Method and apparatus for feedback suppression

Abstract

A method and apparatus reduce feedback in a hearing aid. The method involves a first transfer function, which includes a feedback path, being estimated for a first section of a signal response. A power of a feedback signal from a second transfer function of the feedback path is estimated for a second section of the signal response, and a parameter of the signal processing device and/or of the feedback suppression unit is adjusted on the basis of the estimated power.

Claims

1. A method for reducing feedback in a hearing aid having an acoustoelectric transducer, a signal processing device, a feedback suppression unit and an electroacoustic transducer, which method comprises the steps of: estimating a first transfer function, which includes a feedback path via the electroacoustic transducer, an acoustic signal path from the electroacoustic transducer to the acoustoelectric transducer and via the acoustoelectric transducer back to the signal processing device and a transfer function provided by the signal processing device, for a first section of a signal response; estimating a power of a feedback signal from a second transfer function of the feedback path for a second section of the signal response, wherein the first section and the second section are disjunct or overlap only partially and the second section is secondary to the first section in respect of a propagation time, so that the first transfer function is therefore defined for an earlier time period in the signal response of the feedback path than the second transfer function and so that the second section of the signal response corresponds to a longer signal delay; and adjusting a parameter of at least one of the signal processing device or a feedback suppression unit on a basis of the power estimated.

2. The method according to claim 1, which further comprises taking the first transfer function as a basis for extrapolating the second transfer function.

3. The method according to claim 2, which further comprises determining the power of the second section of the feedback signal by means of the second transfer function.

4. The method according to claim 1, wherein the parameter adjusted indicates an adaptive compensation filter component.

5. The method according to claim 1, wherein the parameter influences a gain of a signal between the acoustoelectric transducer and the electroacoustic transducer in the signal processing device.

6. The method according to claim 4, wherein in the adjusting step, decreasing a gain by a value on a basis of the power estimated or is limited to a value on the basis of the power estimated.

7. The method according to claim 1, which further comprises adjusting a respective parameter in at least two of a plurality of disjunct or only partially overlapping frequency ranges.

8. A hearing aid, comprising: an acoustoelectric transducer; a signal processing device; a feedback suppression unit; an electroacoustic transducer; and a controller configured to: estimate a first transfer function, which includes a feedback path via said electroacoustic transducer, an acoustic signal path from said electroacoustic transducer to said acoustoelectric transducer and via said acoustoelectric transducer back to said signal processing device and a transfer function provided by said signal processing device, for a first section of a signal response; estimate a power of a feedback signal from a second transfer function of said feedback path for a second section of the signal response, wherein the first section and the second section are disjunct or overlap only partially and the second section is secondary to the first section in respect of a propagation time, so that the first transfer function is therefore defined for an earlier time period in the signal response of the feedback path than the second transfer function and so that the second section of the signal response corresponds to a longer signal delay; and adjust a parameter of at least one of said signal processing device or of said feedback suppression unit on a basis of an estimated power.

9. The hearing aid according to claim 8, wherein said controller is configured to take the first transfer function as a basis for extrapolating the second transfer function in the second section.

10. The hearing aid according to claim 9, wherein said controller is configured to determine the power of the second section of the feedback signal by means of the second transfer function.

11. The hearing aid according to claim 8, wherein the parameter influences a gain of a signal between said acoustoelectric transducer and said electroacoustic transducer in said signal processing device.

12. The hearing aid according to claim 11, wherein said controller is configured to decrease the gain by a value proportional to the estimated power.

13. The hearing aid according to claim 8, wherein said controller is configured to estimate a respective transfer function in at least two of a plurality of disjunct or only partially overlapping frequency ranges, to estimate a power of a remaining feedback signal and to adjust the parameter of said signal processing device on the basis of the estimated power.

14. The hearing aid according to claim 8, wherein said controller is part of said signal processing device.

Description

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWING

(1) FIG. 1 is an exemplary schematic illustration of a hearing aid according to the invention;

(2) FIG. 2 is a schematic flowchart for discussing a method according to the invention; and

(3) FIG. 3 is a schematic illustration in function blocks for a possible implementation of a hearing aid according to the invention.

DETAILED DESCRIPTION OF THE INVENTION

(4) Referring now to the figures of the drawings in detail and first, particularly to FIG. 1 thereof, there is shown a basic design of a hearing aid 100 according to the invention. A hearing aid housing 10, 20 incorporates one or more microphones, also called acoustoelectric transducers 2, for picking up the sound or audible signals from the environment. The invention is not limited to the in-the-ear hearing aid (ITE) shown, however, but rather can equally be used in behind-the-ear (BTE) or completely-in-canal (CIC) hearing aids. The microphones are acoustoelectric transducers 2 for converting the sound into first electrical audio signals. A signal processing device 3, which is likewise arranged in the hearing aid housing 10, 20, processes the first audio signals. The output signal from the signal processing device 3 is transmitted to a loudspeaker or receiver 4 that outputs an audible signal. The sound is transmitted to the eardrum of the device wearer, possibly via a sound tube that is fixed in the auditory canal with an ear mold. Alternatively, a different electromechanical transducer is conceivable, such as a bone conduction receiver. The power supply for the hearing aid and particularly that for the signal processing device 3 are provided by a battery 5 that is likewise integrated in the hearing aid housing 1.

(5) FIG. 2 shows the signal processing of an exemplary hearing aid 100 according to the invention as a block diagram. The hearing aid 100 has a feedback suppression unit 6 according to the invention. This has a signal connection to the signal processing device 3 in order to capture information about an audible signal picked up by the microphone 2 and a signal that is output to the receiver 4. Furthermore, the feedback suppression unit 6 is capable of using a signal connection to influence the signal processing device 3, for example to alter the gain.

(6) In this case, it is likewise conceivable for the function of the feedback suppression unit 6 to be implemented in the signal processing device 3 itself, for example as circuits in an ASIC or as a function block in the signal processing unit.

(7) FIG. 3 shows a schematic flowchart for a method according to the invention.

(8) In a step S10, the hearing aid 100 estimates a first transfer function that includes a feedback path via the electroacoustic transducer 4, an acoustic signal path from the electroacoustic transducer to the acoustoelectric transducer 2 and via the acoustoelectric transducer 2 back to the signal processing device 3 and a transfer function provided by the signal processing device 3.

(9) The estimation can be performed using an adaptive filter, for example, in which the transfer function is modeled by a parameterized function and the parameters of the transfer function are approximated using an approximation method, so that a discrepancy between the real signals that are picked up by the acoustoelectric transducer 2 or are output by the acoustoelectric transducer 4 and the signals ascertained using the parameterized function is minimized.

(10) Popular methods in this regard are least mean square (LMS or also NMLS). The transfer function of the signal processing 3 can also be ascertained from internal parameters of the signal processing 3 directly without approximation methods. This is particularly simple when the feedback suppression unit 6 is integrated in the signal processing 3.

(11) The estimation methods, such as LMS, accomplish this by processing a limited number of samples of the audio signals so as first to limit the signal delay, since an estimate cannot be computed until the samples are available in the memory, of course. Second, the need for computation power also increases, since the number of computation operations also rises with the number of samples. Therefore, in step 10, the estimation is performed only for a first section of a signal response with N samples, where N can be equal to a number of 10, 20, 50, 100, 500 or also intermediate powers of two, for example.

(12) In a step S20, a power of a feedback signal from a second transfer function of the feedback path is estimated for a second section of the signal response, the first section and the second section being disjunct or overlapping only partially and the second section being secondary to the first section in respect of a propagation time. As already explained in relation to S10, the estimation of a signal response is in reality limited to a length of a filter that has previously been denoted by the variable N. From N samples, it is possible to determine a maximum of N mutually independent parameters. Under adverse conditions, e.g. in the case of an environment with high reflection and low attenuation, it is alternatively possible for signals that are delayed by more than N samples to have significant acoustic power and to result in feedback. In order to ensure stable operation of the hearing aid 100, it may therefore be necessary to estimate a power of the signal response also in a second section of the signal response that adjoins the first section, partially overlaps it, but is essentially disjunct or even follows it at an interval of time.

(13) In one conceivable embodiment, this is accomplished by extrapolating the first estimated transfer function. A conceivable model in this case is that an attenuation is existent and the first transfer function is continued with an exponential drop and the power for the second section ascertained in this manner is estimated by forming square sums for extrapolated samples, for example.

(14) Alternatively, it is possible for the determined power at the end of the first section to be taken as an output value directly and for the power to be allowed to drop exponentially.

(15) Many other methods are conceivable that make different physical assumptions or are optimized in terms of the computation in order to estimate the power of the second section.

(16) In a step S30, a parameter of the signal processing device and/or of the feedback suppression unit is adjusted on the basis of the estimated power.

(17) If the power estimated in step S20 exceeds a threshold value, for example, a gain can be reduced or provided with a limit in the signal processing device. Conversely, it is also conceivable for the gain to be increased again when the estimated power falls below a threshold value.

(18) Alternatively, it is conceivable for one or more weighting factors for parameters of the adaptive filter, for example, to be raised or lowered in the feedback suppression unit 6.

(19) Although the invention has been illustrated and described in more detail by means of the preferred exemplary embodiment, the invention is not restricted by the disclosed examples and other variations can be derived therefrom by a person skilled in the art without departing from the scope of protection of the invention.