Siemens Audiologische Technik Gmbh

Other

Siemens Corporation

Siemans Augiologische Technik Gmbh

Sivantos Pte. Ltd.

Raimund Martin

Gerhard Pfannenmueller

Tong Fang

Peter Nikles

Joseph Sauer

Fred McBagonluri

Ullrich Sigwanz

Fred Zoels

Eduard Kaiser

Inga Holube

Jörg Bindner

Werner Hohn

Therese Velde

Reinhard Kern

A method and appertaining system implement the use of manufacturing protocols for hearing aid design such that the ability to build an instrument can be displayed as a numeric parameter based on the partial numerical and metrological contributions of all the essential parameters of the given impression, and a buildability index can be displayed as a 3D virtual image of the proposed shell or preferred shell types. The method utilizes a predefined parameter table comprising parameters to utilize for a buildability determination. The buildability index is computed based on impression shape data, selected shell type, selected number of device options, data obtained from the parameter table, and data obtained from a receiver table, and the buildability index is output to a display of a user interface device or an external system.

Hearing aid impression buildability index computation tool

For binaural hearing, a hearing aid worn at the head has two hearing apparatuses respectively allocated to the ears, with at least one of the hearing apparatuses having a transmitter and the other hearing apparatus having a receiver for an optical signal transmission from the transmitting hearing apparatus to the receiving hearing apparatus.

Hearing aid having two hearing apparatuses with optical signal

A hearing aid has a microphone, a signal processing chain having a series of signal processing levels, a signal output transducer, a memory in which at least one set of parameters allocated to a hearing situation is stored that enables matching of the parameters of the signal processing stages to the hearing impairment of the wearer. Adjustment elements independent of the signal processing stage are provided, and the allocation of the adjustment elements 9 to the individual signal processing stages can be selectively determined. Adjustment of the respective signal processing stages can be accomplished in a non-computerized manner using the adjustment elements, thereby allowing the hearing aid to be used in countries and regions wherein personal computers are not readily available or accessible.

Hearing aid which allows non-computerized individual adjustment of

A direction-sensitive hearing aid is provided with a housing, at least one signal processor, at least one microphone in communication with the signal processor as well as at least one sound opening. A simplified arrangement of operating elements is provided as well as effective shielding from electromagnetic disturbances with a continued, good directional effect given improved protection against contamination. The hearing aid is provided with a sound channel. The sound channel has at least two openings, and at least two microphones are positioned along the sound channel via which the sound within the sound channel can be acquired. The direction of the sound can be determined based on the differences in sound transit time within the sound channel.

Hearing aid wherein the direction of incoming sound is determined by

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.

Programmable hearing aid operable in a mode for tinnitus therapy

A hearing aid has at least one microphone, a digital signal conditioning stage having a signal converter, an amplifier as well as filters, and an earphone. For protection against emission of electromagnetic waves, an analog-to-digital converter is arranged in the microphone housing.

Digital hearing aid

A hearing aid that has an analog part with a Class D final amplifier stage for audio signal processing, a digital part with an interface, a memory stage as well as supply stage for generating the voltage and control signals. The hearing aid has a utilized integrated circuit which also includes a pre-amplifier stage with two inputs respectively connected to a microphone and a telephone coil, the signals from the two inputs being selectively pre-amplified individually or in common, with selectable or programmable gains. This gives the hearing aid a small structural size, a comprehensive functionality, versatile adaptability and especially low energy consumption.

Programmable hearing aid

In a hearing aid comprising an input transducer, processing circuits for useful signals including an output stage and an output transducer, the useful signals are sampled with a sampling frequency before the output stage, are converted into data words, and are also processed in discrete-time fashion. The digital data words are capable of being converted into pulse-duration-modulated signals without being reconverted into analog signals. For this purpose, the processed data words can be read into a counting circuit via at least one input which can be placed into an initial condition with counting pulses after every read-in data word. The output stage is designed as a switching amplifier and is driven with an output signal of the counting circuit.

Hearing aid

In a hearing aid having an input transducer (2), a useful signal processor (4 through 9) having an output stage (9), and an output transducer (11), whereby a first time-discrete useful signal processing is provided preceding the output stage (9), and controlled by a sampling signal, a second time-discrete useful signal processing different therefrom is simultaneously employed without disturbing influences. To that end, a second time-discrete useful signal processing with a pulse-duration modulation is provided in the output stage (9), this being formed by a delta signal, whereby the sampling signal and the delta signal are derived from only one oscillator (12).

In a circuit arrangement having a switching amplifier (10), particularly for hearing aids, for limiting a pulse-width-modulated signal (S3) that is formed for a low-frequency signal (S1) and a higher-frequency delta signal (S2), a limitation of the output signal from the switching amplifier is achieved without a reduction in gain given only slight distortions. To that end, the pulse-width-modulated signal (S3) is supplied to a circuit (5; 14; 18) which modifies the width (D1, D2, D4) of individual pulses in the pulse-width-modulated signal (S3), whose width (D1, D2, D4) is longer or/and shorter than a maximum or minimum pulse width D3; D5) prescribable by the circuit (5; 14; 18). The pulse-width-modulated signal (S5; S6) modified by the circuit (5; 14; 18) can be supplied to the switching amplifier (10) as an input signal.

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Eggolsheim, Germany

Raimund Martin