EP1983801A2 - Method for customising a binaural hearing device system - Google Patents
Method for customising a binaural hearing device system Download PDFInfo
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- EP1983801A2 EP1983801A2 EP20080103409 EP08103409A EP1983801A2 EP 1983801 A2 EP1983801 A2 EP 1983801A2 EP 20080103409 EP20080103409 EP 20080103409 EP 08103409 A EP08103409 A EP 08103409A EP 1983801 A2 EP1983801 A2 EP 1983801A2
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- Prior art keywords
- hearing aid
- hearing
- ear
- hardware information
- audiometric data
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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
- H04R25/55—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
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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
- H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
Definitions
- the present invention relates to a method for adapting a hearing aid system with a first hearing aid for supplying the first ear and a second hearing aid for supplying the second ear of a hearing aid wearer by adjusting the first hearing aid based on audiometric data of the first ear.
- Hearing aids are portable hearing aids that are used to care for the hearing impaired.
- different types of hearing aids such as behind-the-ear hearing aids (BTE) and in-the-ear hearing aids (ITO), e.g. also Concha hearing aids or canal hearing aids (CIC), provided.
- BTE behind-the-ear hearing aids
- ITO in-the-ear hearing aids
- CIC canal hearing aids
- the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
- bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
- Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
- the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
- the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
- the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
- a signal processing unit 3 which is also integrated into the hearing aid housing 1, processes the microphone signals and amplifies them she.
- the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
- the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
- the power supply of the hearing device and in particular of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
- the basis for the hearing aid fitting is the audiometric data as well as information about the personal profile of the hearing impaired person.
- the latter can z.
- the tonal-audiometric characteristics are taken into account only for the basic adjustment of the frequency- and level-dependent amplification of the respective side of the binaural hearing system.
- other parameters such as the noise depth of a noise suppression or the time constants of the most diverse algorithms of a hearing system, should be set symmetrically on both sides supplied in order to achieve a symmetrical listening experience. This is among other things decisive for the localization ability.
- Corresponding adjustments are currently taking place only via the profile of the hearing impaired.
- other parameters are not included in the hearing aid fitting.
- the gains of the two hearing aids of a hearing aid system are always set individually.
- the binaural loudness correction the gain in both devices to z. B. 3 dB lowered because amplifies the loudness impression in binaural supply versus individual care.
- the adapter includes a computer having a display for visual presentation of data, a data input for inputting hearing aid program data to the adapter, a data memory, and a data output for outputting the data to a hearing aid.
- means are provided for selecting simultaneous adjustments to two or more different parameters for the sound processing in the hearing aid device to be programmed.
- a gain value can be transmitted from one of the hearing aid devices to the other. Subsequently, a balance of the signal amplitudes, wherein in at least one of the hearing aid devices, the gain is changed. The adjustment can be made taking into account the audiograms measured in both ears. This ensures that, for example, a loudness change caused by a parameter change on a hearing aid device causes a loudness change that is subjective for the hearing aid wearer on the other hearing aid device.
- the patent discloses DE 10 2004 051 325 B3 a method for adjusting the transmission characteristic of a hearing aid.
- a possibility for setting a binaural supply system consisting of two hearing aids is described. Since the two ears of a user often have a similar hearing loss, it is therefore appropriate to first take over the settings selected for the supply of an ear on the hearing aid for the second hearing aid and then perform only a fine adjustment in the hearing aid for supplying the second ear.
- the publication US Pat. No. 7,018,342 B2 relates to a method for determining masking levels in an automated one Hearing test. There, different thresholds for air conduction and bone conduction are determined.
- the object of the present invention is thus to provide a method for adapting a hearing device system with two hearing aids, which leads to a more individual adjustment of the binaural supply.
- this object is achieved by a method for adapting a hearing device system with a first hearing device for supplying the first ear and a second hearing device for supplying the second ear of a hearing device wearer by setting the first hearing device on the basis of audiometric data on the first ear, wherein for setting the First hearing aid also hardware information on the second hearing aid is used.
- the two hearing aids can be configured in a binaural hearing system depending on the hardware of the respective other hearing aid.
- the hearing aids are adjusted symmetrically on the basis of a binaural audiogram if audiometric data about the second ear are also used for setting the first hearing device.
- the audiometric data includes an airline hearing threshold, a bone conduction threshold and / or a discomfort threshold.
- these thresholds for example, the residual dynamics, for example, on the left ear for the hearing aid setting on the right ear is taken into account.
- control time for the compression in the first hearing device is adapted to the residual dynamics of the second ear.
- a shorter settling time for the first hearing aid can be selected for the compression, if this does not require the residual dynamics of the first but of the second ear.
- a peak cropping of the output signal of the first hearing device can be effected as a function of the data of the second ear or the second hearing device.
- a setting of a microphone mode (omnidirectional, directional, automatic) or a volume and pitch of a beep of the first hearing aid in response to this data can be done.
- a regulation depth of a noise suppression of the first hearing device can be set as a function of the data of the second ear or of the second hearing device.
- processing algorithms in the first hearing device can thus be better adapted to the individual hearing loss, taking into account the hearing loss at the second ear or taking into account the data of the second hearing device.
- the above-mentioned hardware information may relate to the device type, namely, an IdO or a BTE.
- the pair of devices can be better adapted to the individual hearing loss in its interaction.
- the hardware information may further relate to the type of amplifier or the sound transmission within the second hearing device.
- the hardware information can relate to an acoustic property of an ear device of the second hearing device.
- the acoustic influence of wearing hooks, sound tubes and the like and other device data of the other hearing aid are taken into account.
- FIG. 2 symbolically shows an inventive fitting method, as it can be carried out for example in an audiologist.
- the two hearing aids 10, 11 of a binaural hearing system are adapted to the individual hearing loss of a hearing impaired person.
- the first hearing aid 10 (in short: "left hearing aid") serves to supply the left ear and the second hearing aid 11 (in short: “right hearing aid”) serves to supply the right ear.
- a left audiogram 12 and a right audiogram 13 determined before the adaptation were made by the left side of the hearing impaired.
- a left audiogram 12 and a right audiogram 13 determined.
- the left hearing aid 10 not only the left audiogram 12 but also the right audiogram 13 are considered here according to the invention.
- the left-hand audiogram 12 is also taken into account when adapting the right-hand hearing device 11.
- the two audiograms 12 and 13 are symbolic here of any audiometric data as well as hardware data of the individual hearing aids.
- hardware data such as hearing aid type (IdO or BTE), type of amplifier, carrying hook, sound tube, etc. of the right hearing aid 11 can be used for the adaptation of the left hearing aid 10 or vice versa.
- the problem of different settings of a binaural hearing aid system is thus solved by an adaptation device or an adaptation software for a binaural hearing system in the adaptation of a device from the one side information about the other side (hearing loss, used device, fitting strategy, etc.) queries and used for presetting the binaural hearing system.
- an otherwise common two-sided monaural adaptation is supplemented to the effect that based on information about the binaural hearing loss or the binaural device combination, the default setting of the hearing less generally for the individual hearing loss and thus more focused on the currently existing hearing loss can be received.
- any criteria which has hitherto been disregarded due to the risk of side-by-side adjustments, may be supplemented by the information of the opposite hearing loss.
- This provides a more reliable classification of hearing loss.
- the risk of page-different settings is significantly reduced. This does not affect frequency- and level-dependent gain values, which are still calculated individually for each page.
Abstract
Description
Die vorliegende Erfindung betrifft ein Verfahren zum Anpassen eines Hörgerätesystems mit einem ersten Hörgerät zur Versorgung des ersten Ohrs und einem zweiten Hörgerät zur Versorgung des zweiten Ohrs eines Hörgeräteträgers durch Einstellen des ersten Hörgeräts anhand von audiometrischen Daten des ersten Ohrs.The present invention relates to a method for adapting a hearing aid system with a first hearing aid for supplying the first ear and a second hearing aid for supplying the second ear of a hearing aid wearer by adjusting the first hearing aid based on audiometric data of the first ear.
Hörgeräte sind tragbare Hörvorrichtungen, die zur Versorgung von Schwerhörenden dienen. Um den zahlreichen individuellen Bedürfnissen entgegenzukommen, werden unterschiedliche Bauformen von Hörgeräten wie Hinter-dem-Ohr-Hörgeräte (HdO) und In-dem-Ohr-Hörgeräte (IdO), z.B. auch Concha-Hörgeräte oder Kanal-Hörgeräte (CIC), bereitgestellt. Die beispielhaft aufgeführten Hörgeräte werden am Außenohr oder im Gehörgang getragen. Darüber hinaus stehen auf dem Markt aber auch Knochenleitungshörhilfen, implantierbare oder vibrotaktile Hörhilfen zur Verfügung. Dabei erfolgt die Stimulation des geschädigten Gehörs entweder mechanisch oder elektrisch.Hearing aids are portable hearing aids that are used to care for the hearing impaired. In order to meet the numerous individual needs, different types of hearing aids such as behind-the-ear hearing aids (BTE) and in-the-ear hearing aids (ITO), e.g. also Concha hearing aids or canal hearing aids (CIC), provided. The hearing aids listed by way of example are worn on the outer ear or in the ear canal. In addition, bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
Hörgeräte besitzen prinzipiell als wesentliche Komponenten einen Eingangswandler, einen Verstärker und einen Ausgangswandler. Der Eingangswandler ist in der Regel ein Schallempfänger, z. B. ein Mikrofon, und/oder ein elektromagnetischer Empfänger, z. B. eine Induktionsspule. Der Ausgangswandler ist meist als elektroakustischer Wandler, z. B. Miniaturlautsprecher, oder als elektromechanischer Wandler, z. B. Knochenleitungshörer, realisiert. Der Verstärker ist üblicherweise in eine Signalverarbeitungseinheit integriert. Dieser prinzipielle Aufbau ist in
Grundlage für die Hörgeräteanpassung sind tonaudiometrische Kenndaten sowie Angaben über das persönliche Profil des Hörgeschädigten. Letztere können z. B. Erfahrungswerte mit Hörsystemen sowie Informationen über den Lebensstil (aktiv - passiv, jung - alt, berufstätig - Rentner, etc.) des Hörgeschädigten sein. Diese Informationen sind für ein binaurales System seitenunabhängig und beeinflussen die Voreinstellung des Hörsystems nach der Erstanpassung auf beiden Seiten gleichermaßen.The basis for the hearing aid fitting is the audiometric data as well as information about the personal profile of the hearing impaired person. The latter can z. B. Experience with hearing aids and information about the lifestyle (active - passive, young - old, working - pensioners, etc.) of the hearing impaired. This information is page-independent for a binaural system and affects the pre-adjustment of the hearing instrument after initial fitting on both sides equally.
Die tonaudiometrischen Kenndaten werden hingegen nur für die Grundeinstellung der frequenz- und pegelabhängigen Verstärkung der jeweiligen Seite des binauralen Hörsystems berücksichtigt. Weitere Parameter, wie beispielsweise die Regeltiefe einer Störgeräuschbefreiung oder die Zeitkonstanten der unterschiedlichsten Algorithmen eines Hörsystems, sollten jedoch symmetrisch auf beiden versorgten Seiten eingestellt sein, um einen symmetrischen Höreindruck zu erreichen. Dieser ist unter anderem für die Lokalisierungsfähigkeit maßgebend. Entsprechende Anpassungen finden derzeit lediglich über das Profil des Hörgeschädigten statt. Weitere Kenngrößen fließen jedoch in die Hörgeräteanpassung nicht ein. So werden beispielsweise die Verstärkungen der beiden Hörgeräte eines Hörgerätesystems stets einzeln eingestellt. Gegebenenfalls wird zur binauralen Lautheitskorrektur die Verstärkung in beiden Geräten um z. B. 3 dB gesenkt, da sich der Lautheitseindruck bei binauraler Versorgung gegenüber Einzelversorgung verstärkt.The tonal-audiometric characteristics, however, are taken into account only for the basic adjustment of the frequency- and level-dependent amplification of the respective side of the binaural hearing system. However, other parameters, such as the noise depth of a noise suppression or the time constants of the most diverse algorithms of a hearing system, should be set symmetrically on both sides supplied in order to achieve a symmetrical listening experience. This is among other things decisive for the localization ability. Corresponding adjustments are currently taking place only via the profile of the hearing impaired. However, other parameters are not included in the hearing aid fitting. For example, the gains of the two hearing aids of a hearing aid system are always set individually. Optionally, the binaural loudness correction, the gain in both devices to z. B. 3 dB lowered because amplifies the loudness impression in binaural supply versus individual care.
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Die Aufgabe der vorliegenden Erfindung besteht somit darin, ein Verfahren zum Anpassen eines Hörgerätesystems mit zwei Hörgeräten bereitzustellen, das zu einer individuelleren Einstellung der binauralen Versorgung führt.The object of the present invention is thus to provide a method for adapting a hearing device system with two hearing aids, which leads to a more individual adjustment of the binaural supply.
Erfindungsgemäß wird diese Aufgabe gelöst durch ein Verfahren zum Anpassen eines Hörgerätesystems mit einem ersten Hörgerät zur Versorgung des ersten Ohrs und einem zweiten Hörgerät zur Versorgung des zweiten Ohrs eines Hörgeräteträgers durch Einstellen des ersten Hörgeräts anhand von audiometrischen Daten über das erste Ohr, wobei zum Einstellen des ersten Hörgeräts auch eine Hardwareinformation über das zweite Hörgerät verwendet wird.According to the invention, this object is achieved by a method for adapting a hearing device system with a first hearing device for supplying the first ear and a second hearing device for supplying the second ear of a hearing device wearer by setting the first hearing device on the basis of audiometric data on the first ear, wherein for setting the First hearing aid also hardware information on the second hearing aid is used.
Dadurch können die beiden Hörgeräte abhängig von der Hardware des jeweils anderen Hörgeräts in einem binauralen Hörsystem konfiguriert werden.As a result, the two hearing aids can be configured in a binaural hearing system depending on the hardware of the respective other hearing aid.
In vorteilhafter Weise kann bei dem erfindungsgemäßen Verfahren erreicht werden, dass auf der Basis eines binauralen Audiogramms die Hörgeräte symmetrisch eingestellt werden, wenn zum Einstellen des ersten Hörgeräts auch audiometrische Daten über das zweite Ohr herangezogen werden.Advantageously, it can be achieved in the method according to the invention that the hearing aids are adjusted symmetrically on the basis of a binaural audiogram if audiometric data about the second ear are also used for setting the first hearing device.
Vorzugsweise umfassen die audiometrischen Daten eine Luftleitungshörschwelle, eine Knochenleitungshörschwelle und/oder eine Unbehaglichkeitsschwelle. Mit diesen Schwellen kann beispielsweise die Restdynamik beispielsweise am linken Ohr für die Einstellung des Hörgeräts am rechten Ohr berücksichtigt werden.Preferably, the audiometric data includes an airline hearing threshold, a bone conduction threshold and / or a discomfort threshold. With these thresholds, for example, the residual dynamics, for example, on the left ear for the hearing aid setting on the right ear is taken into account.
Darüber hinaus ist es von Vorteil, wenn die Regelungszeit für die Kompression in dem ersten Hörgerät an die Restdynamik des zweiten Ohrs angepasst ist. Damit kann beispielsweise für die Kompression eine kürzere Einschwingzeit für das erste Hörgerät gewählt werden, wenn dies die Restdynamik zwar nicht des ersten aber des zweiten Ohrs erfordert. Durch die Wahl gleicher Zeitkonstanten auf beiden Seiten wird für den Schwerhörigen ein symmetrischer Höreindruck erreicht.Moreover, it is advantageous if the control time for the compression in the first hearing device is adapted to the residual dynamics of the second ear. Thus, for example, a shorter settling time for the first hearing aid can be selected for the compression, if this does not require the residual dynamics of the first but of the second ear. By choosing the same time constants on both sides, a symmetrical hearing impression is achieved for the hard of hearing.
Darüber hinaus kann eine Spitzenbeschneidung des Ausgangssignals des ersten Hörgeräts in Abhängigkeit von den Daten des zweiten Ohrs oder des zweiten Hörgeräts erfolgen. Außerdem kann auch eine Einstellung eines Mikrophonmodus (Omnidirektional, Direktional, Automatik) oder einer Lautstärke und Tonhöhe eines Signaltons des ersten Hörgeräts in Abhängigkeit dieser Daten erfolgen. Ebenso kann eine Regeltiefe einer Störgeräuschbefreiung des ersten Hörgeräts in Abhängigkeit der Daten des zweiten Ohrs oder des zweiten Hörgeräts eingestellt werden. Generell können so Verarbeitungsalgorithmen im ersten Hörgerät unter Berücksichtigung des Hörverlusts am zweiten Ohr bzw. unter Berücksichtigung der Daten des zweiten Hörgeräts besser an den individuellen Hörverlust angepasst werden.In addition, a peak cropping of the output signal of the first hearing device can be effected as a function of the data of the second ear or the second hearing device. In addition, a setting of a microphone mode (omnidirectional, directional, automatic) or a volume and pitch of a beep of the first hearing aid in response to this data can be done. Likewise, a regulation depth of a noise suppression of the first hearing device can be set as a function of the data of the second ear or of the second hearing device. In general, processing algorithms in the first hearing device can thus be better adapted to the individual hearing loss, taking into account the hearing loss at the second ear or taking into account the data of the second hearing device.
Die oben genannte Hardwareinformation kann den Gerätetyp, nämlich ein IdO oder ein HdO, betreffen. Somit lässt sich das Gerätepaar in seinem Zusammenwirken besser an den individuellen Hörverlust anpassen.The above-mentioned hardware information may relate to the device type, namely, an IdO or a BTE. Thus, the pair of devices can be better adapted to the individual hearing loss in its interaction.
Die Hardwareinformation kann ferner den Verstärkertyp oder die Schallübertragung innerhalb des zweiten Hörgeräts betreffen. Insbesondere kann sich die Hardwareinformation auf eine akustische Eigenschaft einer Otoplastik des zweiten Hörgeräts beziehen. Somit können bei der Anpassung beispielsweise der akustische Einfluss von Tragehaken, Schallschläuchen und dergleichen sowie andere Gerätedaten des jeweils anderen Hörgeräts berücksichtigt werden.The hardware information may further relate to the type of amplifier or the sound transmission within the second hearing device. In particular, the hardware information can relate to an acoustic property of an ear device of the second hearing device. Thus, in the adaptation, for example, the acoustic influence of wearing hooks, sound tubes and the like and other device data of the other hearing aid are taken into account.
Die vorliegende Erfindung ist anhand der beigefügten Zeichnungen näher erläutert, in denen zeigen.
- FIG 1
- den prinzipiellen Aufbau eines Hörgeräts gemäß dem Stand der Technik;
- FIG 2
- eine symbolische Darstellung der erfindungsgemäßen, wechselseitigen Nutzung von Audiogrammen bei der Anpassung von Hörgeräten eines binauralen Hörsystems;
- FIG 3
- ein Audiogramm eines ersten Hörgeräteträgers für seine rechte Seite;
- FIG 4
- ein Audiogramm des ersten Hörgeräteträgers für seine linke Seite;
- FIG 5
- ein Audiogramm eines zweiten Hörgeräteträgers für seine rechte Seite und
- FIG 6
- ein Audiogramm des zweiten Hörgeräteträgers für seine linke Seite.
- FIG. 1
- the basic structure of a hearing aid according to the prior art;
- FIG. 2
- a symbolic representation of the invention, mutual use of audiograms in the adaptation of hearing aids of a binaural hearing system;
- FIG. 3
- an audiogram of a first hearing aid wearer for his right side;
- FIG. 4
- an audiogram of the first hearing aid wearer for his left side;
- FIG. 5
- an audiogram of a second hearing aid wearer for his right side and
- FIG. 6
- an audiogram of the second hearing aid wearer for his left side.
Die nachfolgend näher geschilderten Ausführungsformen stellen bevorzugte Ausführungsbeispiele der vorliegenden Erfindung dar.The embodiments described in more detail below represent preferred embodiments of the present invention.
Das Problem der unterschiedlichen Einstellungen eines binauralen Hörgerätesystems wird also dadurch gelöst, dass eine Anpasseinrichtung bzw. eine Anpasssoftware für ein binaurales Hörsystem bei der Anpassung eines Geräts von der einen Seite Informationen über die andere Seite (Hörverlust, verwendetes Gerät, Anpassstrategie, etc.) abfragt und für die Voreinstellung des binauralen Hörsystems verwendet. Somit wird eine ansonsten übliche beidseitige monaurale Anpassung dahingehend ergänzt, dass anhand von Informationen über den binauralen Hörverlust bzw. die binaurale Gerätekombination die Voreinstellung der Hörgeräte weniger allgemein für den individuellen Hörverlust erfolgt und damit dezidierter auf den aktuell vorliegenden Hörverlust eingegangen werden kann.The problem of different settings of a binaural hearing aid system is thus solved by an adaptation device or an adaptation software for a binaural hearing system in the adaptation of a device from the one side information about the other side (hearing loss, used device, fitting strategy, etc.) queries and used for presetting the binaural hearing system. Thus, an otherwise common two-sided monaural adaptation is supplemented to the effect that based on information about the binaural hearing loss or the binaural device combination, the default setting of the hearing less generally for the individual hearing loss and thus more focused on the currently existing hearing loss can be received.
Darüber hinaus können beliebige Kriterien, von denen bislang aufgrund der Gefahr seitendifferenter Einstellungen Abstand genommen wird, um die Information des gegenüberliegenden Hörverlusts ergänzt werden. Damit ist eine zuverlässigere Klassifikation des Hörverlusts zu erreichen. Ferner ist die Gefahr seitendifferenter Einstellungen dadurch erheblich reduziert. Davon unberührt bleiben frequenz- und pegelabhängige Verstärkungswerte, die weiterhin für jede Seite individuell berechnet werden.In addition, any criteria, which has hitherto been disregarded due to the risk of side-by-side adjustments, may be supplemented by the information of the opposite hearing loss. This provides a more reliable classification of hearing loss. Furthermore, the risk of page-different settings is significantly reduced. This does not affect frequency- and level-dependent gain values, which are still calculated individually for each page.
Durch die Berücksichtigung binauraler Gegebenheiten bei der Anpassung, insbesondere der Erstanpassung, sind beispielsweise die nachfolgend aufgezählten Ausführungen der Grundeinstellung eines Hörsystems möglich. Über die hier aufgelisteten Beispiele hinaus sind jedoch weitere Ausführungsmöglichkeiten denkbar.
- a) Die
FIG 3 zeigen ein rechtes Audiogramm und ein linkes Audiogramm eines Hörgeschädigten. Der Hörbereich über der Frequenz wird jeweils durch eine Luftleitungshörschwelle 14, 15 und eine Unbehaglichkeitsschwelle 16, 17 begrenzt. Es ist zu erkennen, dass dieund 4 14, 15 im linken Audiogramm und im rechten Audiogramm unterhalbLuftleitungshörschwellen von 2 kHz den gleichen Verlauf besitzen. Im höheren Spektralbereich ist der Hörverlust links etwas stärker. Da die 16, 17 links und rechts hier den gleichen Verlauf besitzen, ist die Restdynamik bei hohen Frequenzen auf der linken Seite deutlich geringer als auf der rechten Seite. In dem gewählten Beispiel vonUnbehaglichkeitsschwellen FIG 4 liegt die Restdynamik unter 10 dB. Für derartige Hörverluste mit deutlich reduzierter Restdynamik (tonaudiometrische Differenz zwischen Luftleitungshörschwelle und Unbehaglichkeitsschwelle) schlägt die Theorie kürzere Ein- und Ausschwingzeiten der eingangsbezogenen Kompression (AGCi) vor. Nur so kann verhindert werden, dass ein sich verändernder Eingangspegel zu einem Ausgangspegel außerhalb des schmalen Restdynamikbereichs führt. Daher werden in Frequenzbereichen mit geringer Restdynamik kürzere Ein- und Ausschwingzeiten für die Grundeinstellung angestrebt. Hierzu kann ein zu definierender Schwellwert (z. B. Restdynamik < 15 dB) herangezogen werden. Die Ein- und Ausschwingzeiten prägen den Klang eines Hörsystems maßgeblich. Da in dem Beispiel derFIG 3 die Restdynamik in dem hohen Frequenzbereich auf der rechten Seite größerund 4als 10 dB und auf der linken Seite kleinerals 10 dB ist, würde bei einerSchwelle von 10 dB auf der rechten Seite die Kompression mit einer geringen Regelungsgeschwindigkeit und auf der linken Seite mit einer hohen Regelungsgeschwindigkeit eingestellt werden. Die entsprechenden unterschiedlichen Ein- und Ausschwingzeiten für die rechte und linke Seite würden einen deutlich seitendifferenten Höreindruck hervorrufen, obwohl das Tonaudiogramm annähernd symmetrisch erscheint. Durch die Abfrage des binauralen Hörverlusts können in diesem Fall symmetrische Zeitkonstanten für die eingangsbezogene Kompression gewählt werden. Gleiches gilt in diesem Beispiel für eine Konfiguration möglicher Spitzenbeschneidungen (adaptive Filter, Ausgangspegelbegrenzung) für den sich ebenfalls hörverlust- und restdynamikabhängige Regeltiefen anbieten. Diese Algorithmen können dann ebenfalls symmetrisch für beide Hörsysteme konfiguriert werden. - b) Hörgeschädigte mit hohen Hörverlusten (vergleiche rechtes und linkes Audiogramm in den
FIG 5 und 6 ) profitieren in der Regel nur wenig von adaptiven Filtern zur Störgeräuschreduktion. Teilweise werden diese Einstellungen sogar abgelehnt, da das Gerät "zu trocken" klingt. Auch hier böte es sich an, in Abhängigkeit vom Hörverlust die Wirkung einer Störgeräuschbefreiung zu konfigurieren. Nach bisheriger Praxis wird davon jedoch Abstand genommen, da ein wie auch immer gestaltetes Kriterium zu seitendifferenten Einstellungen führen kann. Über die zusätzliche Abfrage des binauralen Hörverlusts kann jedoch auch in diesem Beispiel der vorliegende Hörverlust genauer klassifiziert und einzelne Parameter, wie die Regeltiefe der Störgeräuschbefreiung, in Abhängigkeit vom Hörverlust konfiguriert werden, ohne Gefahr zu laufen, nach der Grundeinstellung mit seitendifferenten Einstellungen zu enden. DieFIG 5 und 6 zeigen für den hier vorliegenden hohen Hörverlust nicht nur dieLuftleitungshörschwellen 18 und 19 sowie dieUnbehaglichkeitsschwellen 20 und 21 jeweils für die rechte und linke Seite, sondern auch dieKnochenleitungshörschwellen 22und 23. Während dieKnochenleitungshörschwelle 22 auf der rechten Seite deutlich über der Luftleitungshörschwelle 18 liegt, liegt dieKnochenleitungshörschwelle 23 auf der linken Seite unmittelbar auf derLuftleitungshörschwelle 19. Auch diese Art des unterschiedlichen Hörverlustes auf beiden Seiten kann bei der Anpassung beider Hörgeräte berücksichtigt werden, indem die beiden Leitungshörschwellen jeweils auch für die Anpassung des Geräts auf der anderen Seite heranzogen werden. Dies kann ebenfalls einen Beitrag dazu leisten, seitendifferente Einstellungen zu vermeiden. - c) Die Abfragemöglichkeit des gegenüberliegenden Hörgeräts lässt weitere Möglichkeiten zur individuelleren Hörgeräteanpassung zu. So kann das Beispiel b) dahingehend modifiziert werden, dass abgefragt wird, ob beidseitig ein Hörsystem für hochgradig Schwerhörige verwendet wird. In diesem Fall können einzelne Parameter, wie die Regeltiefe einer Störgeräuschbefreiung, in Abhängigkeit von dem aktuell verwendeten Gerätepaar konfiguriert werden. Auf diese Weise kann beispielsweise der Hörgeräte- bzw. Verstärkertyp des einen Hörgeräts zur Anpassung des anderen Hörgeräts herangezogen werden.
- a) The
3 and 4 show a right audiogram and a left audiogram of a hearing impaired person. The audible range over the frequency is limited in each case by an air 14, 15 and aline hearing threshold 16, 17. It can be seen that the airdiscomfort threshold 14, 15 in the left audiogram and in the right audiogram below 2 kHz have the same course. In the higher spectral range the hearing loss on the left is a bit stronger. Since theline hearing thresholds 16, 17 here on the left and right have the same course, the residual dynamics at high frequencies on the left side is significantly lower than on the right side. In the example ofdiscomfort thresholds FIG. 4 the residual dynamics are below 10 dB. For such hearing losses with significantly reduced residual dynamics (tonaudiometric difference between the air conduction hearing threshold and discomfort threshold), the theory proposes shorter entry and exit times of the input-related compression (AGCi). Only then can it be prevented that a changing input level leads to an output level outside the narrow residual dynamic range. Therefore, in frequency ranges with low residual dynamics, shorter settling and deceleration times are sought for the basic setting. For this purpose, a threshold value to be defined (eg residual dynamics <15 dB) can be used. The decay and release times significantly shape the sound of a hearing system. As in the example of the3 and 4 the residual dynamics in the high frequency range on the right side is greater than 10 dB and on the left side is less than 10 dB, at a threshold of 10 dB on the right side, the compression would be at a low control speed and on the left with a high Control speed can be adjusted. The corresponding different inputs and Dwell times for the right and left sides would produce a distinctly different audio experience, although the audio audiogram appears approximately symmetrical. By interrogating the binaural hearing loss, symmetric time constants for the input-related compression can be selected in this case. The same applies in this example for a configuration of possible Spitzenbeschneidungen (adaptive filters, output level limitation) for the also hearing loss and residual dynamics dependent rule depths offer. These algorithms can then also be configured symmetrically for both hearing systems. - b) Hearing impaired with high hearing losses (compare right and left audiogram in the
FIGS. 5 and 6 ) usually benefit only a little from adaptive filters for noise reduction. Sometimes these settings are even rejected because the device sounds "too dry". Here, too, it would be useful to configure the effect of noise removal depending on the hearing loss. However, according to previous practice, this is not taken into account, as a criterion of any kind can lead to page-different settings. However, the additional query of the binaural hearing loss in this example, the present hearing loss can be classified more accurately and individual parameters, such as the depth of noise removal, depending on the hearing loss can be configured without risk to end after the default setting with page-different settings. TheFIGS. 5 and 6 show for the present here high hearing loss not only the air 18 and 19 and theline hearing thresholds 20 and 21 respectively for the right and left side, but also thediscomfort thresholds 22 and 23. While thebone conduction thresholds bone conduction threshold 22 on the right side is well above the airline hearing threshold 18 , thebone conduction threshold 23 is located on the left side directly on the airline hearing threshold 19. Also, this type of different hearing loss on both sides can be considered in the adjustment of both hearing aids by the two line hearing thresholds also be adapted for the adaptation of the device on the other side. This can also help to avoid page-different settings. - c) The possibility of interrogation of the opposite hearing device allows for further possibilities for more individual hearing device adaptation. Thus, example b) can be modified in such a way that it is queried whether a hearing system is used on both sides for the severely deaf. In this case, individual parameters, such as the noise depth of a noise reduction, can be configured depending on the currently used pair of devices. In this way, for example, the hearing aid or amplifier type of a hearing aid can be used to adapt the other hearing aid.
Claims (13)
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DE102007017761.7A DE102007017761B4 (en) | 2007-04-16 | 2007-04-16 | Method for adapting a binaural hearing aid system |
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EP1983801A3 EP1983801A3 (en) | 2014-10-15 |
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EP08103409.2A Ceased EP1983801A3 (en) | 2007-04-16 | 2008-04-07 | Method for adapting a binaural hearing device system |
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EP (1) | EP1983801A3 (en) |
DE (1) | DE102007017761B4 (en) |
Cited By (3)
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EP2635046A1 (en) * | 2012-02-29 | 2013-09-04 | Bernafon AG | A method of fitting a binaural hearing aid system |
EP2305117A3 (en) * | 2009-08-28 | 2013-11-13 | Siemens Medical Instruments Pte. Ltd. | Method for adjusting a hearing aid and hearing aid adjustment device |
DE102015201945A1 (en) | 2015-02-04 | 2016-08-04 | Sivantos Pte. Ltd. | Hearing device for binaural supply and method of operation |
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US8150542B2 (en) * | 2006-06-14 | 2012-04-03 | Phonak Ag | Positioning and orienting a unit of a hearing device relative to individual's head |
CN101924977B (en) * | 2008-11-04 | 2014-03-05 | Gn瑞声达A/S | Method of adjusting signal processing parameter for first and second hearing aid and hearing aid constituting signal processor |
DK2302951T3 (en) * | 2009-09-24 | 2012-10-08 | Oticon Medical As | Method for determining a gain setting of a bone anchored hearing aid |
US9288584B2 (en) | 2012-09-25 | 2016-03-15 | Gn Resound A/S | Hearing aid for providing phone signals |
US9338566B2 (en) | 2013-03-15 | 2016-05-10 | Cochlear Limited | Methods, systems, and devices for determining a binaural correction factor |
US9324313B1 (en) | 2013-10-23 | 2016-04-26 | Google Inc. | Methods and systems for implementing bone conduction-based noise cancellation for air-conducted sound |
US8989417B1 (en) | 2013-10-23 | 2015-03-24 | Google Inc. | Method and system for implementing stereo audio using bone conduction transducers |
DE102015203855B3 (en) * | 2015-03-04 | 2016-09-01 | Carl Von Ossietzky Universität Oldenburg | Apparatus and method for driving the dynamic compressor and method for determining gain values for a dynamic compressor |
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Also Published As
Publication number | Publication date |
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EP1983801A3 (en) | 2014-10-15 |
DE102007017761B4 (en) | 2016-08-11 |
US20080253595A1 (en) | 2008-10-16 |
DE102007017761A1 (en) | 2008-10-30 |
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