Patent Grant
8311250
This application claims priority of German application No. 10 2006 019 694.5 filed Apr. 27, 2006, which is incorporated by reference herein in its entirety.
The present invention relates to a method for adjusting the amplification of a hearing aid by loudness-based or prescriptive adjustment of the amplification of the hearing aid in a lower frequency range and a different adjustment in the upper frequency range.
The optimum amplification of a hearing aid for compensating loss of hearing is conventionally determined by loudness scalings or hearing threshold-based, prescriptive adaptation formulae. These formulae describe the target amplification as a function of the frequency and the sound level. The established formulae, such as NAL-NL1 or DSL-I/O, are defined for the frequency range 0 to 8 kHz. They say nothing about target amplification in the range above 8 kHz. This is primarily due to the fact that established hearing aids can only transmit frequencies below 8 kHz. An adaptation formula for high frequencies is therefore not required. In addition there is the fact that to measure high-pitch loss of hearing special audiometers are required and implementation of a defined amplification is very difficult in this frequency range (wavelength of the same order of magnitude as auricular canal geometries). However, as a result of special broadband amplifiers and electroacoustic converters hearing aids can nowadays be produced which can transmit frequencies above 8 kHz through to 15 kHz. One problem is accordingly adjustment of amplification in this frequency range to the loss of hearing, and this constitutes the subject matter of the present invention. In addition there is the fact that acoustic feedback can significantly affect the amplification adjustment. This applies to the entire frequency range in general but in particular to the frequency range above 6 kHz.
One approach to the solution to this problem lies in a loudness-normalizing adjustment. In this case amplification across the entire frequency range is adjusted by loudness scalings (narrow band stimuli) and comparison with reference scaling in people with normal hearing in such a way that the loudness impression normalizes, i.e. a stimulus with the hearing aid is perceived to be just as loud by a person who is hard of hearing as by a subject with normal hearing and without a hearing aid. Drawbacks in this connection are however the very long measuring times for the loudness scalings and the relatively frequent acoustic feedback. In addition, for the base frequency range it has not previously been possible to provide evidence of any advantage of a loudness-based adjustment over the “rapid”, prescriptive adaptation formulae requiring only measurement of the audiogram.
A method for adjusting a hearing aid is known from publication DE 699 16 756 T2 with which the object of compensating a patient's audiogram is achieved. This is achieved in that certain frequency bands are amplified or attenuated.
A hearing aid is also known from publication DE 690 12 582 T2 in which acoustic feedback is rendered ineffective.
Publication DE 44 41 755 C1 describes a hearing aid circuit in which a first frequency channel and a second frequency channel exist in one embodiment.
Publication DE 41 25 378 C1 also discloses a hearing aid with a signal path for a lower frequency range and a further signal path for an upper frequency range.
A method for adjusting a hearing aid is known from publication DE 35 42 566 A1. In this case the user can change the steepness of the frequency response above a limit frequency.
A method for recording information in a hearing aid is also known from publication EP 1 414 271 A2. The information can be used to adjust the volume and to avoid feedback.
Publication EP 0 917 397 A1 also discloses a method for determining a set of parameters for a hearing aid. In this case the volume and feedback are again taken into account.
Finally a method for measuring the individual acoustic ratios in a human ear in which an audiogram is created is described in publication CH 678 692 A5.
The object of the present invention therefore lies in disclosing a method with which adjustment of hearing aid amplification in the higher frequency range, in particular above 8 kHz, is effectively possible with little effort and expenditure.
According to the invention this object is achieved by a method for adjusting the amplification of a hearing aid by loudness-based or prescriptive adjustment of the amplification of the hearing aid in a lower frequency range, carrying out an open-loop gain measurement in an upper frequency range adjoining the lower frequency range and fixing a maximum amplification or a frequency-dependent maximum amplification curve at least in the upper frequency range using the open-loop gain measurement.
A hybrid adjustment procedure is therefore provided in which a loudness-based or prescriptive adjustment in the lower frequency range and a different adjustment in the higher frequency range are carried out. Rapid adjustment is therefore possible in the high-frequency range since no audiometric measurements are required. In addition, adjustment of the amplification in the high-frequency range is distinguished by its robustness since feedback whistling is basically ruled out by the OLG (Open-Loop Gain) limitation.
A further advantage that should be emphasized lies in the fact that a good basic adjustment and high spontaneous acceptance by proven adaptation formulae are achieved in the base frequency range.
According to a development of the method according to the invention the feedback susceptibility is reduced by at least one narrow band filter and/or by a feedback reduction algorithm, so a higher maximum amplification or a higher maximum amplification curve may be attained. People with serious hearing damage can thereby also be catered for without feedback whistling occurring.
Starting from the maximum amplification curve, preferably at least one amplification located therebelow is obtained and the hearing aid wearer can choose one of the plurality of amplification curves for amplification. For this purpose it is advantageous to present the hearing aid wearer with sound examples, so he can interactively choose one of the plurality of amplification curves. The hearing aid wearer can make the choice with reference to everyday sounds. A subjective, optimum solution to amplification in the high-frequency range can thus quickly be found.
The amplification curve in the upper frequency range is advantageously adjusted to an amplification curve in the lower frequency range or vice versa or the two are adjusted to each other. This avoids points of discontinuity at the point of intersection between upper and lower frequency ranges.
According to a further embodiment of the present invention it is provided that amplification in the lower and/or upper frequency range is increased automatically with time. An acclimatization effect for the hearing aid wearer can be utilized as a result.
The present invention will now be described in more detail with reference to the accompanying drawings, in which:
The following exemplary embodiments described in more detail constitute preferred embodiments of the present invention.
According to
According to step S2 the amplifications or amplification curves which are to be implemented in the hearing aid are calculated from the loudness scaling or the audiogram. For this purpose prescriptive adaptation formulae are used which, for example, are known by the names NAL-NL1, DSL-I/O. Company-specific formulae as well as a loudness normalization may also be used for the amplification calculation. Ultimately an amplification curve or a family of amplification curves is obtained for the lower frequency range [0-fb Hz]. The base limit frequency fb lies, for example, at 6 kHz.
For the upper frequency range [fb-fg Hz] where fg is for example 12 kHz, what is known as an open-loop gain measurement (OLG measurement) is now carried out according to step S3. This OLG measurement can also be extended to the lower frequency range. For the OLG measurement the signal path of the hearing aid is interrupted for example, test sounds of various frequencies are digitally generated in the hearing aid, output via the hearing aid earpiece and the digital level of the signal again received by the hearing aid microphone(s) determined upstream of the interruption point. The difference from the original digital level of the test stimulus is the open-loop gain (OLG) with the aid of which the maximum possible amplification without feedback whistling (feedback limit) may be quantified. This determination of the maximum amplification corresponding to step S4 takes place for each frequency or each desired frequency band in the high frequency range [fb-fg]. A certain spacing [feedback reserve, preferably 6-12 dB] is advantageously maintained from the feedback limit to avoid feedback whistling even in the event of slight changes in the feedback path in everyday life.
The reduction in feedback susceptibility is optionally reduced by notch filters or other narrow band filters. Alternatively or additionally feedback reductive algorithms, such as oscillation detection and adaptive notch filters or feedback compensators, can be used. In each case the amplification range may be expanded hereby.
While taking account of the feedback limit (maximum amplification) and the feedback reserve a plurality of optional amplification curves are determined in step S5. For example the amplification curves consist of the maximum possible amplification in the upper frequency range Gmax (f) and reduced amplifications, derived therefrom, in the desired number. Percentage reduced curves for example, such as 75% Gmax (f), 50% Gmax (f), etc., may thus be provided. The amplification in the high-frequency range can be exactly adjusted using a plurality of bands, in particular by using a filter bank. Explicitly no prescriptive or loudness-based adjustment methods are therefore used in the high-frequency range.
The amplification curves from the low-frequency and high-frequency ranges would, as a rule, merge discontinuously. Smoothing of the discontinuous transition of the amplification stages is therefore carried out from the base frequency range to the high frequency range at f=fb according to step S6. Smoothing takes place for example by weighted addition within a frequency band [f1-f2], where f1<fb and f2>fb. In a specific example the following could apply: fb=6 kHz, f1=4 kHz and f2=8 kHz. A continuous amplification curve is therefore obtained for all amplification curves in the entire frequency range [0-fg].
In step S7 the hearing aid wearer chooses a variant that is suited to him or her from the whole family of amplification curves. For this purpose he is presented with sound examples or he can make the selection using the everyday acoustic environment. In both cases hearing situations, such as music, speech or the like, can be used (cf. step S8).
If the hearing aid wearer comes to the conclusion that the amplification in the high-frequency range is not suited to him or her, the amplification in the high-frequency range is varied according to step S5. The amplification curves of high-frequency and low-frequency ranges are subsequently smoothed again in step S6 and the hearing aid wearer can then evaluate the newly obtained amplification curve again in step S7.
If, finally, an amplification curve is okay for the hearing aid wearer this amplification curve is permanently implemented in the hearing aid. However, following selection of the amplification curve another automatic amplification increase may optionally also take place with time. The hearing aid wearer may thus gradually adjust, i.e. acclimatize, to the new hearing impression.
The above-mentioned smoothing or adjustment of the amplification curves in the high-frequency range and the low-frequency range can be described in more detail with reference to
In the higher frequency range from about 6 kHz the amplification is fixed according to a different adjustment method. For example the high-frequency fractions should be constantly amplified according to curve 5. Since the maximum amplification curve 4 intersects with the target curve 1 at about 4 kHz and with the amplification curve 5 at about 8 kHz, amplification for loud levels is limited to the maximum amplification in the range between 4 and 8 kHz. For medium and quiet levels interpolations are carried out in the range between 4 and 6 kHz which connect the amplification curve 5 or the maximum amplification curve 4 at about 6 kHz to the target amplification curve 2 or the target amplification curve 3 at 4 kHz. This results in the interpolation sections 6 and 7. A smooth transition from the respective amplification curve 1, 23 in the low-frequency range to the amplification curve 5 in the high-frequency range may thus be ensured.
Amplification in the high-frequency range can be varied according to arrow 8. An amplification curve 9 in the high-frequency range can, for example, equally be selected thereby. In this case this curve 9 is not obtained by division of the maximum amplification curve 4 by a constant factor according to the above-mentioned example either, rather the example of
| Number | Date | Country | Kind |
|---|---|---|---|
| 10 2006 019 694 | Apr 2006 | DE | national |
| Number | Name | Date | Kind |
|---|---|---|---|
| 4630305 | Borth et al. | Dec 1986 | A |
| 5276739 | Krokstad et al. | Jan 1994 | A |
| 5991417 | Topholm | Nov 1999 | A |
| 6134329 | Gao et al. | Oct 2000 | A |
| 6408273 | Quargliaro et al. | Jun 2002 | B1 |
| 7058182 | Kates | Jun 2006 | B2 |
| 7349549 | Bachler et al. | Mar 2008 | B2 |
| 20030002699 | Schulz et al. | Jan 2003 | A1 |
| 20040151332 | Danielsen et al. | Aug 2004 | A1 |
| Number | Date | Country |
|---|---|---|
| 678 692 | Oct 1991 | CH |
| 35 42 566 | Jul 1986 | DE |
| 690 12 582 | Sep 1992 | DE |
| 41 25 378 | Oct 1992 | DE |
| 44 41 755 | Jan 1996 | DE |
| 699 16 756 | Jun 2000 | DE |
| 10110258 | Aug 2002 | DE |
| 10131964 | Jan 2003 | DE |
| 10344032 | Jun 2005 | DE |
| 122005020317 | Nov 2006 | DE |
| 0845921 | Jun 1998 | EP |
| 0 917 397 | May 1999 | EP |
| 1 414 271 | Apr 2004 | EP |
| 1448022 | Aug 2004 | EP |
| 9409604 | Apr 1994 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 20070280494 A1 | Dec 2007 | US |
