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EP1696700B2 - Hearing aid with user-controlled automatic calibration system - Google Patents

Hearing aid with user-controlled automatic calibration system Download PDF

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Publication number
EP1696700B2
EP1696700B2 EP06101565.7A EP06101565A EP1696700B2 EP 1696700 B2 EP1696700 B2 EP 1696700B2 EP 06101565 A EP06101565 A EP 06101565A EP 1696700 B2 EP1696700 B2 EP 1696700B2
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EP
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Prior art keywords
hearing apparatus
hearing
measuring cycle
measuring
hearing aid
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EP06101565.7A
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German (de)
French (fr)
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EP1696700B1 (en
EP1696700A3 (en
EP1696700A2 (en
Inventor
Tom Weidner
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Sivantos GmbH
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Sivantos GmbH
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    • 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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • 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 present invention relates to a hearing aid device with a measuring device for measuring a feedback path and an operating device for the hearing device wearer to operate the hearing device.
  • the actual feedback path or its properties is not known and what is known as an adaptation is constantly running, the risk of artifacts being very high.
  • the actual feedback path is first measured by a matching computer or a programming device. Basic values for the feedback reduction result from this measurement and only a minimal continuous adaptation has to be carried out by the hearing aid on the basis of these basic values, or this fine adaptation is completely dispensed with. Since a special fitting computer is required to measure the feedback path, the measurement is only carried out by an acoustician and never by a hearing aid wearer.
  • the patent specification DE 199 04 538 C1 discloses a method for feedback detection in a hearing aid. After switching on the hearing aid or after an initialization command triggered by the user, a signal transmission path is monitored for feedback. A control unit gradually increases the amplification of the hearing aid as long as there is no feedback and a predetermined maximum amplification has not yet been reached.
  • the publication also describes EP 0 581 261 A1 a hearing aid with user-controlled sound feedback.
  • the hearing aid has an adaptable feedback compensator.
  • the user can activate the adaptation by means of a control element.
  • the object of the present invention is to make the feedback reduction as comfortable as possible for the user of a hearing device.
  • a hearing device according to claim 1 is provided for this purpose.
  • the invention is based on the idea of creating a hearing device and, in particular, a hearing device with a feedback compensator which is automatically initialized after conscious activation by the wearer or hearing device wearer.
  • a type of adaptive filtering can be used for feedback compensation, which, however, does not adapt permanently, but only during a calibration phase.
  • the parameters determined in this way are then recorded permanently.
  • a hearing aid device can independently measure the current feedback path and after successful measurement, depending on the program, can store it permanently in the hearing aid, without a programming device having to be connected to the hearing aid device or any connection to an external computer.
  • the operating device of the hearing device is preferably implemented as a remote control. This means that there is no need for a separate switching mechanism for triggering the measurement phase.
  • the operating device can have several keys, the measuring cycle being represented by a key combination can be triggered.
  • the measuring cycle can, however, also be triggered by a predetermined time sequence of pressing a key. In this way, buttons can be used to trigger the measuring cycle that are also used for other functionalities.
  • the operating device is arranged invisibly from the outside in the shell of the hearing aid device or the hearing device.
  • the operating device can comprise, for example, a reed relay as a magnetic field detector or a high-frequency detector. Both enable the hearing aid to be operated through the hearing aid shell.
  • the hearing device according to the invention has a signal generator for outputting a control tone upon activation and / or upon termination of the measurement cycle.
  • a control tone can also be output if the measurement cycle has been carried out successfully / unsuccessfully.
  • optical or tactile signals are also suitable for checking the measuring cycle.
  • the operating device has a sound receiver so that the measurement cycle can be triggered or influenced by a tone or a sequence of tones.
  • the measuring cycle can be triggered, for example, with the aid of a mobile phone that emits the corresponding key tones.
  • a special control is implemented which is activated by a predetermined operation of the hearing aid to carry out a calibration process.
  • the measured coefficients are written into a non-volatile memory of the hearing aid. From this point on, even after switching off and changing the battery, the feedback algorithm present in the hearing aid remains preset with the measured parameters. This immediately results in an effective reduction in feedback. Since the feedback algorithm no longer has to adapt, there are no adaptation artifacts.
  • the advantage of the calibration method according to the invention is that complex algorithms such as a feedback compensator can be individually calibrated and preset even in the case of non-programmable devices (e.g. headsets) or devices in which the adjustment is not carried out by an acoustician. This makes calibration processes more user-friendly.
  • Step S1 symbolically indicates that the hearing device or specifically the hearing device is ready to carry out a calibration process.
  • step S2 the user triggers the calibration process through conscious operation.
  • an instruction manual or other information may give the hearing aid wearer the necessary information and explanations about the system.
  • a special key combination or an operating element must be actuated in a certain time sequence. This can be done either directly on the hearing aid or on a remote control that may be present.
  • Another alternative, as already mentioned, is to use an invisible control element, e.g. B. to provide a reed relay or an RFID detector on the hearing aid and to start the calibration process.
  • the hearing aid expediently emits a control signal (step S3) which indicates to the hearing aid wearer that the calibration system has started.
  • This control signal can be a tone, but also an optical signal.
  • the hearing aid is put into the measuring state. Special device settings may be made here.
  • the measurement process is thus started in accordance with step S5 and a measurement signal is output.
  • a measurement signal is output.
  • a defined noise is emitted via the receiver.
  • an input transducer e.g. B. a microphone
  • the returning portion of the measurement noise is recorded according to step S6 and fed to an analysis unit.
  • a step S7 it is checked whether the measurement has been completed successfully. It is monitored whether a measuring time has expired and / or an error parameter has fallen below a certain limit. After a successful measurement, the measured parameters for the current program are stored permanently in a non-volatile memory of the hearing aid in accordance with step S8. The hearing aid then returns to the original operating state in accordance with step S9. However, the feedback system now works with the newly measured parameters. In accordance with step S10, the hearing aid then outputs a control signal to the hearing aid wearer about the successful measurement. This control signal can also be of an optical, acoustic or tactile nature. The feedback algorithm is now available with the updated default settings and can work without artifacts, since additional adaptation is not necessary or only to a very limited extent.
  • step S7 If the measurement has not yet ended after step S7, one or more termination criteria are checked in accordance with step S11. This includes, for example, the timeout or the presence a certain error condition. If the termination criteria are not met, the measurement continues with step S5. If, on the other hand, a termination criterion is met, the hearing aid returns to the original operating state in accordance with step S12, but no parameters are stored. This means that the feedback system continues to work with the old parameters.
  • step S13 a control signal of an optical, acoustic or tactile nature is output according to step S13 and indicated to the user that the measurement, i.e. i.e., the measurement of the feedback path has failed.
  • the end of the entire measuring process is symbolized in the graphic by step S14.
  • the described method for calibrating a hearing aid device with regard to a feedback path can be used for any hearing aids, but also for non-programmable headsets and the like.
  • a static, currently optimized compensation of the feedback can be achieved through the calibration.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Circuit For Audible Band Transducer (AREA)

Description

Die vorliegende Erfindung betrifft ein Hörhilfegerät mit einer Messeinrichtung zum Messen eines Rückkopplungspfads und einer Bedieneinrichtung zum Bedienen des Hörgeräts durch den Hörgeräteträger.The present invention relates to a hearing aid device with a measuring device for measuring a feedback path and an operating device for the hearing device wearer to operate the hearing device.

Bislang sind zwei Ansätze bekannt, ein Hörhilfegerät an eine individuelle Rückkopplungssituation anzupassen. Bei einem ersten Ansatz ist der tatsächliche Rückkopplungs- bzw. Feedbackpfad bzw. seine Eigenschaften nicht bekannt und es läuft ständig eine sogenannte Adaption, wobei die Gefahr von Artefakten sehr hoch ist. Gemäß dem zweiten Ansatz wird zunächst der tatsächliche Feedbackpfad durch einen Anpasscomputer oder ein Programmiergerät gemessen. Aus dieser Messung ergeben sich Grundwerte für die Feedbackreduktion und es muss nur noch eine minimale kontinuierliche Adaption durch das Hörgerät ausgehend von diesen Grundwerten durchgeführt werden oder es wird auf diese Feinadaption gänzlich verzichtet. Da für das Messen des Feedbackpfads ein spezieller Anpasscomputer notwendig ist, wird die Messung nur von einem Akustiker, nie jedoch von einem Hörgeräteträger selbst durchgeführt.So far, two approaches have been known for adapting a hearing aid device to an individual feedback situation. In a first approach, the actual feedback path or its properties is not known and what is known as an adaptation is constantly running, the risk of artifacts being very high. According to the second approach, the actual feedback path is first measured by a matching computer or a programming device. Basic values for the feedback reduction result from this measurement and only a minimal continuous adaptation has to be carried out by the hearing aid on the basis of these basic values, or this fine adaptation is completely dispensed with. Since a special fitting computer is required to measure the feedback path, the measurement is only carried out by an acoustician and never by a hearing aid wearer.

Aus dem US-Patent US 4 783 818 ist ein Verfahren und eine Vorrichtung zur adaptiven Filterung von akustischen Rückkopplungssignalen bekannt. Zur Identifikation der akustischen Rückkopplungsparameter wird die Konfiguration des Kommunikationssystems von einem üblichen Betriebsmodus in einen Parameteridentifikationsmodus gewechselt. Dabei wird der Verstärker in üblicher Weise von dem Mikrofon und dem Lautsprecher getrennt und durch einen Identifikationsschaltkreis ersetzt. Zwischen den beiden Modi wird automatisch in Abhängigkeit eines Schwellwerts hin- und hergeschaltet. Nachteilig daran ist, dass das Hörgerät dann für den normalen Hörbetrieb unter Umständen sehr häufig ausfällt, nämlich immer dann, wenn es in den Identifikationsmodus wechselt.From the US patent U.S. 4,783,818 a method and a device for adaptive filtering of acoustic feedback signals are known. To identify the acoustic feedback parameters, the configuration of the communication system is changed from a conventional operating mode to a parameter identification mode. The amplifier is separated from the microphone and the loudspeaker in the usual way and replaced by an identification circuit. It automatically switches back and forth between the two modes depending on a threshold value. The disadvantage of this is that the hearing aid then under certain circumstances fails very frequently for normal hearing operation, namely whenever it changes to the identification mode.

Ferner sind aus den Druckschriften EP 0 415 677 B1 , EP 0 634 084 B1 und WO 94/09604 Hörgeräte mit Feedbackunterdrückung bekannt. Dabei werden teilweise eigene Geräuschquellen eingesetzt.Furthermore, from the publications EP 0 415 677 B1 , EP 0 634 084 B1 and WO 94/09604 Hearing aids with feedback suppression known. In some cases, own noise sources are used.

Darüber hinaus ist in der Patentschrift DE 41 28 172 C2 ein digitales Hörgerät beschrieben, bei dem ein akustischer Sensor eine otoakustische Reaktion des Innenohrs des Hörgeräteträgers auf die von einem elektroakustischen Wandler abgegebenen Messtöne erfasst. Ein Mikrorechner nimmt anhand der jeweiligen Sensorspannung einen Vergleich und eine Korrektur der Übertragungsfunktion vor. Eingeleitet wird der Mess- und Korrekturvorgang beispielsweise durch Betätigen einer mit dem Mikrorechner verbundenen Taste, die die Funktion eines Schalters hat.In addition, is in the patent DE 41 28 172 C2 describes a digital hearing aid in which an acoustic sensor detects an otoacoustic reaction of the inner ear of the hearing aid wearer to the measurement tones emitted by an electroacoustic transducer. A microcomputer compares and corrects the transfer function based on the respective sensor voltage. The measurement and correction process is initiated, for example, by pressing a button that is connected to the microcomputer and has the function of a switch.

In dem Artikel Bisgaard, Nikolai; Dyrlund, Ole; "DFS - ein neues digitales System zur Rückkopplungsunterdrückung in Hörgeräten"; in Audiologische Akustik 5/91, Seiten 166, 168 und 173 - 177 ist ein digitales System zur Rückkopplungsunterdrückung in Hörgeräten beschrieben. Hier ist das Rückkopplungssignal als der Teil des Ausgangssignals definiert, der zum Mikrofon zurückgeführt wird. Die Rückführung erfolgt entweder durch eine Belüftungsrille oder eine Undichtigkeit zwischen Ohrpassstück und Gehörgang. Ist die Dämpfung auf der Strecke des Rückkopplungssignals geringer als die Verstärkung des Hörgeräts, treten im System Schwingungen mit einem sehr hohen Schalldruckpegel auf. Das digitale Rückkopplungsunterdrückungssystem misst laufend den Frequenzgang der Rückkopplungsstrecke und erzeugt ein Korrektursignal, das mit dem Eingangssignal überlagert wird, um die Rückkopplung zu unterdrücken. Dieses System weist jedoch auch die oben genannten Nachteile eines ständig adaptierenden Systems auf.In the article Bisgaard, Nikolai; Dyrlund, Ole; "DFS - a new digital system for feedback suppression in hearing aids"; in Audiologische Akustik 5/91, pages 166, 168 and 173 - 177 describes a digital system for suppressing feedback in hearing aids. Here the feedback signal is defined as that part of the output signal that is fed back to the microphone. The return occurs either through a ventilation groove or a leak between the earmold and the ear canal. If the attenuation on the path of the feedback signal is less than the amplification of the hearing aid, vibrations with a very high sound pressure level occur in the system. The digital feedback suppression system continuously measures the frequency response of the feedback path and generates a correction signal that is superimposed on the input signal in order to suppress the feedback. However, this system also has the above-mentioned disadvantages of a continuously adapting system.

Die Patentschrift DE 199 04 538 C1 offenbart ein Verfahren zur Rückkopplungserkennung in einem Hörgerät. Nach dem Einschalten des Hörgeräts oder nach einem vom Benutzer ausgelösten Initialisierungsbefehl wird eine Signalübertragungsstrecke auf Rücckopplungen überwacht. Eine Steuereinheit erhöht die Verstärkung des Hörgeräts allmählich, so lange keine Rückkopplung auftritt und eine vorgegebene Maximalverstärkung noch nicht erreicht ist.The patent specification DE 199 04 538 C1 discloses a method for feedback detection in a hearing aid. After switching on the hearing aid or after an initialization command triggered by the user, a signal transmission path is monitored for feedback. A control unit gradually increases the amplification of the hearing aid as long as there is no feedback and a predetermined maximum amplification has not yet been reached.

Weiterhin beschreibt die Druckschrift EP 0 581 261 A1 ein Hörgerät mit benutzergesteuerter Schallrücckopplung. Das Hörgerät besitzt einen adaptierbaren Feedback-Kompensator. Der Benutzer kann die Adaption durch ein Steuerelement aktivieren.The publication also describes EP 0 581 261 A1 a hearing aid with user-controlled sound feedback. The hearing aid has an adaptable feedback compensator. The user can activate the adaptation by means of a control element.

Die Aufgabe der vorliegenden Erfindung besteht darin, die Feedbackreduktion für den Nutzer einer Hörvorrichtung so komfortabel wie möglich zu gestalten.The object of the present invention is to make the feedback reduction as comfortable as possible for the user of a hearing device.

Erfindungsgemäß wird hierzu bereitgestellt eine Hörvorrichtung nach Anspruch 1.According to the invention, a hearing device according to claim 1 is provided for this purpose.

Die Erfindung basiert auf dem Gedanken, eine Hörvorrichtung und insbesondere ein Hörgerät mit einem Feedback-Kompensator zu schaffen, der sich selbsttätig nach bewusster Aktivierung durch den Träger bzw. Hörgeräteträger initialisiert. Hierzu kann beispielsweise eine Art adaptives Filtern zur Feedback-Kompensation verwendet werden, welches jedoch nicht permanent, sondern nur während einer Einmessphase adaptiert. Danach werden die so ermittelten Parameter dauerhaft festgehalten. Dies bedeutet, dass ein Hörhilfegerät auf Veranlassung des Hörgeräteträgers hin selbstständig den aktuellen Feedbackpfad messen und nach erfolgreicher Messung programmabhängig dauerhaft im Hörgerät abspeichern kann, ohne dass dazu ein Programmiergerät an das Hörhilfegerät angeschlossen oder irgendeine Verbindung zu einem externen Computer hergestellt sein muss.The invention is based on the idea of creating a hearing device and, in particular, a hearing device with a feedback compensator which is automatically initialized after conscious activation by the wearer or hearing device wearer. For this purpose, for example, a type of adaptive filtering can be used for feedback compensation, which, however, does not adapt permanently, but only during a calibration phase. The parameters determined in this way are then recorded permanently. This means that, at the instigation of the hearing aid wearer, a hearing aid device can independently measure the current feedback path and after successful measurement, depending on the program, can store it permanently in the hearing aid, without a programming device having to be connected to the hearing aid device or any connection to an external computer.

Vorzugsweise ist die Bedieneinrichtung der Hörvorrichtung als Fernbedienung realisiert. Damit kann auf einen eigenen Schaltmechanismus für das Auslösen der Messphase verzichtet werden.The operating device of the hearing device is preferably implemented as a remote control. This means that there is no need for a separate switching mechanism for triggering the measurement phase.

Die Bedieneinrichtung kann mehrere Tasten aufweisen, wobei der Messzyklus durch eine Tastenkombination auslösbar ist. Der Messzyklus kann aber auch durch eine vorgegebene zeitliche Abfolge einer Betätigung einer Taste ausgelöst werden. Auf diese Weise können für das Auslösen des Messzyklus Tasten verwendet werden, die auch für andere Funktionalitäten eingesetzt sind.The operating device can have several keys, the measuring cycle being represented by a key combination can be triggered. The measuring cycle can, however, also be triggered by a predetermined time sequence of pressing a key. In this way, buttons can be used to trigger the measuring cycle that are also used for other functionalities.

Entsprechend einer ebenfalls bevorzugten Ausführungsform ist die Bedieneinrichtung von außen unsichtbar in der Schale des Hörhilfegeräts bzw. der Hörvorrichtung angeordnet. Hierzu kann die Bedieneinrichtung beispielsweise ein Reedrelais als Magnetfelddetektor oder einen Hochfrequenzdetektor umfassen. Beide ermöglichen eine Bediendung des Hörgeräts durch die Hörgeräteschale hindurch.According to a likewise preferred embodiment, the operating device is arranged invisibly from the outside in the shell of the hearing aid device or the hearing device. For this purpose, the operating device can comprise, for example, a reed relay as a magnetic field detector or a high-frequency detector. Both enable the hearing aid to be operated through the hearing aid shell.

Vorteilhaft ist auch, wenn die erfindungsgemäße Hörvorrichtung einen Signalgenerator zur Ausgabe eines Kontrolltons bei Aktivierung und/oder bei Beendigung des Messzyklus aufweist. Alternativ oder zusätzlich kann ein Kontrollton auch bei erfolgreicher/nicht erfolgreicher Durchführung des Messzyklus ausgegeben werden. Anstelle des Kontrolltons eignen sich auch optische oder taktile Signale zur Kontrolle des Messzyklus.It is also advantageous if the hearing device according to the invention has a signal generator for outputting a control tone upon activation and / or upon termination of the measurement cycle. As an alternative or in addition, a control tone can also be output if the measurement cycle has been carried out successfully / unsuccessfully. Instead of the control tone, optical or tactile signals are also suitable for checking the measuring cycle.

In einer speziellen Ausgestaltung weist die Bedieneinrichtung einen Schallempfänger auf, so dass der Messzyklus durch einen Ton oder eine Abfolge von Tönen auslösbar oder beeinflussbar ist. Damit kann der Messzyklus beispielsweise mit Hilfe eines Handy ausgelöst werden, das entsprechende Tastentöne ausgibt.In a special embodiment, the operating device has a sound receiver so that the measurement cycle can be triggered or influenced by a tone or a sequence of tones. In this way, the measuring cycle can be triggered, for example, with the aid of a mobile phone that emits the corresponding key tones.

Die vorliegende Erfindung wird nun anhand der beigefügten Zeichnung näher erläutert, die ein Flussdiagramm für das Einmessen eines Hörhilfegeräts wiedergibt.The present invention will now be explained in more detail with reference to the accompanying drawing, which shows a flow chart for calibrating a hearing aid device.

Das nachfolgend näher geschilderte Ausführungsbeispiel stellt eine bevorzugte Ausführungsform der vorliegenden Erfindung dar.The exemplary embodiment described in more detail below represents a preferred embodiment of the present invention.

In einem erfindungsgemäßen Hörgerät ist eine spezielle Steuerung implementiert, die durch eine vorgegebene Bedienung des Hörgeräts zur Durchführung eines Einmessvorgangs aktiviert wird. Die gemessenen Koeffizienten werden in einen nicht flüchtigen Speicher des Hörgeräts geschrieben. Ab diesem Zeitpunkt, auch nach Ausschalten und Batteriewechsel bleibt der im Hörgerät vorhandene Feedbackalgorithmus mit den gemessenen Parametern voreingestellt. Dadurch ist sofort eine wirksame Feedbackreduktion gegeben. Da der Feedbackalgorithmus nicht mehr adaptieren muss, gibt es keine Adaptionsartefakte.In a hearing aid according to the invention, a special control is implemented which is activated by a predetermined operation of the hearing aid to carry out a calibration process. The measured coefficients are written into a non-volatile memory of the hearing aid. From this point on, even after switching off and changing the battery, the feedback algorithm present in the hearing aid remains preset with the measured parameters. This immediately results in an effective reduction in feedback. Since the feedback algorithm no longer has to adapt, there are no adaptation artifacts.

Der Vorzug der erfindungsgemäßen Einmessmethode besteht darin, dass auch bei nicht programmierbaren Geräten (z. B. Headsets) oder bei Geräten, bei denen die Anpassung nicht über einen Akustiker geschieht, so komplexe Algorithmen wie ein Feedbacckompensator individuell eingemessen und voreingestellt werden können. Dadurch werden Einmessvorgänge nutzerfreundlicher.The advantage of the calibration method according to the invention is that complex algorithms such as a feedback compensator can be individually calibrated and preset even in the case of non-programmable devices (e.g. headsets) or devices in which the adjustment is not carried out by an acoustician. This makes calibration processes more user-friendly.

Im Einzelnen erfolgt der Einmessvorgang entsprechend den Schritten aus der Figur. Der Schritt S1 deutet symbolisch an, dass die Hörvorrichtung oder speziell das Hörgerät zum Durchführen eines Einmessvorgangs bereit ist. In einem Schritt S2 löst der Benutzer den Einmessvorgang durch bewusste Bedienung aus. Hierzu gibt gegebenenfalls eine Bedienungsanleitung oder eine anderweitige Information dem Hörgeräteträger die notwendigen Hinweise und Erläuterungen zu dem System. Beispielsweise muss eine spezielle Tastenkombination oder ein Bedienelement in einer bestimmten zeitlichen Abfolge betätigt werden. Dies kann sowohl direkt am Hörgerät oder an einer eventuell vorhandenen Fernbedienung ausgeführt werden. Eine weitere Alternative besteht, wie bereits erwähnt, darin, ein nicht sichtbares Bedienelement, z. B. ein Reedrelais oder einen RFID-Detektor am Hörgerät vorzusehen und den Einmessvorgang darüber zu starten.In detail, the calibration process takes place in accordance with the steps from the figure. Step S1 symbolically indicates that the hearing device or specifically the hearing device is ready to carry out a calibration process. In a step S2, the user triggers the calibration process through conscious operation. For this purpose, an instruction manual or other information may give the hearing aid wearer the necessary information and explanations about the system. For example, a special key combination or an operating element must be actuated in a certain time sequence. This can be done either directly on the hearing aid or on a remote control that may be present. Another alternative, as already mentioned, is to use an invisible control element, e.g. B. to provide a reed relay or an RFID detector on the hearing aid and to start the calibration process.

Nach dem Start des Einmessvorgangs gibt das Hörgerät günstigerweise ein Kontrollsignal aus (Schritt S3), das dem Hörgeräteträger den Start des Einmesssystems anzeigt. Dieses Kontrollsignal kann ein Ton, aber auch ein optisches Signal sein. In einem anschließenden Schritt S4 wird das Hörgerät in den Messzustand versetzt. Dabei werden eventuell spezielle Geräteeinstellungen vorgenommen.After the calibration process has started, the hearing aid expediently emits a control signal (step S3) which indicates to the hearing aid wearer that the calibration system has started. This control signal can be a tone, but also an optical signal. In a subsequent step S4, the hearing aid is put into the measuring state. Special device settings may be made here.

Der Messvorgang ist somit gemäß Schritt S5 gestartet und es wird ein Messsignal ausgegeben. Beispielsweise wird ein definiertes Rauschen über den Hörer abgegeben. Von einem Eingangswandler, z. B. einem Mikrofon wird der zurückkommende Anteil des Messgeräuschs gemäß Schritt S6 aufgenommen und einer Analyseeinheit zugeführt.The measurement process is thus started in accordance with step S5 and a measurement signal is output. For example, a defined noise is emitted via the receiver. From an input transducer, e.g. B. a microphone, the returning portion of the measurement noise is recorded according to step S6 and fed to an analysis unit.

In einem Schritt S7 wird überprüft, ob die Messung erfolgreich beendet wurde. Dabei wird überwacht, ob eine Messzeit abgelaufen und/oder ein Fehlerparameter unter eine bestimmte Grenze gesunken ist. Nach erfolgreicher Messung werden die gemessenen Parameter für das aktuelle Programm dauerhaft in einem nicht flüchtigen Speicher des Hörgeräts entsprechend Schritt S8 abgelegt. Anschließend kehrt das Hörgerät wieder in den ursprünglichen Betriebszustand gemäß Schritt S9 zurück. Das Feedbacksystem arbeitet nun jedoch mit den neu gemessenen Parametern. Daraufhin gibt das Hörgerät entsprechend Schritt S10 ein Kontrollsignal an den Hörgeräteträger über die erfolgreiche Messung aus. Auch dieses Kontrollsignal kann optischer, akustischer oder aber auch taktiler Natur sein. Der Feedbackalgorithmus steht nun mit den aktualisierten Voreinstellungen zur Verfügung und kann ohne Artefakte arbeiten, da eine zusätzliche Adaption nicht oder nur in sehr geringem Umfang notwendig ist.In a step S7 it is checked whether the measurement has been completed successfully. It is monitored whether a measuring time has expired and / or an error parameter has fallen below a certain limit. After a successful measurement, the measured parameters for the current program are stored permanently in a non-volatile memory of the hearing aid in accordance with step S8. The hearing aid then returns to the original operating state in accordance with step S9. However, the feedback system now works with the newly measured parameters. In accordance with step S10, the hearing aid then outputs a control signal to the hearing aid wearer about the successful measurement. This control signal can also be of an optical, acoustic or tactile nature. The feedback algorithm is now available with the updated default settings and can work without artifacts, since additional adaptation is not necessary or only to a very limited extent.

Sollte später aufgrund von Änderungen des Sitzes der Otoplastik oder des Hörgeräts ein erneutes Einmessen notwendig sein, so kann dies leicht durch Wiederholung des oben genannten Ablaufs getan werden. Der Ablauf ist prinzipiell beliebig oft wiederholbar.Should a new measurement be necessary later due to changes in the fit of the otoplastic or the hearing aid, this can easily be done by repeating the above-mentioned procedure. In principle, the process can be repeated as often as required.

Ist die Messung nach Schritt S7 noch nicht beendet, so werden entsprechend Schritt S11 ein oder mehrere Abbruchkriterien überprüft. Dazu zählt beispielsweise die Zeitüberschreitung oder das Vorliegen einer bestimmten Fehlerbedingung. Sind die Abbruchkriterien nicht erfüllt, so geht die Messung mit Schritt S5 weiter. Ist die Erfüllung eines Abbruchkriteriums hingegen gegeben, so kehrt entsprechend Schritt S12 das Hörgerät in den ursprünglichen Betriebszustand zurück, aber es werden keine Parameter abgespeichert. Dies bedeutet, dass das Feedbacksystem mit den alten Parametern weiter arbeitet.If the measurement has not yet ended after step S7, one or more termination criteria are checked in accordance with step S11. This includes, for example, the timeout or the presence a certain error condition. If the termination criteria are not met, the measurement continues with step S5. If, on the other hand, a termination criterion is met, the hearing aid returns to the original operating state in accordance with step S12, but no parameters are stored. This means that the feedback system continues to work with the old parameters.

Auch bei der nicht erfolgreichen Messung wird gemäß Schritt S13 ein Kontrollsignal optischer, akustischer oder taktiler Natur ausgegeben und dem Benutzer dadurch angedeutet, dass das Einmessen, d. h., das Messen des Rückkopplungs- bzw. Feedbackpfads, gescheitert ist. Das Ende des gesamten Messvorgangs wird in der Grafik durch Schritt S14 symbolisiert.Even if the measurement is unsuccessful, a control signal of an optical, acoustic or tactile nature is output according to step S13 and indicated to the user that the measurement, i.e. i.e., the measurement of the feedback path has failed. The end of the entire measuring process is symbolized in the graphic by step S14.

Das beschriebene Verfahren zum Einmessen eines Hörhilfegeräts hinsichtlich eines Rückkopplungspfads kann für beliebige Hörgeräte, aber auch für nicht programmierbare Headsets und dergleichen verwendet werden. In jedem Fall kann durch das Einmessen eine statische, aktuell optimierte Kompensation der Rücckopplung erreicht werden. In vielen Fällen erübrigt sich dadurch eine dynamische Kompensation, oder aber die dynamische Kompensation kann in sehr geringem Rahmen durchgeführt werden.The described method for calibrating a hearing aid device with regard to a feedback path can be used for any hearing aids, but also for non-programmable headsets and the like. In any case, a static, currently optimized compensation of the feedback can be achieved through the calibration. In many cases this makes dynamic compensation unnecessary, or dynamic compensation can be carried out within a very limited range.

Claims (11)

  1. Hearing apparatus with
    - a measuring facility for measuring a feedback path of the hearing apparatus and
    - an operating facility for operating the hearing apparatus by a wearer, wherein
    - a measuring cycle for determining at least one characteristic of the feedback path can be activated (S2) using the operating facility, and
    - a feedback compensator comprising a number of changeable parameters, the values of which are determined on the basis of measuring cycles,
    characterised in that
    - the hearing apparatus is set up monitor whether the measurement has terminated (S7) successfully, and to this end to monitor whether a measurement time has elapsed and whether a defect parameter has dropped below a certain limit, and
    - to only write the determined values of the parameters permanently in a non-volatile memory of the hearing apparatus (S8) after successful measurement for a current program, wherein following successful measurement, the feedback compensator operates with the determined values of the parameters.
  2. Hearing apparatus according to claim 1, with the operating facility being a remote control.
  3. Hearing apparatus according to claim 1 or 2, with the operating facility comprising a number of keys and the measuring cycle able to be activated by a key combination (S2) .
  4. Hearing apparatus according to one of the preceding claims, with the measuring cycle being activateable by a predetermined chronological sequence of an activation of a key.
  5. Hearing apparatus according to one of the preceding claims, with the operating facility being arranged in the shell of the hearing apparatus and thus being invisible from the outside.
  6. Hearing apparatus according to claim 5, with the operating facility featuring a magnetic field detector, in particular a reed relay or an RFID detector, or a high frequency detector.
  7. Hearing apparatus according to one of the preceding claims, comprising a signal generator for outputting (S3, S10, S13) a control tone during the activation and/or the termination of the measuring cycle.
  8. Hearing apparatus according to one of the preceding claims, comprising a signal generator for outputting (S3, S10, S13) a control tone with a successful execution and a further control tone with an unsuccessful execution of the measuring cycle (S7) .
  9. Hearing apparatus according to one of the preceding claims, comprising an optical signalling device and/or a motion generator for outputting (S3, S10, S13) a control signal relating to the execution of a measuring cycle.
  10. Hearing apparatus according to claim 1, with the operating facility comprising an acoustic receiver, so that the measuring cycle can be activated or influenced by a tone or a sequence of tones.
  11. Hearing apparatus according to claim 10, wherein the operating facility is configured to activate the measuring cycle as a function of key tones of a cell phone.
EP06101565.7A 2005-02-23 2006-02-13 Hearing aid with user-controlled automatic calibration system Active EP1696700B2 (en)

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Also Published As

Publication number Publication date
US20060188106A1 (en) 2006-08-24
EP1696700B1 (en) 2013-08-07
DE102005008318A1 (en) 2006-08-31
EP1696700A3 (en) 2009-07-01
US8842862B2 (en) 2014-09-23
DE102005008318B4 (en) 2013-07-04
DK1696700T4 (en) 2021-10-18
DK1696700T3 (en) 2013-11-04
EP1696700A2 (en) 2006-08-30

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