Abstract: For reducing feedback-conditioned oscillations in a hearing aid device, microphone signals of a first microphone and of a distanced, second microphone are compared to one another. When oscillations are detected at the same frequency in both microphone signals, these oscillations are determined to be useful (non-feedback) tonal signals. Oscillations that are only present in one of the microphone signals, in contrast, are feedback-conditioned and are suppressed using suitable measures.

Abstract: For reducing feedback-conditioned oscillations in a hearing aid device, microphone signals of a first microphone and of a distanced, second microphone are compared to one another. When oscillations are detected at the same frequency in both microphone signals, these oscillations are determined to be useful (non-feedback) tonal signals. Oscillations that are only present in one of the microphone signals, in contrast, are feedback-conditioned and are suppressed using suitable measures.

Abstract: In a method and circuit for the amplification of input signals of a hearing aid, a compression of the signals picked up by the hearing aid ensues in a AGC circuit dependent on the acquirable signal level. For assuring a dynamics compression, the method and circuit implement a signal analysis for the recognition of the acoustic situation in addition to the acquisition of the signal level of the input signal, and the behavior of the dynamics compression is adaptively varied on the basis of the result of the signal analysis. A fixed input-output characteristic that is usually defined on the basis of stationary signals forms the basis of parameter settings of a dynamics compression has been used in conventional calculations. The resulting time behavior for the compensation of input signals by a hearing aid exhibits an effectively different compression given time-variable, modulated signals, particularly given speech. The result is that the compression parameters are not optimally set for all signals.

Abstract: A digital hearing aid is employable for tinnitus therapy, as well as for retraining tinnitus therapy, in combination with correction of other hearing impairments of a user of the hearing aid. For this purpose, the hearing aid contains a signal processing chain, between a hearing aid input and a hearing aid output, which is responsible for producing a useful signal by acting on the input signal in a manner to correct the hearing impairment of a user of the hearing aid. The signal processing chain also includes an arrangement for generating a tinnitus therapy signal, which is combined in the signal processing chain with the useful signal, dependent on a mode of operation which has been selected or set.

Abstract: A hearing aid system with a hearing aid has a matching arrangement with a first memory for several parameter sets available for selection for each of several hearing situations, an input unit for selecting a current hearing situation and for selecting one of the several parameter sets available for this hearing situation, and a second memory for allocation data that identify the parameter sets selected for each hearing situation. For the determination of an optimal parameter set for each of several hearing situations, an optimal user-specific parameter set is allocated to each hearing situation as it arises during an optimization phase. After the optimization phase, the allocation data are evaluated for the determining an optimal parameter set for each hearing situation. This parameter set is then permanently programmed as the parameter set which will be called to set the transmission characteristics of the hearing aid whenever the hearing situation allocated thereto occurs.