must be programmable. Their respective values must then be stored in a configuration memory or data carrier 6. The individual memory elements can be arranged in a concentrated form or locally assigned to the respective neuron.
  • the stored parameters can be modified either by external programming of the memory elements and / or by an algorithm implemented in the circuit. Modification is also possible here while the neural structure is in operation.
  • Figure 8 shows an example of the circuitry implementation of a single-layer feedback network.
  • Amplifiers 24 with complementary outputs act as threshold elements.
  • the connections (synapses) between the outputs and inputs of the neurons are weighted using the guide values R ij .
  • the output signals of the amplifiers and thus the neural structure are the voltage signals U i .
  • E1 to e4 denote the inputs of the circuit and a1 to a4 denote inverting and non-inverting outputs of the circuit.
  • FIG. 9 shows a possible circuit implementation of a synapse (weighted input of a neuron) with a programmable connection strength.
  • connection strengths +1, -1 and 0 are possible and the signals to be transmitted from this synapse can only assume the logical values 0 and 1.
  • output a is independent of input e; the synapse therefore represents an interruption (connection strength 0).
  • the memory cell 25 is programmed to close the switch and the memory cell 26 to open the associated switch, then a current flows from output a (logic 1) when the input is logic 1, and no current (logic 0) if the input is logic 0.
  • the synapse acts as a connection of strength +1. If both memory cells 25, 26 are programmed inversely for this purpose, the inverse logic behavior results. The synapse then acts as a connection of strength -1. V dd indicates the circuit connection to the supply voltage in the drawing.
  • FIG. 10 shows a possible implementation of a programmable synapse with variable connection strength. It works on the principle of the multiplier.
  • the strength of the synaptic connection is stored as the difference between two analog voltage values on two capacitors 29, 30.
  • the controller 5, which is arranged next to the signal path from the microphone 2 to the receiver 3, has additional functional parts comprises, which operate according to a fuzzy logic system 20.
  • the fuzzy logic system 20 has components for fuzzification 21 and for inference formation 22 and, furthermore, an assigned decision means component 23 is designed as a neural structure.
  • the hearing aid in addition to its signal path (not shown here) from the microphone via the amplifier and transmission part to the listener, the hearing aid has a controller 5 as a neural structure with a data carrier 6 for configuration information of the controller and a signal conditioning unit 9. Signals 8 from signal path of the hearing aid are fed to signal processing unit 9.
  • the controller 5 comprises a fuzzy logic system 20 which is subdivided into a component for fuzzification 21 and a component for inference formation 22.
  • the processed signals 10, 10 ', 10''of the signal processing 9 and optionally signals 14 of the fuzzification component 21 are supplied.
  • the inference formation component 22 is connected downstream of the fuzzification component 21.
  • the further decision means component 23 of the controller 5 is then designed as a neural structure. All three components 21, 22, 23 are exchanging information with the data carrier 6.
  • the generated control signals 11 form, for example, selection signals for individual listening situations and / or signal processing parameters.
  • a further advantageous realization of the controller with a combination of the principles of the neural structures and the fuzzy logic can consist in that the implementation of the rules, which determine the regulation or selection behavior of the fuzzy logic part, is realized with the aid of a neural structure ,

Claims (14)

  1. Appareil (1) auditif programmable, comportant une partie (4) d'amplificateur et de transmission dont les propriétés de transmission entre un microphone (2) et un écouteur (3) peuvent être réglées sur diverses caractéristiques de transmission, caractérisé par une structure (5) neuronale qui est disposée à côté de la voie de signaux du microphone à l'écouteur et qui est associée à un support (6) de données, des signaux (8) étant prélevés dans la voie de signaux en un ou plusieurs points (7) de prélèvement et envoyés à un module (8) pour la préparation des signaux, et les signaux (10, 10', 10") préparés pouvant être envoyés à la structure (5) neuronale qui produit des signaux (11) de commande pour sélectionner automatiquement, en fonction des signaux, des situations d'écoute mémorisées dans une mémoire (12) de données associée à la voie de signaux.
  2. Appareil auditif suivant la revendication 1, caractérisé en ce que la structure (5) neuronale forme, conjointement avec le module (9) pour la préparation des signaux et le support (6) de données, un contrôleur pour régler automatiquement des paramètres individuels de traitement de signaux de la partie (4) d'amplificateur et de transmission.
  3. Appareil auditif suivant la revendication 1 ou 2, caractérisé en ce qu'il est présent des moyens (13) pour détecter des états de système de l'appareil (1) auditif dont les signaux (14) de sortie peuvent être envoyés au module (9) pour la préparation des signaux et/ou à la structure (5) neuronale, ces signaux de sortie pouvant être pris en compte lors de la production des signaux (11) de commande.
  4. Appareil auditif suivant la revendication 3, caractérisé en ce qu'il est présent, comme moyen (13) pour détecter des états de système de l'appareil (1) auditif, des éléments de réglage pouvant être actionnés par le porteur de l'appareil auditif, par exemple des commutateurs, des boutons poussoirs, des potentiomètres.
  5. Appareil auditif suivant la revendication 3, caractérisé en ce qu'il est présent, comme moyen (13, 13') pour détecter des états de système de l'appareil (1) auditif, un dispositif (15) surveillant l'état de charge de la pile de l'appareil auditif.
  6. Appareil auditif suivant l'une des revendications 1 à 5, caractérisé en ce que le module (9) pour la préparation de signaux comprend des composants pour redresser (16) et/ou former (17) des valeurs moyennes et/ou pour effectuer une dérivation (18) dans le temps.
  7. Appareil auditif suivant l'une des revendications 1 à 16, caractérisé en ce qu'il est présent, dans un appareil auditif comportant plusieurs canaux de fréquence, des points (7) de prélèvement pour les signaux (8) dans les canaux individuels.
  8. Appareil auditif suivant la revendication 1, caractérisé en ce qu'il est mis en mémoire dans le support (6) de données, qui est associé à la structure (5) neuronale, une information de configuration du contrôleur.
  9. Appareil auditif suivant la revendication 1, caractérisé en ce que le contrôleur disposé à côté de la voie de signaux du microphone à l'écouteur comprend des parties (20) fonctionnelles supplémentaires qui fonctionnent suivant le principe de la logique floue.
  10. Appareil auditif suivant la revendication 9, caractérisé en ce que le système 20 de logique floue comporte des composants pour la mise (21) en logique floue et pour la formation (22) d'inférences, et un composant (23) de moyen de décision étant réalisé en structure neuronale.
  11. Appareil auditif suivant l'une des revendications 1 à 10, caractérisé en ce que la structure (5) neuronale est réalisée soit en réseau rétrocouplé monocouche (figure 6), soit en réseau exempt de rétrocouplage multicouche (figure 7), soit sous forme mixte des deux structures de réseau.
  12. Appareil auditif suivant l'une des revendications 1 à 11, caractérisé en ce que les fonctions de pondération sont prescrites de manière fixe à l'entrée de tous les neurones par la structure de circuit.
  13. Appareil auditif suivant l'une des revendications 1 à 11, caractérisé en ce que les fonctions de pondération sont réalisées de manière programmable à l'entrée de tous les neurones par un appareil de commande externe, les données de programmation étant mémorisées dans un support (6) de données commun ou les données de programmation associées étant mémorisées dans des sous-mémoires individuelles associées aux neurones.
  14. Appareil auditif suivant l'une des revendications 1 à 11, caractérisé en ce que les fonctions de pondération peuvent être modifiées à des instants déterminés ou en continu à l'entrée de tous les neurones par un algorithme mis en oeuvre dans la structure de circuit.
EP19940117797 1994-11-10 1994-11-10 Prothèse auditive programmable Revoked EP0712263B1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
DE59410236T DE59410236D1 (de) 1994-11-10 1994-11-10 Programmierbares Hörgerät
DK94117797T DK0712263T3 (da) 1994-11-10 1994-11-10 Programmerbart høreapparat.
EP19940117797 EP0712263B1 (fr) 1994-11-10 1994-11-10 Prothèse auditive programmable

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
EP19940117797 EP0712263B1 (fr) 1994-11-10 1994-11-10 Prothèse auditive programmable

Publications (2)

Publication Number Publication Date
EP0712263A1 EP0712263A1 (fr) 1996-05-15
EP0712263B1 true EP0712263B1 (fr) 2003-01-29

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ID=8216452

Family Applications (1)

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EP19940117797 Revoked EP0712263B1 (fr) 1994-11-10 1994-11-10 Prothèse auditive programmable

Country Status (3)

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EP (1) EP0712263B1 (fr)
DE (1) DE59410236D1 (fr)
DK (1) DK0712263T3 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8638949B2 (en) 2006-03-14 2014-01-28 Starkey Laboratories, Inc. System for evaluating hearing assistance device settings using detected sound environment
US8917891B2 (en) 2010-04-13 2014-12-23 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices
US8942398B2 (en) 2010-04-13 2015-01-27 Starkey Laboratories, Inc. Methods and apparatus for early audio feedback cancellation for hearing assistance devices
US9654885B2 (en) 2010-04-13 2017-05-16 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices

Families Citing this family (9)

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Publication number Priority date Publication date Assignee Title
DK0814634T3 (da) * 1996-06-21 2003-02-03 Siemens Audiologische Technik Programmerbart høreapparatsystem og fremgangsmåde til fastsættelse af optimale parametersæt i et høreapparat
EP0814636A1 (fr) * 1996-06-21 1997-12-29 Siemens Audiologische Technik GmbH Prothèse auditive
US7889879B2 (en) 2002-05-21 2011-02-15 Cochlear Limited Programmable auditory prosthesis with trainable automatic adaptation to acoustic conditions
AUPS247002A0 (en) * 2002-05-21 2002-06-13 Hearworks Pty Ltd Programmable auditory prosthesis with trainable automatic adaptation to acoustic conditions
DK1367857T3 (da) * 2002-05-30 2012-06-04 Gn Resound As Fremgangsmåde til dataregistrering i en høreprotese
DE10347211A1 (de) 2003-10-10 2005-05-25 Siemens Audiologische Technik Gmbh Verfahren zum Nachtrainieren und Betreiben eines Hörgeräts und entsprechendes Hörgerät
CN101513084A (zh) * 2006-09-27 2009-08-19 奥迪康有限公司 具有用于功能设置和学习设置的存储空间的助听器及其编程方法
WO2008154706A1 (fr) 2007-06-20 2008-12-24 Cochlear Limited Procédé et appareil pour optimiser la commande de fonctionnement d'une prothèse auditive
US9729976B2 (en) 2009-12-22 2017-08-08 Starkey Laboratories, Inc. Acoustic feedback event monitoring system for hearing assistance devices

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US5101361A (en) * 1989-09-29 1992-03-31 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Analog hardware for delta-backpropagation neural networks
NO169689C (no) * 1989-11-30 1992-07-22 Nha As Programmerbart hybrid hoereapparat med digital signalbehandling samt fremgangsmaate ved deteksjon og signalbehandlingi samme.
US5253300A (en) * 1991-03-22 1993-10-12 H. C. Knapp Sound Technology Inc. Solar powered hearing aid
JPH05127706A (ja) * 1991-10-31 1993-05-25 Toshiba Corp ニユーラルネツト型シミユレータ

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8638949B2 (en) 2006-03-14 2014-01-28 Starkey Laboratories, Inc. System for evaluating hearing assistance device settings using detected sound environment
US8917891B2 (en) 2010-04-13 2014-12-23 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices
US8942398B2 (en) 2010-04-13 2015-01-27 Starkey Laboratories, Inc. Methods and apparatus for early audio feedback cancellation for hearing assistance devices
US9654885B2 (en) 2010-04-13 2017-05-16 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices

Also Published As

Publication number Publication date
DK0712263T3 (da) 2003-05-26
EP0712263A1 (fr) 1996-05-15
DE59410236D1 (de) 2003-03-06

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