Method of estimating a feedback path of a hearing aid and a hearing aid

Patent metadata

Field	Value
Publication number	US-10979827-B2
Application number	US-201816498266-A
Country	US
Kind code	B2
Filing date	Mar 23, 2018
Priority date	Mar 31, 2017
Publication date	Apr 13, 2021
Grant date	Apr 13, 2021

Abstract

A method of estimating a feedback path of a hearing aid (200). The invention also relates to a hearing aid (200) adapted to carry out said method.

First claim

The invention claimed is:

1. A method of estimating a feedback path of a hearing aid comprising the steps of:
storing, in a memory of the hearing aid, at least one of a measure of the energy of a feedback test signal and an autocorrelation matrix based on a feedback test signal or a characteristic of a feedback suppression filter;
performing an in-situ feedback test by providing the feedback test signal, represented by an output signal vector x(n), using an output transducer of the hearing aid and measuring the resulting input signal using an input transducer of the hearing aid and hereby providing an input signal vector y(n) representing the measured input signal samples;
using an analytical expression to determine a feedback suppression filter vector ĥ based on the output signal vector x(n), the corresponding samples of the input signal vector y(n) and at least one of the measure of the energy of the feedback test signal and the autocorrelation matrix based on the feedback test signal or the characteristic of the feedback suppression filter, wherein the feedback suppression filter vector ĥ comprises the filter coefficients of the feedback suppression filter;
operating the hearing aid with a feedback suppressing system comprising the feedback suppression filter that is at least initially set with the determined filter coefficients.

2. The method according to claim 1 , wherein the feedback test signal is a white noise signal.

3. The method according to claim 1 , wherein the output signal vector represents a Maximum Length Sequence noise signal.

4. The method according to claim 1 , wherein the feedback test signal does not comprise parts consisting only of a pure tone.

5. The method according to claim 1 , wherein the analytical expression used to determine the feedback suppression filter vector is derived by using a Least Mean Square approach.

6. The method according to claim 2 , wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ =( P ) −1 Xy T

wherein y T is the transposed input signal vector, X is an output signal matrix formed by at least one output signal vector and P is the measure of the feedback test signal energy.

7. The method according to claim 1 , wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ =( W T XX T W ) −1 ( W T X ) y T

wherein y T is the transposed input signal vector, wherein X is an output signal matrix formed by at least one output signal vector, wherein W is a warped filter matrix and wherein the feedback suppression filter is a warped filter.

8. The method according to claim 2 , wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ =( P ) −1 ( W T W ) −1 ( W T X ) y T

wherein the feedback suppression filter is a warped filter, wherein P is the measure of the feedback test signal energy, wherein y T is the transposed input signal vector, wherein X is an output signal matrix formed by at least one output signal vector, wherein W is a warped filter matrix representing characteristics of a delay line of the warped feedback suppression filter and wherein (W T W) −1 is the inverse of an autocorrelation matrix of the warped filter matrix.

9. The method according to claim 8 , wherein the inverse autocorrelation matrix of the warped filter matrix (W T W) −1 is expressed in the form of a KMS matrix and is stored in the memory of the hearing aid.

10. A hearing aid comprising an input transducer, a signal processor, an output transducer, a feedback suppression filter inserted in a feedback path, and a non-volatile memory, wherein
the non-volatile memory comprises at least one of a measure of the energy of a feedback test signal and an autocorrelation matrix based on a feedback test signal or a characteristic of a feedback suppression filter, and wherein the signal processor is configured to:
perform an in-situ feedback test by providing the feedback test signal, represented by an output signal vector x(n), using an output transducer of the hearing aid and measuring the resulting input signal using an input transducer of the hearing aid and hereby providing an input signal vector y(n) representing the measured input signal samples;
use an analytical expression to determine a feedback suppression filter vector ĥ based on the output signal vector x(n), the corresponding samples of the input signal vector y(n) and at least one of the measure of the energy of the feedback test signal and the autocorrelation matrix based on the feedback test signal or the characteristic of the feedback suppression filter, wherein the feedback suppression filter vector ĥ comprises the filter coefficients of the feedback suppression filter; and
operate the hearing aid with a feedback suppressing system comprising the feedback suppression filter that is at least initially set with the determined filter coefficients.

11. The hearing aid according to claim 10 , wherein the feedback test signal is a white noise signal.

12. The hearing aid according to claim 11 wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ =( P ) −1 Xy T

wherein y T is the transposed input signal vector, X is an output signal matrix formed by at least one output signal vector and P is the measure of the feedback test signal energy.

13. The hearing aid according to claim 11 , wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ w =( P ) −1 ( W T W ) −1 ( W T X ) y T

wherein the feedback suppression filter is a warped filter, wherein P is the measure of the feedback test signal energy, wherein y T is the transposed input signal vector, wherein X is an output signal matrix formed by at least one output signal vector, wherein W is a warped filter matrix representing characteristics of a delay line of the warped feedback suppression filter and wherein (W T W) −1 is the inverse of an autocorrelation matrix of the warped filter matrix.

14. The hearing aid according to claim 10 , wherein the analytical expression used to determine the feedback suppression filter vector ĥ is given as:
ĥ =( W T XX T W ) −1 ( W T X ) y T

wherein y T is the transposed input signal vector, wherein X is an output signal matrix formed by at least one output signal vector, wherein W is a warped filter matrix and wherein the feedback suppression filter is a warped filter.

Assignees

• Widex As

Inventors

• Norgaard Peter Magnus
• Ungstrup Michael
• Thiede Thilo Volker

Classifications

• H04R25/453 Primary

  electronically · CPC title

• G10L25/21

  the extracted parameters being power information · CPC title

• H04R25/30

  Monitoring or testing of hearing aids, e.g. functioning, settings, battery power · CPC title