EP1983801A2 - Method for customising a binaural hearing device system - Google Patents

Abstract

The method involves configuring a left hearing device (10) with reference to audio metric data about an ear and using hardware information about a right hearing device (11). Audiometric data about another ear is based on the configuration of the left hearing device. A selected regulation time for the compression in the left hearing device is made shorter than a residual dynamic range of the latter ear. The hardware information is concerned with an acoustic characteristic of an otoplastic of the right hearing device.

Description

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. 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.

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. 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.

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.

From the publication WO 2005/086537 A1 For example, a fitting device for hearing aids is known. 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. In addition, 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.

From the patent DE 102 28 632 B3 is a binaural hearing aid supply for directional hearing known. In this case, 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.

Furthermore, the patent discloses DE 10 2004 051 325 B3 a method for adjusting the transmission characteristic of a hearing aid. In particular, 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.

In addition, in the document DE 196 24 092 B4 a compression circuit for hearing aids described. The compression increases relatively below the individual discomfort threshold, so that the hearing is not endangered by loud sounds.

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.

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.

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.

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.

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.

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.

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.

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.

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.

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.

The present invention is explained in more detail with reference to the accompanying drawings, in which show.

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.

The embodiments described in more detail below represent preferred embodiments of the present invention.

FIG. 2 symbolically shows an inventive fitting method, as it can be carried out for example in an audiologist. In this case, 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. Before the adaptation were made by the left side of the hearing impaired a left audiogram 12 and a right audiogram 13 determined. In the adaptation of the left hearing aid 10, not only the left audiogram 12 but also the right audiogram 13 are considered here according to the invention. In the same way, in addition to the right-hand audiogram 13, 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. Thus, for example, 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. 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.

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.

1. a) Die FIG 3 und 4 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 die Luftleitungshörschwellen 14, 15 im linken Audiogramm und im rechten Audiogramm unterhalb von 2 kHz den gleichen Verlauf besitzen. Im höheren Spektralbereich ist der Hörverlust links etwas stärker. Da die Unbehaglichkeitsschwellen 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 von 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 der FIG 3 und 4 die Restdynamik in dem hohen Frequenzbereich auf der rechten Seite größer als 10 dB und auf der linken Seite kleiner als 10 dB ist, würde bei einer Schwelle 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.
2. 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. Die FIG 5 und 6 zeigen für den hier vorliegenden hohen Hörverlust nicht nur die Luftleitungshörschwellen 18 und 19 sowie die Unbehaglichkeitsschwellen 20 und 21 jeweils für die rechte und linke Seite, sondern auch die Knochenleitungshörschwellen 22 und 23. Während die Knochenleitungshörschwelle 22 auf der rechten Seite deutlich über der Luftleitungshörschwelle 18 liegt, liegt die Knochenleitungshörschwelle 23 auf der linken Seite unmittelbar auf der Luftleitungshörschwelle 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.
3. 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.

By considering binaural conditions in the adaptation, in particular the Erstanpassung, for example, the following enumerated embodiments of the basic setting of a hearing aid are possible. Beyond the examples listed here, however, further implementation options are conceivable.

1. 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 line hearing threshold 14, 15 and a discomfort threshold 16, 17. It can be seen that the air line hearing thresholds 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 the discomfort 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 of 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 the 3 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.
2. 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. The FIGS. 5 and 6 show for the present here high hearing loss not only the air line hearing thresholds 18 and 19 and the discomfort thresholds 20 and 21 respectively for the right and left side, but also the bone conduction thresholds 22 and 23. While the bone conduction threshold 22 on the right side is well above the air line hearing threshold 18 , the bone conduction threshold 23 is located on the left side directly on the air line 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.
3. 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)

A method for adjusting a hearing aid system with a first hearing aid (10) for supplying the first ear and a second hearing aid (11) for supplying the second ear of a hearing aid wearer Setting the first hearing device (10) on the basis of audiometric data (12) via the first ear, characterized in that - For setting the first hearing aid (10) and a hardware information on the second hearing aid (11) is used. The method of claim 1, wherein audiometric data (12, 13) is used via the second ear to adjust the first hearing aid (10). The method of claim 2, wherein the audiometric data (12, 13) comprises a bone conduction threshold (22, 23). The method of claim 2 or 3, wherein the audiometric data (12, 13) comprises a discomfort threshold (16, 17, 20, 21). Method according to one of the preceding claims, wherein the smaller the residual dynamics of the second ear, the shorter the control time for the compression in the first hearing aid (10). Method according to one of claims 2 to 5, wherein a Spitzenbeschneidung the output signal of the first hearing aid (10) in dependence on the audiometric data of the second ear or the hardware information on the second hearing aid. Method according to one of claims 2 to 5, wherein the volume and pitch of the beeps of the first hearing aid (10) in dependence on the audiometric data of the second ear or the hardware information on the second hearing aid is set. Method according to one of the preceding claims, wherein the microphone mode of the first hearing aid (10) in dependence on the audiometric data of the second ear or the hardware information on the second hearing aid is set. Method according to one of the preceding claims, wherein a depth of adjustment of noise removal of the first hearing aid (10) in dependence on the audiometric data of the second ear or the hardware information on the second hearing aid (11). Method according to one of the preceding claims, wherein the hardware information relates to the device type, namely an IdO, a BTE, an implantable hearing aid or a vibrotactile hearing aid. The method of any one of the preceding claims, wherein the hardware information relates to the type of amplifier. Method according to one of the preceding claims, wherein the hardware information relates to a sound transmission within the second hearing device (11). Method according to one of the preceding claims, wherein the hardware information relates to an acoustic property of an ear device of the second hearing aid.

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