EP1307072A2 - Procédé pour actionner une prothèse auditive et prothèse auditive - Google Patents

Procédé pour actionner une prothèse auditive et prothèse auditive Download PDF

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Publication number
EP1307072A2
EP1307072A2 EP02022530A EP02022530A EP1307072A2 EP 1307072 A2 EP1307072 A2 EP 1307072A2 EP 02022530 A EP02022530 A EP 02022530A EP 02022530 A EP02022530 A EP 02022530A EP 1307072 A2 EP1307072 A2 EP 1307072A2
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EP
European Patent Office
Prior art keywords
operating state
signal
hearing aid
switching process
hearing
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP02022530A
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German (de)
English (en)
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EP1307072A3 (fr
EP1307072B1 (fr
Inventor
Eghart Fischer
Volkmar Hamacher
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Original Assignee
Siemens Audiologische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1307072A2 publication Critical patent/EP1307072A2/fr
Publication of EP1307072A3 publication Critical patent/EP1307072A3/fr
Application granted granted Critical
Publication of EP1307072B1 publication Critical patent/EP1307072B1/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/43—Electronic input selection or mixing based on input signal analysis, e.g. mixing or selection between microphone and telecoil or between microphones with different directivity characteristics
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/502—Customised settings for obtaining desired overall acoustical characteristics using analog signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/35—Electric hearing aids using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression

Definitions

  • the invention relates to a method for operating a hearing aid with an input converter for receiving an input signal and conversion into an electrical signal, a signal processing unit for processing and reinforcing the electrical signal and an output converter. Furthermore concerns the invention a hearing aid for performing the method.
  • Hearing aids are also known from the prior art, at those for further adaptation to different listening situations Algorithms for signal processing in the hearing aid on and can be turned off. These algorithms concern e.g. the compression, the reduction of interference signals or the Speech signal enhancement.
  • From DE 195 42 961 C1 is a circuit for operating a equipped with at least one variable operating parameter Hearing aid and a hearing aid known as such, wherein the operating parameter settings in a memory arrangement a starting situation and a target situation are and by means of a control unit over a certain Time interval a transition of the operating parameter from the Attitude in the initial situation in the attitude of Target situation is feasible.
  • DE 195 34 981 A1 describes a method for fine adjustment known from hearing aids, in which first in an evaluation step an assessment of the degree of optimization set on the hearing aid Parameters, for example by means of psychoacoustic Sizes, and in a subsequent optimization step an adjustment of parameters in need of improvement is carried out.
  • DE 198 59 171 C2 includes an implantable hearing aid Tinnitus maskers or noisers known in which a digital Signal processor is provided, both for processing of the audio signal and for the generation of tinnitus masking or noise function necessary signals and for the combination of the latter signals with the Audio signal is designed.
  • the object of the present invention is by on, off or Switching processes caused disruptive acoustic effects to avoid with a hearing aid.
  • This task is carried out in a method for operating a hearing aid with an input converter for receiving an input signal and converting it into an electrical signal, one Signal processing unit for processing and amplification of the electrical signal and an output converter, wherein a Switching process for transferring the hearing aid from a first one Operating state triggered in a second operating state and with a smooth transition from the first Operating state to the second operating state takes place, thereby resolved that both operating states during the switching process are present in parallel in the hearing aid, at least in the part of a signal path of the hearing aid parallel signal processing takes place in which the two Operating states differ, with a first signal, the results from the first operating state, and a second Signal resulting from the second operating state over a weighting function is linked and where the weight of the first signal during the switching process decreases and the weight of the second signal increases.
  • the task is carried out with a hearing aid of the method in that during the switching process both operating states exist in parallel in the hearing aid are and the hearing aid means for weighted linkage of a Signal resulting from the first operating state and a signal that results from the second operating state, includes.
  • the invention is used, for example around a hearing aid worn behind the ear, one in the ear portable hearing aid, an implantable hearing aid or a pocket hearing aid.
  • the hearing aid used can also Part of several devices to care for the hard of hearing comprehensive hearing aid system, e.g. Part of a hearing aid system with two hearing aids worn on the head for binaural Supply or part of a hearing aid system consisting of one device that can be worn on the head and one that can be worn on the body Processor unit.
  • the hearing aid comprises an input converter for recording an input signal. Usually serves as Input converter a microphone that records an acoustic signal and converts it into an electrical signal.
  • the hearing aid further comprises a signal processing unit for processing and frequency-dependent amplification of the electrical signal.
  • a signal processing unit for processing and frequency-dependent amplification of the electrical signal.
  • DSP digital signal processor
  • the Mode of operation by means of programs which can be transmitted to the hearing aid or parameters can be influenced. This allows the operation of the signal processing unit on the individual Hearing loss of a hearing aid wearer as well as the current one Hearing situation in which the hearing aid is currently being operated will adjust.
  • the electrical signal so changed is finally fed to an output converter.
  • This is in usually designed as a handset, the electrical output signal converts into an acoustic signal.
  • an implantable Output converter that directly with an ossicle is connected and this stimulates vibrations.
  • the signal processing can be controlled by parameters in the hearing aid.
  • Called hearing program On whole set of parameters used to adjust signal processing to serve a specific listening situation is called Called hearing program.
  • a variety of parameters are usually changed.
  • the parameters for controlling the signal processing but also certain algorithms used in signal processing Affect hearing aid. For example, by an algorithm an automatic gain control (AGC - Automatic Gain Control).
  • AGC - Automatic Gain Control Another algorithm can be used to detect and reduce interference signals.
  • a special enhancement of speech signals by one appropriate algorithm is possible.
  • hearing aids offer additional features that can be activated, deactivated or set.
  • a such a function that can be performed with the hearing aid can e.g. the microphone system affect. So with a hearing aid an omnidirectional or set up a directional reception and in the case of a directional reception, the degree of directivity of the Microphone system can be set.
  • Other functions concern for example a switchable signal for tinnitus therapy or receiving an input signal using a telephone coil.
  • Modern hearing aids therefore offer a variety of setting options, by means of which they adapt to different listening situations or individual wishes and needs of a hearing aid wearer can be customized. Changes during the Operation of the hearing aid the listening situation or the Hearing aid wearer a change in a function of the hearing aid, so a switching process is required. Under a The switching process is the switching on or off of a Algorithm, the activation or deactivation of a function or the sudden change of at least one parameter of the Signal processing understood. For example, a continuous one Change the gain using a volume control is therefore not a switching process in the sense of the invention.
  • hearing aids have become abrupt due to the switching process from a first operating state to a second operating state transferred. Compared to the first operating state an algorithm is on or in the second operating state switched off or the algorithm is functioning changed. Likewise, switching can also cause a Function of the hearing aid activated, deactivated or changed become. With the sudden change in the operating state disruptive acoustic effects and the associated irritation in the perception of sound signals. By the smooth transition from the first operating state to the second operating state according to the invention will be such Effects avoided. Trigger for changing the operating state is still activating or deactivating one Algorithm or a function or a change of one Algorithm or function.
  • the changes made are not instantaneous in full on the output via the output converter Signal off.
  • the arising with conventional hearing aids Clicks or clicks, unnatural level jumps as well as unnatural sound changes are prevented.
  • the operating state is changed by a smooth transition from the first operating state to the second operating state.
  • the method according to the invention can be switched on or off of an algorithm can be used in the same way as for Change an activated algorithm. In the latter Fall through the algorithm in the first operating state a first function and in the second operating state second function performed. This can be the case with a Algorithm for automatic gain control Change the compression characteristic mean. You can also but also algorithms that reduce the frequency response of interference signals, the raising of speech signals or the Directional characteristics concern, switched on, switched off or be changed in their function.
  • the invention can also with functions of the hearing aid be applied, behind which there is no algorithm hides.
  • a function Microphone characteristics concern. Possible functions of a Microphone systems are omnidirectional reception, directional Reception, directional first-order reception, directional Second order reception etc.
  • Tinnitus therapy may be provided at the generation of a signal for a hearing aid. If this function is activated, so in addition to that transmitted by the hearing aid Signal a signal to mask the tinnitus in the Ear canal given.
  • a switchable or switchable Function is the reception of an electromagnetic Signals by means of the telephone coil.
  • the invention provides that when switching Hearing aid from a first operating state to a second Operating state temporarily both operating states in parallel are present in the hearing aid. For example, when changing of the operating state an algorithm is switched on, so means this that during the switching process the signal processing both with the algorithm turned on and in parallel this is also done with the algorithm switched off.
  • the Results of the parallel signal processing are eventually weighted and merged. This is advantageously done not a parallel over the complete signal path of the hearing aid Signal processing, but only in the part of the Signal path of the hearing aid in which the two operating states differ. A previous and subsequent one Signal processing can therefore be used for both operating states done equally.
  • the smooth transition from the first Operating state to the second operating state is now according to an embodiment of the invention achieved in that both operating states via a weighting function are linked, the during the switching process Weight of a first signal from the first operating state results in a gradual, continuous or at most starting at 1 decreases in small jumps and the weight of one second signal, which results from the second operating state, starting at 0 gradually, continuously or at most in small jumps increases.
  • the sum of the weights is preferably at least approximately always equal to 1.
  • an algorithm for noise suppression switched on this means that in a signal path of the Hearing aid initially continues the signal processing done without this algorithm.
  • the Signal processing in a second signal path of the hearing aid with the noise suppression algorithm In parallel, the Signal processing in a second signal path of the hearing aid with the noise suppression algorithm.
  • the hearing aid Immediately in Connection to the noise reduction algorithm and to the corresponding point in the parallel signal path of the hearing aid are the two signal paths via a weighting function linked together.
  • the weight of the Noise reduction algorithm starting from 0 to 1 increased and the weight of the corresponding parallel processing without the corresponding algorithm starting from 1 lowered.
  • the sum of the weights is preferred always the same 1. So the hearing aid is automatic, "soft" and almost imperceptible from a first operating state in the transferred second operating state. Clicks or clicks, unnatural level jumps and unnatural sound changes are avoided.
  • An embodiment of the invention is characterized in that at least one parameter for controlling the signal processing in the hearing aid has a certain value in the first operating state and has a value which has changed suddenly compared to the first value in a second operating state.
  • the switchover process does not immediately have its full effect here, but instead there is a smooth transition from the first operating state to the second operating state.
  • parallel signal processing takes place at least in the sub-area of the signal processing unit of the hearing aid on which the parameter acts, on the one hand with the parameter in its initial value and on the other hand with the parameter in its end value.
  • the outputs of the parallel signal processing blocks are then added with automatically changing weighting until, at the end of the transition, only the signal branch with the parameter is active in its final value.
  • the invention is limited in this case to manually carried out adjustment processes on the hearing aid, which are carried out continuously or quasi continuously in the case of a digital hearing aid.
  • Such settings concern, for example, the volume control or settings relating to the sound. These can be set by means of operating elements, but this is not to be understood as a "switching process" in the sense of the invention.
  • the switchover process is preferably controlled by a switchover algorithm specially designed for this purpose. This determines the weighting of the two signals and, if appropriate, the point in the signal path of the hearing aid at which the two parallel paths are brought together, so that the parallel signal processing is limited to only part of the signal path if possible.
  • One embodiment of the invention provides that the duration of the switching process is adjustable. Depending on how a user may find the switching operations disturbing then the switching process is set to "harder” or "softer” become. As a rule, the duration of the switching process in Range of a few seconds can be selected.
  • Figure 1 shows a block diagram of a hearing aid 1, in which Recording an acoustic input signal both an omnidirectional Microphone 2 and one of the microphones 3 and 4 directional microphone are provided.
  • a signal processing unit 7 For education the two microphones 3 of a directional microphone system and 4 via a delay element 5 and a differential element 6 electrically interconnected.
  • the signal processing unit 7 is to compensate for individual hearing loss a hearing aid wearer through a variety of parameters adjustable.
  • several different ones can be included Parameter sets for adapting the signal processing in the hearing aid 1 to different listening situations, so-called hearing programs, provided and activated.
  • Hearing aid 1 Furthermore allows the signal processing unit 7 to activate and Setting of various algorithms for signal processing or functions of the hearing aid 1. Such algorithms can for example the frequency response, the reduction of Interference signals, the raising of speech signals, the directional microphone characteristic, compression, etc.
  • Hearing aid 1 adjustable functions are e.g. the choice of Signal input via a telephone coil 8, via the microphone 2 or via the microphone system 3, 4.
  • Another example of an adjustable function is the generation of a signal for tinnitus therapy.
  • the activation or setting of the algorithms or functions can be done manually or automatically with the hearing aid 1.
  • the hearing aid 1 can automatically determine Detect listening situations, e.g. the listening situation "environment with Noise ", and then a corresponding hearing program activate. Simultaneously with the hearing program in question then an algorithm for noise suppression is also activated.
  • this is due to the circuit unit 9 for reducing interference signals within the signal processing unit 7 illustrates.
  • the circuit unit 9 receives an input signal s (t) and at the output an output signal y (t) is supplied. It can be both for s (t) and for y (t) around vectors, i.e. one Majority of signals, act. So overall, at least a signal in the signal path of the hearing aid 1 tapped, the circuit unit for reducing interference signals 9 supplied and again after signal processing emitted into the signal path. For example, can in the circuit unit 9 filtering.
  • FIG. 2 shows the circuit unit 9 schematically in the block diagram illustrated.
  • the circuit unit 9 is on one Signal input an input signal s (t) supplied.
  • An analysis unit 11A analyzes the input signal s (t) and recognizes whether it contains an interference signal.
  • As the output signal of the A binary signal a (t) is supplied to analysis unit 11A.
  • the value 0 means that no interference signal is detected and a value of 1 is generated when a disturbance signal is detected.
  • the signal a (t) does not directly switch an algorithm for noise suppression in the computing unit 12 or off, but is initially at an input of a low pass 11B.
  • the value of the signal a (t) jumps from 0 to 1
  • the value of the signal k (t) at the output of the low pass increases 11B as a function of the time constant of the low pass 11B from 0 to 1.
  • the analysis unit 11A thus forms together with the low pass 11B a classifier 11 that is not "hard” between 0 or 1 - "No interference signal present” or “Interference signal present” - switches, but a "soft” smooth transition provided.
  • the signal k (t) is directly at an input 13A and the in a value 1-k (t) formed at a computer at an input a multiplier 13B.
  • the multiplier 13B is the input signal s (t) fed directly while it was initially the computing unit 12 passes through before being fed to multiplier 13A is.
  • the two parallel signal paths brought together again by a summer 15. In order to with a jump from a (t) from 0 to 1, those of the Computing unit 12 first performed computing operations not with full effect on the output signal y (t), but only to the extent that the signal k (t) increases. In to the same extent, the effect of the originally direct is reduced signal s (t) switched through to the output y (t).
  • the value of the signal k (t) has increased to 1, with which the computing unit 12 has its full effect at the signal output y (t) unfolded and the direct signal path bypassing the computing unit 12 is deactivated.
  • the analysis unit 11A does not Interference signals more detected in the input signal s (t), so switches the signal a (t) from 1 to 0 and the reverse process is started.
  • the invention offers the advantage that it can be switched on, off or on Switching caused noise or unnatural Sound changes in the hearing aid according to the invention be avoided. This effect is particularly at Switching processes in the hearing aid advantageous, which triggered automatically become. Often, you will find under certain external Conditions very many switching operations within short Time, for example within a few seconds. in the Embodiment this may be the case if only there is a weak interference signal. Then the output signal changes the analysis unit 11A, a (t), very often between 1 and 0, ie: "interference signal present" or "no interference signal available ".
  • the Multipliers 13A and 13B and the computing unit 14 leads this then becomes a condition in which for a long period of time both operating states are active in parallel in the hearing aid are, since the output signal k (t) of the classifier 11 none of the end values 0 or 1 reached. In the embodiment would be thus the noise reduction is only partially effective. This is one for the given starting situation weak interference signal, however, quite desirable and useful.
  • FIG. 2 shows only one possible one Embodiment of a weighting function with automatic changing weighting.
  • it is only a schematic block diagram. So are with the practical Realization still further, not shown here, the expert however, common circuit elements necessary in favor of improved clarity of presentation was waived. So, for example, during a realization A / D converter still required in digital circuit technology, around the weighting functions k (t) and 1-k (t) in to transfer digital functions.
  • FIG. 3 shows another exemplary embodiment of the invention.
  • a Hearing aid by a circuit unit 9 'a signal processing realized, namely by means of a computing unit 20 an adapted to a specific environmental situation Processing the input signal s (t).
  • the signal processing in the computing unit 20, a parameter set, in the exemplary embodiment, the “hearing program 1”.
  • the output of the computing unit 20 is identical with the output signal of the circuit unit 9 ', namely y (t).
  • the circuit unit 9 ' has a switching unit 22 on.
  • an output signal k '(t) of the low pass 25 which is generated within a certain Time period drops steadily from 1 to 0.
  • the signal k '(t) and that formed in the computing unit 26 Signal 1-k '(t) fed to a multiplier 27A or 27B.
  • the switching process between two hearing programs can also be done automatically to be triggered.
  • the invention can be based on the example of a switching process between two hearing programs analogously also on more than two programs, between which are switched can be expanded.
  • a classifier cannot cope with the current hearing situation recognize clearly, this changes very often and in short Time intervals between different listening situations. Thereby In connection with the invention there is the advantage that then several hearing programs automatically over one be operated in parallel in the hearing aid for a longer period of time. He follows the situation detection, for example by a Classifier 11 comparable circuit arrangement according to FIG. 1, so the weight of the respective listening situation is on average roughly proportional to the length of time for which the particular Hearing situation is determined.
  • FIG. 4 An example of this shows Figure 4.
  • a microphone arrangement with the microphones 30, 31 and 32 are different microphone reception characteristics adjustable.
  • There is a switch S in a first switch position so is only the omnidirectional Microphone 30 with a signal processing unit 33 connected.
  • the switch S is in the in Figure 4 shown second switching position, this is the directional Microphone 31, 32 with the signal processing unit 33 connected.
  • Such a switchable microphone system is known from the prior art.
  • the automatic one following a trigger Switching process is also in this embodiment controlled by a switching unit 37. This determines what parts of the signal processing during the switching process are to be executed in parallel and, if necessary, at which point y '' (t) in the signal path of the hearing aid joint further processing can take place. So in Embodiment the two differently weighted Signal paths in the summer 38 merged and common be reinforced.
  • the changing weighting of the parallel microphone signal paths takes place in this embodiment by a binary Signal a "(t), which when switching from an omnidirectional Received by the microphone 30 on a directional Reception by the microphone system 31, 32 changes from 1 to 0.
  • a signal k "(t) is emitted, which in the exemplary embodiment steadily falls from 1 to 0 and as one of the input signals a multiplier 40A. That in one computing unit 41 formed signal 1-k '' (t) is an input of a Multiplier 40B supplied.
  • the Multiplier 40A is from the microphone 30 Signal on, at the second input of multiplier 40B is one of the interconnected microphones 31 and 32 originating signal.
  • the circuit according to the block diagram allows a soft and smooth switching between an omnidirectional and directional microphone reception. Also in this embodiment it is possible that by switching very often at short intervals by the switching element 36, e.g. caused by a hearing situation that cannot be clearly determined, both microphone characteristics over a longer one Period in parallel in the hearing aid.
  • the smooth, smooth transition between omnidirectional and Directional microphone reception is shown by the directional diagrams A to H additionally illustrated graphically according to FIG. 6. Shown is the transition from the first operating state, in which only an omnidirectional reception takes place (Polar pattern A).
  • the diagrams B to G then show the transition for which both operating states are parallel in the hearing aid are present, i.e. both from the omnidirectional Microphone as well as the directional microphone is used an input signal is recorded and processed.
  • By the weighting of the processed that changes over time and summed microphone signals give the directional characteristics B to G.
  • the directional characteristic shows that in figure 6H illustrated kidney shape.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Electrophonic Musical Instruments (AREA)
  • Amplifiers (AREA)
  • Electrically Operated Instructional Devices (AREA)
  • Electronic Switches (AREA)
EP02022530A 2001-10-17 2002-10-07 Procédé pour actionner une prothèse auditive et prothèse auditive Expired - Lifetime EP1307072B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10150675 2001-10-17
DE10150675 2001-10-17

Publications (3)

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EP1307072A2 true EP1307072A2 (fr) 2003-05-02
EP1307072A3 EP1307072A3 (fr) 2005-10-05
EP1307072B1 EP1307072B1 (fr) 2007-12-12

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US (1) US7181033B2 (fr)
EP (1) EP1307072B1 (fr)
AT (1) ATE381237T1 (fr)
DE (1) DE50211346D1 (fr)
DK (1) DK1307072T3 (fr)
ES (1) ES2296861T3 (fr)

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DE102004010867B3 (de) * 2004-03-05 2005-08-18 Siemens Audiologische Technik Gmbh Verfahren und Vorrichtung zum Anpassen der Phasen von Mikrofonen eines Hörgeräterichtmikrofons
DE102005019149B3 (de) * 2005-04-25 2006-08-31 Siemens Audiologische Technik Gmbh Hörhilfevorrichtung mit Kompensation von akustischen und elektromagnetischen Rückkopplungssignalen
DE102005043348A1 (de) * 2005-09-12 2006-12-28 Siemens Audiologische Technik Gmbh Schaltungsvorrichtung zum Betrieb eines Hörgeräts mit zeitadaptivem Verhalten und entsprechendes Verfahren
WO2007057837A1 (fr) * 2005-11-18 2007-05-24 Koninklijke Philips Electronics N.V. Systeme de traitement des signaux, par exemple systeme de traitement des signaux sonores, ou dispositif d'aide auditive
DE102005061000A1 (de) * 2005-12-20 2007-06-21 Siemens Audiologische Technik Gmbh Signalverarbeitung für Hörgeräte mit mehreren Kompressionsalgorithmen
EP1858292A1 (fr) 2006-05-16 2007-11-21 Phonak AG Prothèse auditive et procédé d'utilisation d'une prothèse auditive
WO2007131815A1 (fr) * 2006-05-16 2007-11-22 Phonak Ag Dispositif auditif et procédé pour le faire fonctionner
EP1945000A1 (fr) 2007-01-11 2008-07-16 Siemens Audiologische Technik GmbH Procédé destiné à la réduction de puissances d'interférence et système acoustique correspondant
DE102007030067A1 (de) 2007-06-29 2009-01-08 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit passiver, eingangspegelabhängiger Geräuschreduktion
EP2109330A1 (fr) 2008-04-07 2009-10-14 Siemens Medical Instruments Pte. Ltd. Procédé de commutation d'une prothèse auditive entre deux états de fonctionnement et prothèse auditive
DE102009004185B3 (de) * 2009-01-09 2010-04-15 Siemens Medical Instruments Pte. Ltd. Verfahren zur Signalverarbeitung einer Hörvorrichtung und entsprechende Hörvorrichtung
US7957548B2 (en) 2006-05-16 2011-06-07 Phonak Ag Hearing device with transfer function adjusted according to predetermined acoustic environments
DE102010040689A1 (de) * 2010-09-14 2012-03-15 Bayerische Motoren Werke Aktiengesellschaft Audiosystem und Verfahren zum Durchführen eines Audioquellenwechsels
EP1801786B1 (fr) * 2005-12-20 2014-12-10 Oticon A/S Système audio avec délai temporel variable et procédé de traitement des signaux audio.

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DE10327890A1 (de) * 2003-06-20 2005-01-20 Siemens Audiologische Technik Gmbh Verfahren zum Betrieb eines Hörhilfegerätes sowie Hörhilfegerät mit einem Mikrofonsystem, bei dem unterschiedliche Richtcharakteristiken einstellbar sind
DE102004035256B3 (de) † 2004-07-21 2005-09-22 Siemens Audiologische Technik Gmbh Hörhilfegerätesystem sowie Verfahren zum Betrieb eines Hörhilfegerätesystems bei Audio-Empfang
EP1513371B1 (fr) * 2004-10-19 2012-08-15 Phonak Ag Procédé pour actionner une prothèse auditive et prothèse auditive
US7542580B2 (en) * 2005-02-25 2009-06-02 Starkey Laboratories, Inc. Microphone placement in hearing assistance devices to provide controlled directivity
EP1841286B1 (fr) * 2006-03-31 2014-06-25 Siemens Audiologische Technik GmbH Prothèse auditive dotée de valeurs de départ de paramètres adaptatives
DE102007013394A1 (de) * 2007-03-20 2008-10-02 Siemens Audiologische Technik Gmbh Verfahren zum Betreiben eines Hörgeräts
DE102007035173A1 (de) * 2007-07-27 2009-02-05 Siemens Medical Instruments Pte. Ltd. Verfahren zum Einstellen eines Hörsystems mit einem perzeptiven Modell für binaurales Hören und entsprechendes Hörsystem
DE102008004659A1 (de) * 2008-01-16 2009-07-30 Siemens Medical Instruments Pte. Ltd. Verfahren und Vorrichtung zur Konfiguration von Einstellmöglichkeiten an einem Hörgerät
WO2010010550A1 (fr) * 2008-07-23 2010-01-28 Yosef Shimoni Procédé et appareil permettant de soulager un patient souffrant d'acouphènes
EP2533550B2 (fr) * 2011-06-06 2021-06-23 Oticon A/s Diminution du niveau sonore de tintement par traitement d'instrument auditif
US9398379B2 (en) * 2012-04-25 2016-07-19 Sivantos Pte. Ltd. Method of controlling a directional characteristic, and hearing system
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DE102004010867B3 (de) * 2004-03-05 2005-08-18 Siemens Audiologische Technik Gmbh Verfahren und Vorrichtung zum Anpassen der Phasen von Mikrofonen eines Hörgeräterichtmikrofons
DE102005019149B3 (de) * 2005-04-25 2006-08-31 Siemens Audiologische Technik Gmbh Hörhilfevorrichtung mit Kompensation von akustischen und elektromagnetischen Rückkopplungssignalen
EP1718113A2 (fr) 2005-04-25 2006-11-02 Siemens Audiologische Technik GmbH Dispositif de prothèse auditive avec compensation du signal de rétroaction acoustique et électromagnetique
US7844063B2 (en) 2005-04-25 2010-11-30 Siemens Audiologische Technik Gmbh Hearing and apparatus with compensation of acoustic and electromagnetic feedback signals
DE102005043348A1 (de) * 2005-09-12 2006-12-28 Siemens Audiologische Technik Gmbh Schaltungsvorrichtung zum Betrieb eines Hörgeräts mit zeitadaptivem Verhalten und entsprechendes Verfahren
WO2007057837A1 (fr) * 2005-11-18 2007-05-24 Koninklijke Philips Electronics N.V. Systeme de traitement des signaux, par exemple systeme de traitement des signaux sonores, ou dispositif d'aide auditive
EP1801786B1 (fr) * 2005-12-20 2014-12-10 Oticon A/S Système audio avec délai temporel variable et procédé de traitement des signaux audio.
DE102005061000A1 (de) * 2005-12-20 2007-06-21 Siemens Audiologische Technik Gmbh Signalverarbeitung für Hörgeräte mit mehreren Kompressionsalgorithmen
DE102005061000B4 (de) * 2005-12-20 2009-09-03 Siemens Audiologische Technik Gmbh Signalverarbeitung für Hörgeräte mit mehreren Kompressionsalgorithmen
EP1858292A1 (fr) 2006-05-16 2007-11-21 Phonak AG Prothèse auditive et procédé d'utilisation d'une prothèse auditive
WO2007131815A1 (fr) * 2006-05-16 2007-11-22 Phonak Ag Dispositif auditif et procédé pour le faire fonctionner
US7957548B2 (en) 2006-05-16 2011-06-07 Phonak Ag Hearing device with transfer function adjusted according to predetermined acoustic environments
DE102007001642A1 (de) * 2007-01-11 2008-07-24 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Störleistungen und entsprechendes Akustiksystem
EP1945000A1 (fr) 2007-01-11 2008-07-16 Siemens Audiologische Technik GmbH Procédé destiné à la réduction de puissances d'interférence et système acoustique correspondant
US8090128B2 (en) 2007-01-11 2012-01-03 Siemens Audiologische Technik Gmbh Method for reducing interference powers and corresponding acoustic system
DE102007030067B4 (de) * 2007-06-29 2011-08-25 Siemens Medical Instruments Pte. Ltd. Hörgerät mit passiver, eingangspegelabhängiger Geräuschreduktion und Verfahren
DE102007030067A1 (de) 2007-06-29 2009-01-08 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit passiver, eingangspegelabhängiger Geräuschreduktion
DE102008017552B3 (de) * 2008-04-07 2009-10-15 Siemens Medical Instruments Pte. Ltd. Verfahren zum Umschalten eines Hörgeräts zwischen zwei Betriebszuständen und Hörgerät
EP2109330A1 (fr) 2008-04-07 2009-10-14 Siemens Medical Instruments Pte. Ltd. Procédé de commutation d'une prothèse auditive entre deux états de fonctionnement et prothèse auditive
US8682011B2 (en) 2008-04-07 2014-03-25 Siemens Medical Instruments Pte. Ltd. Method for switching a hearing device between two operating states and hearing device
EP2222096A2 (fr) 2009-01-09 2010-08-25 Siemens Medical Instruments Pte. Ltd. Procédé destiné au traitement du signal d'un dispositif auditif et dispositif auditif correspondant
DE102009004185B3 (de) * 2009-01-09 2010-04-15 Siemens Medical Instruments Pte. Ltd. Verfahren zur Signalverarbeitung einer Hörvorrichtung und entsprechende Hörvorrichtung
US8280084B2 (en) 2009-01-09 2012-10-02 Siemens Medical Instruments Pte. Ltd. Method for signal processing for a hearing aid and corresponding hearing aid
DE102010040689A1 (de) * 2010-09-14 2012-03-15 Bayerische Motoren Werke Aktiengesellschaft Audiosystem und Verfahren zum Durchführen eines Audioquellenwechsels

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US7181033B2 (en) 2007-02-20
DK1307072T3 (da) 2008-04-14
EP1307072A3 (fr) 2005-10-05
EP1307072B1 (fr) 2007-12-12
US20030072465A1 (en) 2003-04-17
DE50211346D1 (de) 2008-01-24
ATE381237T1 (de) 2007-12-15
ES2296861T3 (es) 2008-05-01

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