SELF-CALIBRATION OF MULTI-MICROPHONE NOISE REDUCTION SYSTEM FOR HEARING ASSISTANCE DEVICES USING AN AUXILIARY DEVICE

• US 20150289064A1
• Filed: 04/03/2015
• Published: 10/08/2015
• Est. Priority Date: 04/04/2014
• Status: Active Grant

• Current Assignee: Oticon A/S (William Demant Fonden)
• Original Assignee: Oticon A/S (William Demant Fonden)
• Inventors: JENSEN, Jesper, PEDERSEN, Michael Syskind
• Granted Patent: US 9,591,411 B2
• Time in Patent Office: Days
• US Class Current: 1/1
• CPC Class Codes: A61N 1/36039 fitting procedures
• CPC Class Codes: H04R 2225/41 Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
• CPC Class Codes: H04R 2430/23 Direction finding using a sum-delay beam-former
• CPC Class Codes: H04R 25/30 Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
• CPC Class Codes: H04R 25/407 Circuits for combining signals of a plurality of transducers
• CPC Class Codes: H04R 25/50 Customised settings for obtaining desired overall acoustical characteristics
• CPC Class Codes: H04R 25/558 Remote control, e.g. of amplification, frequency
• CPC Class Codes: H04R 3/002 Damping circuit arrangements for transducers, e.g. motional feedback circuits

Abstract

The application relates to hearing assistance system (use and method) for calibrating a noise reduction system of a hearing assistance device. The system comprises a hearing assistance device, and an auxiliary device. The hearing assistance device comprises a multitude of input units, and a multi-channel beamformer filtering unit configured to determine filter weights for a beamformed signal. The system further comprises a user interface for activating a calibration mode. The auxiliary device comprises an output transducer for converting an electric calibration signal to an acoustic calibration sound signal. The system is configured to estimate a look vector for a target signal originating from a target signal source located at a specific location relative to the user based on the acoustic calibration sound signal.

Claims

1. A hearing assistance system comprising a hearing assistance device and an auxiliary device;

the hearing assistance device comprising

HD-a) a multitude M of input units IU_i, i=1, . . . , M, adapted to provide or to receive a time-frequency representation S_i(k,m) of a signal s_i(n) at an i^th input unit in a number of frequency bands and a number of time instances, k being a frequency band index, m being a time index, n representing time, and M being larger than or equal to two; and

HD-b) a multi-input unit noise reduction system comprising a multi-channel beamformer filtering unit operationally coupled to said multitude of input units IU_i, i=1, . . . , M, and configured to determine filter weights w(k,m) for providing a beamformed signal Y(k,m), wherein signal components from other directions than a direction of a target signal source are attenuated, whereas signal components from the direction of the target signal source are left un-attenuated or are attenuated less than signal components from said other directions;

the system comprising a user interface for activating a calibration mode in the auxiliary device and in the hearing assistance device;

the auxiliary device comprising

AD-a) an output transducer for converting an electric signal representative of a sound to an acoustic sound signal;

AD-b) a control unit for forwarding an electric calibration signal to the output transducer when said calibration mode is activated;

wherein the system is configured to estimate a look vector d(k,m) for a target signal originating from a target signal source located at a specific location relative to the user based on the electric calibration signal converted by the output transducer of the auxiliary device to an acoustic calibration sound signal, wherein said specific location relative to the user is the location of said output transducer of the auxiliary device.

2. A hearing assistance system according to claim 1 wherein said auxiliary device comprises said user interface for activating the calibration mode.

3. A hearing assistance system according to claim 1 wherein said hearing assistance device and said auxiliary device are adapted to establish a wireless link between them.

4. A hearing assistance system according to claim 3 adapted to communicate one or more of the start time of the calibration signal, the specific location of the auxiliary device relative to the user, and characteristics of the calibration signal to the hearing assistance device.

5. A hearing assistance system according to claim 1 configured to determine filter weights for one or more fixed beamformers based on said estimate of a look vector d(k,m).

6. A hearing assistance system according to claim 1 configured to determine filter weights for one or more fixed beamformers based an assumption of the spatial noise distribution.

7. A hearing assistance system system according to claim 5 wherein said fixed beamformers comprise:

an enhanced omni beamformer for providing a beamformed signal E_omni,(k,m) with a gain of 0 dB when a signal is received from the target direction/location, and/or

a target cancelling beamformer for providing a target-cancelling beamformed signal C_R(k,m), which ideally rejects a signal played from the target direction/location.

8. A hearing assistance system according to claim 1 wherein said hearing assistance device further comprises a single channel post-processing filter unit operationally coupled to said multi-channel beamformer filtering unit and configured to provide an enhanced signal Ŝ

(k,m).

9. A hearing assistance system according to claim 1 comprising a control unit configured to compare beamformer weights w_cal(k,m) resulting from the calibration to a set of default beamformer weights w_pd(k,m) and to provide a difference measure.

10. A hearing assistance system according to claim 9 adapted to provide that default beamformer weights are used, if the difference measure is above a predefined threshold.

11. A hearing assistance system according to claim 1 configured to provide that the calibration signal is adapted to the current noise level and/or spectrum, by shaping the calibration signal to ensure a predetermined calibration signal to noise ratio and/or the duration in time of the calibration signal.

12. A hearing assistance system according to claim 5 wherein the fixed beamformer(s) is/are determined from the estimated look vector and an estimate of the inter-input unit covariance matrix {circumflex over (R)}_vv(k,m) of the noise v_i impinging on the respective input units (i=1, 2, . . . , M).

13. A hearing assistance system according to claim 12 wherein an estimate of the noise covariance matrix, termed {circumflex over (R)}_vv,diffuse(k,m), is predetermined and stored in a memory of the hearing assistance device.

14. A hearing assistance system according to claim 1 comprising a voice activity detector for estimating whether or not a target signal is present or dominating at a given point in time.

15. A hearing assistance system according to claim 1 wherein the auxiliary device comprises, a remote control, an audio gateway device, a mobile telephone, or a computer.

16. A hearing assistance system according to claim 1 wherein the auxiliary device comprises or forms part of a fitting system.

17. A hearing assistance system according to claim 1 comprising a sensor for allowing a user a) to locate the auxiliary device at a predetermined angle and/or height and/or distance relative to the user and/or b) to track the location of the auxiliary device relative to the user.

18. A hearing assistance system according to claim 1 wherein the hearing assistance device comprises a hearing instrument adapted for being located at the ear or fully or partially in the ear canal of a user, or for being fully or partially implanted in the head of a user, a headset, an earphone, an ear protection device or a combination thereof.

20. Use of an audio processing system as claimed in claim 1.

19. A method of calibrating a multi-input unit noise reduction system of a hearing assistance device, the method comprising

a) Providing a hearing assistance device comprising the multi-input unit noise reduction system and a multitude M of input units, where M is larger than or equal to two;

b) Providing an auxiliary device comprising an output transducer;

c) Locating the auxiliary device within a predetermined distance of a user wearing said hearing assistance device, thereby defining a specific location of (the output transducer of) the auxiliary device relative to (the hearing assistance device of) the user;

d) Initiating a calibration mode in the hearing assistance device and the auxiliary device;

e) Providing an acoustic calibration signal by the output transducer of the auxiliary device;

f) Providing a time-frequency representation S_i(k,m) of the calibration signal s_i(n) at an i^th input unit, i=1, 2, . . . , M, in a number of frequency bands and a number of time instances, k being a frequency band index and m being a time index, the method further comprising

g) estimating a look vector d(k,m) for a target signal originating from a target signal source located in said specific location relative to the user based on said time-frequency representation S_i(k,m) of the calibration signal s_i(n), i=1, 2, . . . , M; and

h) determining optimal beam former weights based on said estimated look vector