EP1489885B1 - Method for operating a hearing aid system as well as a hearing aid system with a microphone system in which different directional characteristics are selectable - Google Patents

Method for operating a hearing aid system as well as a hearing aid system with a microphone system in which different directional characteristics are selectable Download PDF

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Publication number
EP1489885B1
EP1489885B1 EP04013290A EP04013290A EP1489885B1 EP 1489885 B1 EP1489885 B1 EP 1489885B1 EP 04013290 A EP04013290 A EP 04013290A EP 04013290 A EP04013290 A EP 04013290A EP 1489885 B1 EP1489885 B1 EP 1489885B1
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EP
European Patent Office
Prior art keywords
microphone
hearing aid
hearing
signal
frequency
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EP04013290A
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German (de)
French (fr)
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EP1489885A2 (en
EP1489885A3 (en
Inventor
Eghart Fischer
Volkmar Hamacher
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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Publication of EP1489885A3 publication Critical patent/EP1489885A3/en
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest

Definitions

  • the invention relates to a method for setting a hearing aid and a hearing aid with a microphone system with variable directional characteristic for receiving an acoustic input signal and output of at least one microphone signal, a signal processing unit and an output transducer. Furthermore, the invention relates to a programming device for a hearing aid.
  • the transmission parameters of the hearing aid are automatically varied.
  • the classification can have an influence on the mode of operation of noise suppression algorithms as well as on the microphone system.
  • an omnidirectional directional characteristic directional characteristic of zero order
  • a clear directivity of the microphone system directivity of the first or higher order.
  • To generate the directional characteristic gradient microphones are used or interconnected several omnidirectional microphones with each other. Such microphone systems show a frequency-dependent transmission behavior, in which a significant drop to low frequencies is recorded.
  • the noise behavior of the microphones is frequency independent.
  • the high-pass frequency response of the microphone system must be balanced by amplifying the low frequencies.
  • the noise in the low frequency range is also amplified and, under certain circumstances, clearly and disturbingly audible, while quiet noise is obscured by the noise.
  • microphone noise is increased over a single omnidirectional microphone, with microphone noise increasing with the number of omnidirectional microphones used.
  • a hearing aid is known with a signal processing unit and at least two microphones, which are interconnected to form directional microphone systems of different order, the directional microphone systems in turn are interconnected in dependent on the frequency of the votes of the microphones microphone signals weighting.
  • the cut-off frequency between adjacent frequency bands, in which a different weighting of the microphone signals is provided can be set.
  • From the EP 0 942 627 A2 is a hearing aid with directional microphone system with a signal processing device, a handset and a plurality of microphones known whose output signals for generating an individual directional microphone characteristic via delay means and the signal processing means in different weighting are interconnected.
  • the preferred direction of reception (main direction) can be set individually in adaptation to a present hearing situation.
  • a hearing aid with an omnidirectional microphone and a directional microphone first or higher order known is a hearing aid with an omnidirectional microphone and a directional microphone first or higher order known.
  • the microphone signal of the directional microphone is amplified in the region of low signal frequencies in amplitude and matched to the microphone signal of the omnidirectional microphone.
  • Both the microphone signal of the omnidirectional microphone and the microphone signal of the directional microphone are supplied to a switching unit. In a first switching position of the switching unit is omnidirectional microphone and connected in a second switching position of the switching unit, the directional microphone with a hearing aid amplifier.
  • the switching unit can automatically switch depending on the signal level of a microphone signal.
  • a disadvantage of the known hearing aid devices with a directional microphone system is that in certain listening situations either the directivity of the microphone system is not optimally used or that a high degree of directivity leads to a clearly audible deterioration of the sound quality.
  • Object of the present invention is to improve the sound quality of a hearing aid with directional microphone system.
  • This object is achieved by a method for adjusting a hearing aid according to claims 1 and 5. Furthermore, the object is achieved by hearing aid devices according to claims 9 to 12 and by a programming device according to claims 13 and 14.
  • the hearing aid according to the invention comprises a microphone system with at least two microphones in order to realize directional characteristics zeroth and first order. Preferably, more than two microphones are available, so that directional characteristics of second and higher order are possible.
  • the hearing aid device comprises a signal processing unit for processing and frequency-dependent amplification of the microphone signal generated by the microphone system.
  • the signal output is usually carried out by an acoustic output signal by means of a handset. But there are also other, eg vibration generating output transducer known.
  • an omnidirectional directivity is to be understood, for example, by a single, not with others Microphones interconnected omnidirectional microphone emerges.
  • a microphone unit with a directional pattern of first order can be realized for example by a single gradient microphone or the electrical interconnection of two omnidirectional microphones.
  • DI directivity index
  • the KEMAR a standard research dummy
  • DI values of 4-4.5 dB with optimum positioning of the microphones and best matching of the signals generated by the microphones.
  • Directional microphones of the second and higher order have DI values of 10 dB and more, which are advantageous for better speech intelligibility, for example. If a hearing aid device contains a microphone system with, for example, three omnidirectional microphones, microphone units with directional characteristics of zeroth to second order can be realized on this basis at the same time by suitable interconnection of the microphones.
  • a single omnidirectional microphone represents a zeroth-order microphone unit. If two microphone omnidirectional microphones, the microphone signal of a microphone delayed, inverted and added to the microphone signal of the other microphone, creating a first-order microphone unit. If, in turn, the microphone signal of a microphone unit is delayed, inverted and added to the microphone signal of the second microphone unit of the first order in the case of two microphone units of the first order, the result is a microphone unit with a directional characteristic of second order. In this way - depending on the number of omnidirectional microphones - microphone units of any order can be realized.
  • a microphone system comprises microphone units of different order
  • it is possible to switch between different directional characteristics for example by switching on or off one or more microphones.
  • Any mixed forms between the directional characteristics of different order can be generated.
  • the microphone signals of the microphone units are weighted differently and added before they are further processed and amplified in the signal processing unit of the hearing aid.
  • a continuous, smooth transition between different directional characteristics can be realized, which can avoid disturbing artifacts when switching.
  • a high degree of directivity in a hearing aid is desirable.
  • the words of a conversation partner can be better understood during a conversation or in a listening situation with side noise this is largely suppressed.
  • a higher degree of directivity also increases the microphone noise caused by the microphone system. It is therefore always necessary to find a compromise between the strength of the directivity and the maximum microphone noise accepted.
  • the admitted microphone noise is adapted to the individual hearing loss of the hearing aid wearer by allowing a change in the directional characteristic only to the extent microphone noise, in which this is not perceived by the hearing aid wearer as disturbing.
  • the microphone noise is perceived as disturbing, in particular in the case of quiet output signals of the hearing aid device, since it is not covered (masked) by these signals due to the useful signal.
  • the microphone noise is obscured and thus inaudible at a loud output of the hearing aid. Therefore, in situations with a relatively high signal level of the microphone signal generated by the microphone system, the directivity due to the psychoacoustic masking of the microphone noise by the loud input signal need not be restricted.
  • the invention provides for the individual hearing threshold of the hearing aid wearer to be taken into account when setting the directivity.
  • the rest hearing threshold of the hearing aid wearer is first determined as a function of the frequency of a test signal supplied to the hearing aid wearer's ear. Based on current hearing aid settings, which relate in particular to the signal transmission behavior of the hearing aid and the microphone system, the microphone noise emanating from the microphone system and supplied to the hearing aid wearer's hearing can be calculated fairly accurately over the frequency. As an alternative to the calculation, it is also possible to measure the microphone noise under the given settings of the hearing aid as a function of the frequency. A comparison with the previously measured individual rest hearing threshold of the hearing aid wearer now shows whether the microphone noise is at least in certain frequency ranges above the rest hearing threshold and thus perceived by the hearing aid wearer. According to the invention, the highest possible level of directivity is then set for the frequencies that can be transmitted with the hearing aid device, without the microphone noise caused by the microphone system exceeding the threshold hearing threshold.
  • the directional characteristic of the microphone system is set so that the microphone noise caused by the microphone system and supplied to the hearing aid wearer microphone noise is at least in a certain frequency range above the rest hearing threshold, but one of the hearing aid wearer individually considered tolerable measure does not exceed.
  • the microphone noise can be adjusted so that it is at least approximately over the entire, transferable by the hearing aid Frequency range coincides with the quiet auditory threshold or deemed tolerable level of noise.
  • An embodiment of the invention provides that the setting of the directional microphone system during operation of the hearing aid is adapted to the current environment situation.
  • a higher degree of directivity is permitted than would be the case if only the quiescent hearing threshold were taken into account.
  • An optimization of the directivity is achieved in particular when the individual masking threshold of the hearing aid wearer is determined with respect to the microphone noise. This indicates at which signal level of a component of the microphone system resulting from an acoustic input signal, the proportion of the microphone noise in this output signal is masked, ie hidden, and thus no longer perceptible by the hearing aid wearer.
  • the masking threshold is dependent on the frequency and signal level of the microphone noise and indicates which microphone signals are suitable for masking the microphone noise.
  • the degree of directivity of the microphone system is then varied so that the highest possible directivity is achieved as a function of the frequency of an acoustic input signal, without causing the microphone noise exceeds the Mask michsschelle.
  • a measure of microphone noise that is individually tolerated by the hearing aid wearer can also be permitted here, which means that the directivity is set such that the microphone noise can exceed the masking threshold by a certain amount, at least in a certain frequency range.
  • any function can be specified which indicates by what value the microphone noise should exceed or also fall below the threshold hearing threshold as a function of the frequency. In practice it will However, at least for a certain frequency range (eg from 2 kHz to 4 kHz) a constant value (eg 5 dB above the rest hearing threshold measured in this frequency range) for the permissible microphone noise is set.
  • the adjustment of the directivity of the hearing aid according to the invention as a function of the rest hearing threshold or the masking threshold can be done for example during the adaptation of the hearing aid to the individual hearing loss of a hearing aid wearer by the acoustician.
  • this adaptation is advantageously carried out automatically by the programming device, controlled by a corresponding programming software.
  • Serving as input variables in the calculation are audiometric data of the hearing aid wearer, in particular the rest hearing threshold or the masking threshold, characteristic values of the hearing aid and the hearing aid settings to compensate for the individual hearing loss of the hearing aid wearer.
  • the programmer uses these data to calculate values of the setting parameters which relate to the setting of the directivity as a function of the frequency.
  • the adjustment of the directivity additionally takes place as a function of the signal level of the output signal which is fed to the hearing aid wearer's ear. Also in this regard, setting parameters are calculated by the programmer and transmitted to the hearing aid, which regulate the directivity of the microphone system as a function of this signal level during operation of the hearing aid.
  • the invention can be applied to all known hearing aid types with an adjustable directional microphone, for example, in behind the ear portable hearing aids, in the ear portable hearing aids, implantable hearing aids or Taschen speak Walkerellan.
  • the hearing aid device according to the invention may also be part of a plurality of devices for supplying a hearing aid device system comprising a hearing-impaired person be part of a hearing aid system with two worn on the head hearing aids for binaural care or part of a hearing aid system consisting of a portable on the head device and a wearable processor unit.
  • FIG. 1 shows a schematic diagram of a hearing aid with a directional microphone system according to the invention.
  • the microphone system comprises three omnidirectional microphones 1, 2 and 3.
  • the microphone signal emanating from the microphone 2 is delayed in a delay unit 4A, inverted by an inverter 5A and summed in a summer 6A to the microphone signal R0 emanating from the microphone 1.
  • the two omnidirectional microphones 1 and 2 thereby form a directional microphone 1, 2 with directivity of the first order, from which the microphone signal R1 starts.
  • the microphone signal emanating from the microphone 3 is delayed in a delay unit 4B, inverted by an inverter 5B and in one Totalizer 6B added to the output from the microphone 2 microphone signal.
  • the microphones 2 and 3 thereby form a directional microphone system 2, 3 with directivity of the first order, the microphone signal is applied to the output of the summer 6B. If, in turn, the microphone signal emitted by the directional microphone system 2, 3 is delayed in a delay unit 7 and inverted in an inverter 8 and added in a summer 9 to the microphone signal R1 emanating from the directional microphone system 1, 2, the result is the microphones 1, 2 and 3 a directional microphone system 1, 2, 3 with directivity second order, the microphone signal R2 is applied to the output of the summer 9.
  • the three microphone signals R0, R1 and R2 are finally fed to a circuit unit 10 in which it is possible to switch between the different microphone signals or in which the different microphone signals R0, R1 and R2 are weighted and added differently.
  • the resulting and output at the output of the circuit unit 10 microphone output signal RA is finally fed to a signal processing unit 11, in which the further processing and frequency-dependent amplification of the microphone output signal RA takes place to compensate for the individual hearing loss of a hearing aid wearer.
  • the processed microphone signal is converted by an earphone 12 into an acoustic signal for delivery into an auditory canal of the hearing aid wearer.
  • the hearing aid has a control unit 13 in which different parameter sets, so-called hearing programs, can be stored and retrieved in the hearing aid to control the signal processing. Between the different hearing programs can be switched by means of a program selection button 14. Furthermore, the hearing aid has an automatic situation detection, by means of which the signal processing related parameters of the hearing aid adjusted during operation of the hearing aid can be.
  • the control unit 13 is supplied with the microphone signal emitted by the omnidirectional microphone 1.
  • the directional characteristic of the microphone system is adapted to the detected environmental situation or to the set hearing program, wherein in the embodiment, a microphone control unit 15 is provided, which is also controlled by the control unit 13.
  • the microphone control unit 15 can thus be switched over the microphone control unit 15 between directional microphone systems with directional characteristics zeroth, first or second order or it can be outgoing from the directional microphones of different order microphone signals, controlled by the microphone control unit 15, weighted differently and added become.
  • the adjustment of the directional characteristic takes place taking into account the individual rest hearing threshold of a hearing aid wearer. This is determined by an auditory test, which is usually performed by a hearing care professional. Further, in the hearing aid according to the embodiment, the microphone noise for different directional characteristics is determined, for example, measured or calculated taking into account the microphone characteristics, the different interconnections of the microphones and the signal processing in the hearing aid at the respective hearing aid settings. Subsequently, in the hearing aid, the directivity is set as a function of the frequency, the rest hearing threshold and the microphone noise at the respective frequency.
  • the directional characteristic is set such that the microphone noise generated by the microphone system and supplied to the hearing aid wearer's hearing is of the order of magnitude of this rest hearing threshold, so that the highest possible directivity is achieved without the microphone noise generated by the microphone system is perceived by the hearing aid wearer as disturbing. If the rest hearing threshold of the hearing aid wearer lies in another frequency range, for example at 50 dB SPL, a higher degree of directivity can be allowed in this frequency range, for example a second order directivity, without the microphone noise being perceived by the hearing aid wearer.
  • the goal is thus pursued to allow the highest possible level of directivity without causing the microphone noise generated by the microphone system, taking into account the current hearing aid settings above the individual rest hearing threshold of the hearing aid wearer.
  • Another strategy of hearing aid setting may be that a microphone noise perceivable by the hearing aid wearer does not exceed a certain level.
  • the microphone system is then adjusted so that in the output signal of the hearing aid device, the microphone noise caused by the microphone system exceeds the rest hearing threshold of the hearing aid wearer by a maximum of just this degree.
  • this amount of microphone noise which is considered tolerable by the hearing aid wearer, can relate to the entire frequency range which can be transmitted by the hearing aid device or can only be limited to a specific frequency range.
  • a further development of the invention provides that the microphone control unit 15 is also supplied with the output signal of the control unit 10 and thus with the microphone output signal RA intended for further processing.
  • This has the advantage that, in addition to the individual rest threshold, the signal level of this microphone signal can also be taken into account when setting the directional characteristic.
  • the microphone noise is perceived as disturbing only at relatively low signal levels of this microphone output signal RA.
  • the microphone noise takes up only a small portion of this signal and the majority of the microphone output signal RA is determined by the acoustic input signal.
  • the directional microphone system is achieved by determining the individual masking threshold for the microphone noise in the hearing aid wearer. Then, the directivity depending on the frequency of outgoing from the microphones 1-3 microphone signals R0, R1 and R2 can be set so that always the maximum directivity is set, in which the microphone noise is barely concealed. In the case of a very quiet acoustic input signal or without acoustic input signal, at least substantially only the microphone signal R0 emanating from the omnidirectional microphone 1 is then automatically forwarded to the signal processing unit 11. As the signal level in the microphone signal increases, the directional characteristics of higher order are gradually switched or the weight of the microphone signal R1 or R2 is increased continuously relative to R0.
  • a certain level of microphone noise from the individual hearing aid wearer can also be considered tolerable when the masking threshold is taken into account. Then, the directional characteristic of the microphone system is adjusted so that this level of microphone noise remains perceptible either over the entire transmittable frequency range or only in at least one frequency band of the hearing aid wearer.
  • the microphone control unit 15 is supplied with the microphone output signal RA in order to set the directivity of the microphone system such that the microphone noise supplied to the hearing aid wearer's hearing lies below the rest hearing threshold or is concealed by a useful signal. Since the feedback thus takes place before the actual signal processing in the hearing aid by means of the signal processing unit 11, the microphone control unit 15 is additionally supplied with the current control parameters of the control unit 13, so that the further processing of the microphone output signal RA by the signal processing unit 11 can be taken into account. Alternatively, the microphone control unit 15 could also be supplied with the output signal of the signal processing unit 11.
  • the signal processing in the hearing aid device can take place in analog, digital or in combined circuit technology. Furthermore, the signal processing can also take place in parallel in adjoining frequency bands (channels). Preferably, the adjustment of the directional characteristic of the microphone system in frequency bands.
  • FIG. 2 a block diagram for setting a directional microphone system taking into account an individual rest threshold.
  • the microphone system of the hearing aid comprises a microphone array 20 with a plurality of microphones, from each of which a microphone signal is emitted.
  • the microphone signals are fed to a circuit unit 21. This provides at its signal output a microphone signal, which is provided for further processing in the hearing aid.
  • the aim of the hearing aid setting is to achieve the highest possible level of directivity, without causing the microphone noise to rise so that this is perceived by a hearing aid wearer as disturbing.
  • the individual resting hearing threshold of the hearing aid wearer is first determined with a test device as a function of the frequency of a test signal supplied to the hearing aid wearer's hearing device and stored in a memory device 22.
  • the measurement of the rest hearing threshold can be carried out by a hearing aid acoustician, but it can also be carried out by the hearing aid wearer himself with a suitable measuring device (PC with corresponding software) or a hearing aid device with integrated tone generator. If the individual rest hearing threshold of a hearing aid wearer is known as a function of the frequency, the required amplification of quiet input signals as a function of the frequency by the hearing aid can also be determined therefrom in order to compensate for the hearing loss.
  • the hearing loss is not completely compensated by the hearing aid, but based on the resting hearing threshold of a normal hearing only by 50%, for example.
  • the microphone noise supplied to the hearing aid wearer's hearing aid can be determined with quiet input signals or in the absence of an acoustic input signal.
  • the microphone noise is calculated based on Hearing aid and microphone characteristics.
  • an optimized directional characteristic of the microphone array is now determined as a function of the frequency of an acoustic input signal and the individual rest hearing threshold of the hearing aid wearer at the respective frequency, for which purpose the values of adjustment parameters of the hearing aid and in particular of the circuit unit 21 for adjustment this directional characteristic calculated and adjusted in the hearing aid.
  • the calculation takes place in a computing device 23, which is preferably designed as a programming device or PC with a corresponding software and includes the memory device 22.
  • the calculated parameters are then transferred to the hearing aid.
  • the computing device 23 can also be arranged within the hearing aid.
  • the adjustment of the hearing aid and in particular of the circuit unit 21 is such that the hearing aid supplied to the hearing aid carrier microphone noise at least approximately coincides with the rest hearing threshold or at least does not exceed.
  • the directivity of the microphone array can also be adjusted so that the resulting microphone noise exceeds the rest hearing threshold of the hearing aid wearer by a tolerable measure of this at least in a certain frequency range. Preferably, this measure is freely selectable depending on the frequency.
  • the microphone signals of a number of microphones 30 for adjusting the directional characteristic are first supplied to a circuit unit 31.
  • the setting is not static, for example, once during the adaptation of the hearing aid by the acoustician, but adaptive during operation of the hearing aid.
  • To adjust the directivity of the microphone signal generated by the microphone system or a signal resulting from it is also taken into account. If the microphone signal has a high signal level at least in a certain frequency range, then a higher microphone noise and thus a higher degree of directivity can be tolerated at least in this frequency range.
  • the directivity is then increased at least in this frequency range until the proportion of the microphone noise in the output signal is just concealed by the portion of the output signal resulting from the acoustic input signal, or the maximum directivity is achieved. This ensures that the maximum directivity is always set at which the microphone noise is not perceived as disturbing.
  • the masking threshold for the microphone noise is also determined on the basis of test signals which are supplied to the hearing aid wearer's hearing, for example during the adaptation of the hearing aid. As test signals, sinusoidal signals, white noise, or noise similar to microphone noise are preferably used. Data relating to the measured, individual masking threshold as a function of the frequency are then stored in a memory device 32 in the hearing aid.
  • a computing device 33 calculates adaptively an optimized setting of the circuit unit 31 from these data and the output signal of the circuit unit 31, so that as much directivity as possible is set and nevertheless no microphone noise is perceived by the hearing aid device carrier.
  • the directivity of the microphone array is adjusted so that the resulting microphone noise exceeds the rest hearing threshold of the hearing aid wearer by a tolerable amount, at least in a certain frequency range.
  • this measure is freely selectable depending on the frequency.
  • FIG. 4 Another embodiment for adjusting the directivity of a microphone system with multiple microphones 40 shows FIG. 4 , Again, as in the previous embodiment, the adjustment is adaptive taking into account the individual masking threshold.
  • the output signal of a circuit unit 41 provided for further processing in a signal processing unit of the hearing aid device is not considered.
  • the microphone system comprises a second circuit unit 42, into which the microphone signals generated by the omnidirectional microphones 40 also enter and from which the output signal of the microphone system provided for further processing emerges.
  • the settings of the first circuit unit 41 are static, ie, they are adjusted at best during the adaptation of the hearing aid, but not during normal operation.
  • the output signal of this first circuit unit 41 is then used together with the data relating to the individual masking threshold of the hearing aid wearer, which are stored in a memory device 43 in the hearing aid, to control the second circuit unit 42. If, for example, it results that in the current listening situation in the static settings of the first circuit unit 41 the microphone noise would be obscured by the acoustic input signal, a higher degree of directivity can be set in the adaptive circuit unit 42.
  • the setting parameters of the circuit unit 42 are thereby determined during operation of the hearing aid from the stored in the memory device 43 course of the masking threshold depending on the frequency and the signal level of the microphone noise and the desired signal and the output signal of the circuit unit 41 by means of the computing device 44.
  • the degree of occlusion ie the difference of the signal level of the microphone noise in comparison to the signal level of the signal originating from the acoustic input signal in the output signal of the circuit unit 41, with considered.
  • the computing device 44 in the circuit unit 42 With a large difference of these two signal levels can be set by the computing device 44 in the circuit unit 42, a relatively large increase in the directivity against the directivity generated by the circuit unit 41.
  • the advantage of this embodiment is that a feedback loop as in the previous embodiment is avoided.
  • the adaptive setting of a directional microphone system according to the invention can also be based on a masking model based on measurements on a large number of test persons.
  • the memory devices 32 and 43 of the embodiments according to the Figures 3 and 4 are then stored data relating to this general masking model, which usually also provides good results in the calculation of setting parameters of the directional microphone system.
  • the complex measurement of the individual masking threshold can thereby be omitted.
  • the directivity is to be improved by the invention in a hearing aid with a microphone system comprising several microphones, without this one of a hearing aid wearer perceived as disturbing increase in microphone noise.
  • the invention proposes that the adjustment of the microphone system takes place statically or adaptively taking into account the individual rest hearing threshold or taking into account the individual masking threshold for the microphone noise generated by the microphone system.
  • the greatest possible degree of directivity can always be allowed without the hearing aid wearer perceiving the microphone noise generated by the microphone system as disturbing.

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  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
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Description

Die Erfindung betrifft Verfahren zum Einstellen eines Hörhilfegerätes sowie ein Hörhilfegerät mit einem Mikrofonsystem mit veränderbarer Richtcharakteristik zur Aufnahme eines akustischen Eingangssignals und Abgabe wenigstens eines Mikrofonsignals, einer Signalverarbeitungseinheit und einem Ausgangswandler. Ferner betrifft die Erfindung ein Programmiergerät für ein Hörhilfegerät.The invention relates to a method for setting a hearing aid and a hearing aid with a microphone system with variable directional characteristic for receiving an acoustic input signal and output of at least one microphone signal, a signal processing unit and an output transducer. Furthermore, the invention relates to a programming device for a hearing aid.

In modernen Hörhilfegeräten finden Einrichtungen zur Klassifikation von Hörsituationen Verwendung. Je nach Hörsituation werden die Übertragungsparameter des Hörhilfegerätes automatisch variiert. Dabei kann die Klassifikation u.a. Einfluss haben auf die Wirkungsweise von Störgeräuschunterdrückungsalgorithmen als auch auf das Mikrofonsystem. So wird beispielsweise je nach erkannter Hörsituation gewählt (diskret umgeschaltet bzw. kontinuierlich übergeblendet) zwischen einer omnidirektionalen Richtcharakteristik (Richtcharakteristik nullter Ordnung) und einer deutlichen Richtwirkung des Mikrofonsystems (Richtcharakteristik erster oder höherer Ordnung). Zur Erzeugung der Richtcharakteristik werden Gradientenmikrofone verwendet oder mehrere omnidirektionale Mikrofone elektrisch miteinander verschaltet. Derartige Mikrofonsysteme zeigen ein frequenzabhängiges Übertragungsverhalten, bei dem ein deutlicher Abfall zu tiefen Frequenzen zu verzeichnen ist. Das Rauschverhalten der Mikrofone ist dagegen frequenzunabhängig. Zum Erreichen eines natürlichen Klangeindrucks muss der Hochpassfrequenzgang des Mikrofonsystems durch Verstärkung der tiefen Frequenzen ausgeglichen werden. Dabei wird das im tiefen Frequenzbereich vorhandene Rauschen ebenfalls mitverstärkt und unter Umständen deutlich und störend hörbar, während leise Geräusche vom Rauschen verdeckt werden. Weiterhin ist bei einem aus mehreren omnidirektionalen Mikrofonen aufgebauten Mikrofonsystem das Mikrofonrauschen gegenüber einem einzelnen omnidirektionalen Mikrofon erhöht, wobei das Mikrofonrauschen mit der Anzahl der verwendeten omnidirektionalen Mikrofone zunimmt.In modern hearing aids devices for the classification of hearing situations are used. Depending on the hearing situation, the transmission parameters of the hearing aid are automatically varied. The classification can have an influence on the mode of operation of noise suppression algorithms as well as on the microphone system. Thus, for example, depending on the detected hearing situation selected (discretely switched or continuously faded) between an omnidirectional directional characteristic (directional characteristic of zero order) and a clear directivity of the microphone system (directivity of the first or higher order). To generate the directional characteristic gradient microphones are used or interconnected several omnidirectional microphones with each other. Such microphone systems show a frequency-dependent transmission behavior, in which a significant drop to low frequencies is recorded. The noise behavior of the microphones is frequency independent. To achieve a natural sound impression, the high-pass frequency response of the microphone system must be balanced by amplifying the low frequencies. The noise in the low frequency range is also amplified and, under certain circumstances, clearly and disturbingly audible, while quiet noise is obscured by the noise. Farther For example, with a microphone system made up of multiple omnidirectional microphones, microphone noise is increased over a single omnidirectional microphone, with microphone noise increasing with the number of omnidirectional microphones used.

Aus der WO 00/76268 A2 ist ein Hörhilfegerät bekannt mit einer Signalverarbeitungseinheit und mindestens zwei Mikrofonen, die zur Bildung von Richtmikrofonsystemen unterschiedlicher Ordnung miteinander verschaltbar sind, wobei die Richtmikrofonsysteme ihrerseits in von der Frequenz der von den Mikrofonen abgegebenen Mikrofonsignale abhängiger Gewichtung miteinander verschaltbar sind. In Abhängigkeit des Ergebnisses einer Signalanalyse kann die Grenzfrequenz zwischen benachbarten Frequenzbändern, bei denen eine unterschiedliche Gewichtung der Mikrofonsignale vorgesehen ist, eingestellt werden.From the WO 00/76268 A2 a hearing aid is known with a signal processing unit and at least two microphones, which are interconnected to form directional microphone systems of different order, the directional microphone systems in turn are interconnected in dependent on the frequency of the votes of the microphones microphone signals weighting. Depending on the result of a signal analysis, the cut-off frequency between adjacent frequency bands, in which a different weighting of the microphone signals is provided, can be set.

Aus der EP 0 942 627 A2 ist ein Hörgerät mit Richtmikrofon-System mit einer Signalverarbeitungseinrichtung, einem Hörer und mehreren Mikrofonen bekannt, deren Ausgangssignale zur Erzeugung einer individuellen Richtmikrofoncharakteristik über Verzögerungseinrichtungen und die Signalverarbeitungseinrichtung in unterschiedlicher Gewichtung miteinander verschaltbar sind. Bei dem Richtmikrofon-System kann die bevorzugte Empfangsrichtung (Hauptrichtung) in Anpassung an eine vorliegende Hörsituation individuell eingestellt werden.From the EP 0 942 627 A2 is a hearing aid with directional microphone system with a signal processing device, a handset and a plurality of microphones known whose output signals for generating an individual directional microphone characteristic via delay means and the signal processing means in different weighting are interconnected. In the directional microphone system, the preferred direction of reception (main direction) can be set individually in adaptation to a present hearing situation.

Aus der US 5,524,056 ist ein Hörgerät mit einem omnidirektionalen Mikrofon und einem direktionalen Mikrofon erster oder höherer Ordnung bekannt. Das Mikrofonsignal des direktionalen Mikrofons wird im Bereich niedriger Signalfrequenzen in seiner Amplitude verstärkt und dem Mikrofonsignal des omnidirektionalen Mikrofons angeglichen. Sowohl das Mikrofonsignal des omnidirektionalen Mikrofons als auch das Mikrofonsignal des direktionalen Mikrofons sind einer Umschalteinheit zugeführt. In einer ersten Schaltstellung der Umschalteinheit ist das omnidirektionale Mikrofon und in einer zweiten Schaltstellung der Umschalteinheit das direktionale Mikrofon mit einem Hörgeräte-Verstärker verbunden. Die Umschalteinheit kann in Abhängigkeit des Signalpegels eines Mikrofonsignals automatisch umschalten.From the US 5,524,056 is a hearing aid with an omnidirectional microphone and a directional microphone first or higher order known. The microphone signal of the directional microphone is amplified in the region of low signal frequencies in amplitude and matched to the microphone signal of the omnidirectional microphone. Both the microphone signal of the omnidirectional microphone and the microphone signal of the directional microphone are supplied to a switching unit. In a first switching position of the switching unit is omnidirectional microphone and connected in a second switching position of the switching unit, the directional microphone with a hearing aid amplifier. The switching unit can automatically switch depending on the signal level of a microphone signal.

Aus der Druckschrift US 2002/0057815 A1 ist ein Hörgerät mit einem direktionalen Mikrofon mit Richtwirkung erster Ordnung und einem direktionalen Mikrofon mit Richtwirkung zweiter Ordnung bekannt. Mittels eines Schalters schaltet das Hörhilfegerät in Abhängigkeit vom Signalpegel eines Umgebungsgeräusches automatisch zwischen den unterschiedlichen Richtcharakteristiken um.From the publication US 2002/0057815 A1 is a hearing aid with a directional microphone first-order directivity and a directional microphone with directivity second order known. By means of a switch, the hearing aid automatically switches depending on the signal level of an ambient noise between the different directional characteristics.

Aus der Druckschrift US 2001/0038699 A1 ist ein Hörgerät mit einem omnidirektionalen Mikrofon und einem Richtmikrofon bekannt, wobei das Hörhilfegerät in Abhängigkeit des Signalpegels eines Eingangssignals eine Richtwirkung mehr oder weniger stark aktiviert.From the publication US 2001/0038699 A1 a hearing aid with an omnidirectional microphone and a directional microphone is known, wherein the hearing aid activates more or less strongly a directivity depending on the signal level of an input signal.

Nachteilig bei den bekannten Hörhilfegeräten mit einem RichtMikrofonsystem ist, dass in bestimmten Hörsituationen entweder die Richtwirkung des Mikrofonsystems nicht optimal verwendet wird oder dass ein hoher Grad an Richtwirkung zu einer deutlich hörbaren Verschlechterung der Klangqualität führt.A disadvantage of the known hearing aid devices with a directional microphone system is that in certain listening situations either the directivity of the microphone system is not optimally used or that a high degree of directivity leads to a clearly audible deterioration of the sound quality.

Aufgabe der vorliegenden Erfindung ist es, die Klangqualität eines Hörhilfegerätes mit Richtmikrofonsystem zu verbessern.Object of the present invention is to improve the sound quality of a hearing aid with directional microphone system.

Diese Aufgabe wird gelöst durch Verfahren zum Einstellen eines Hörhilfegerätes gemäß den Ansprüchen 1 und 5. Ferner wird die Aufgabe gelöst durch Hörhilfegeräte gemäß den Ansprüchen 9 bis 12 sowie durch ein Programmiergerät gemäß den Ansprüchen 13 und 14.This object is achieved by a method for adjusting a hearing aid according to claims 1 and 5. Furthermore, the object is achieved by hearing aid devices according to claims 9 to 12 and by a programming device according to claims 13 and 14.

Das erfindungsgemäße Hörhilfegerät umfasst ein Mikrofonsystem mit mindestens zwei Mikrofonen, um Richtcharakteristiken nullter und erster Ordnung realisieren zu können. Vorzugsweise sind jedoch mehr als zwei Mikrofone vorhanden, so dass auch Richtcharakteristiken zweiter und höherer Ordnung möglich sind. Weiterhin umfasst das Hörhilfegerät eine Signalverarbeitungseinheit zur Verarbeitung und frequenzabhängigen Verstärkung des von dem Mikrofonsystem erzeugten Mikrofonsignals. Die Signalausgabe erfolgt üblicherweise durch ein akustisches Ausgangssignal mittels eines Hörers. Es sind aber auch andere, z.B. Vibrationen erzeugende Ausgangswandler bekannt.The hearing aid according to the invention comprises a microphone system with at least two microphones in order to realize directional characteristics zeroth and first order. Preferably However, more than two microphones are available, so that directional characteristics of second and higher order are possible. Furthermore, the hearing aid device comprises a signal processing unit for processing and frequency-dependent amplification of the microphone signal generated by the microphone system. The signal output is usually carried out by an acoustic output signal by means of a handset. But there are also other, eg vibration generating output transducer known.

Als Richtcharakteristik nullter Ordnung im Sinne der Erfindung ist eine omnidirektionale Richtcharakteristik zu verstehen, die beispielsweise von einem einzelnen, nicht mit weiteren Mikrofonen verschalteten omnidirektionalen Mikrofon hervorgeht. Eine Mikrofoneinheit mit einer Richtcharakteristik erster Ordnung (Richtmikrofon erster Ordnung) kann beispielsweise durch ein einzelnes Gradientenmikrofon oder die elektrische Verschaltung zweier omnidirektionaler Mikrofone realisiert werden. Mit Richtmikrofonen erster Ordnung ist ein theoretisch erreichbarer Maximalwert des Direktiviti-Index (DI) von 6 dB (Hyperniere) zu erreichen. In der Praxis erhält man am KEMAR (einer Standardforschungspuppe) bei optimaler Lage der Mikrofone und bestem Abgleich der von den Mikrofonen erzeugten Signale DI-Werte von 4-4,5 dB. Richtmikrofone zweiter und höherer Ordnung weisen DI-Werte von 10 dB und mehr auf, die beispielsweise für eine bessere Sprachverständlichkeit vorteilhaft sind. Enthält ein Hörhilfegerät ein Mikrofonsystem mit beispielsweise drei omnidirektionalen Mikrofonen, so können auf dieser Basis durch geeignete Verschaltung der Mikrofone gleichzeitig Mikrofoneinheiten mit Richtcharakteristiken nullter bis zweiter Ordnung realisiert werden.As a directional characteristic of zero order in the context of the invention, an omnidirectional directivity is to be understood, for example, by a single, not with others Microphones interconnected omnidirectional microphone emerges. A microphone unit with a directional pattern of first order (directional microphone first order) can be realized for example by a single gradient microphone or the electrical interconnection of two omnidirectional microphones. With directional microphones of the first order a theoretically achievable maximum value of the directivity index (DI) of 6 dB (hypercardioid) can be achieved. In practice, the KEMAR (a standard research dummy) achieves DI values of 4-4.5 dB with optimum positioning of the microphones and best matching of the signals generated by the microphones. Directional microphones of the second and higher order have DI values of 10 dB and more, which are advantageous for better speech intelligibility, for example. If a hearing aid device contains a microphone system with, for example, three omnidirectional microphones, microphone units with directional characteristics of zeroth to second order can be realized on this basis at the same time by suitable interconnection of the microphones.

Ein einzelnes omnidirektionales Mikrofon stellt für sich eine Mikrofoneinheit nullter Ordnung dar. Wird bei zwei omnidirektionalen Mikrofonen das Mikrofonsignal eines Mikrofons verzögert, invertiert und zu dem Mikrofonsignal des anderen Mikrofons addiert, so entsteht eine Mikrofoneinheit erster Ordnung. Wird wiederum bei zwei Mikrofoneinheiten erster Ordnung das Mikrofonsignal einer Mikrofoneinheit verzögert, invertiert und zu dem Mikrofonsignal der zweiten Mikrofoneinheit erster Ordnung addiert, so ergibt sich eine Mikrofoneinheit mit Richtcharakteristik zweiter Ordnung. Auf diese Weise lassen sich - abhängig von der Anzahl omnidirektionaler Mikrofone - Mikrofoneinheiten beliebiger Ordnung realisieren.A single omnidirectional microphone represents a zeroth-order microphone unit. If two microphone omnidirectional microphones, the microphone signal of a microphone delayed, inverted and added to the microphone signal of the other microphone, creating a first-order microphone unit. If, in turn, the microphone signal of a microphone unit is delayed, inverted and added to the microphone signal of the second microphone unit of the first order in the case of two microphone units of the first order, the result is a microphone unit with a directional characteristic of second order. In this way - depending on the number of omnidirectional microphones - microphone units of any order can be realized.

Umfasst ein Mikrofonsystem Mikrofoneinheiten unterschiedlicher Ordnung, so kann zwischen unterschiedlichen Richtcharakteristiken umgeschaltet werden, z.B. durch An- oder Ausschalten eines oder mehrerer Mikrofone. Weiterhin können durch eine geeignete elektrische Verschaltung der Mikrofoneinheiten auch beliebige Mischformen zwischen den Richtcharakteristiken unterschiedlicher Ordnung erzeugt werden. Hierzu werden die Mikrofonsignale der Mikrofoneinheiten unterschiedlich gewichtet und addiert, bevor sie in der Signalverarbeitungseinheit des Hörhilfegerätes weiter verarbeitet und verstärkt werden. So kann ein kontinuierlicher, gleitender Übergang zwischen unterschiedlichen Richtcharakteristiken realisiert werden, wodurch sich störende Artefakte beim Umschalten vermeiden lassen.If a microphone system comprises microphone units of different order, it is possible to switch between different directional characteristics, for example by switching on or off one or more microphones. Furthermore, by a suitable electrical connection of the microphone units Any mixed forms between the directional characteristics of different order can be generated. For this purpose, the microphone signals of the microphone units are weighted differently and added before they are further processed and amplified in the signal processing unit of the hearing aid. Thus, a continuous, smooth transition between different directional characteristics can be realized, which can avoid disturbing artifacts when switching.

In vielen Alltagssituationen ist ein hohes Maß an Richtwirkung bei einem Hörhilfegerät wünschenswert. So können zum Beispiel die Worte eines Gesprächspartners bei einem Gespräch besser verstanden werden oder in einer Hörsituation mit seitlichem Störlärm wird dieser weitgehend unterdrückt. Allerdings vergrößert ein höheres Maß an Richtwirkung auch das durch das Mikrofonsystem verursachte Mikrofonrauschen. Es muss daher stets ein Kompromiss zwischen der Stärke der Richtwirkung und dem maximal in Kauf genommenen Mikrofonrauschen gefunden werden.In many everyday situations, a high degree of directivity in a hearing aid is desirable. Thus, for example, the words of a conversation partner can be better understood during a conversation or in a listening situation with side noise this is largely suppressed. However, a higher degree of directivity also increases the microphone noise caused by the microphone system. It is therefore always necessary to find a compromise between the strength of the directivity and the maximum microphone noise accepted.

Bei einem Hörhilfegerät gemäß der Erfindung wird das zugelassene Mikrofonrauschen an den individuellen Hörverlust des Hörhilfegeräteträgers angepasst, indem über eine Veränderung der Richtcharakteristik nur in dem Maß Mikrofonrauschen zugelassen wird, in dem dies von dem Hörhilfegeräteträger nicht als störend empfunden wird. Dabei wird das Mikrofonrauschen insbesondere bei leisen Ausgangssignalen des Hörhilfegerätes als störend empfunden, da es bei diesen nicht durch das Nutzsignal verdeckt (maskiert) wird. Hingegen wird bei einem lauten Ausgangssignal des Hörhilfegerätes das Mikrofonrauschen verdeckt und damit unhörbar. Daher muss in Situationen mit einem relativ hohen Signalpegel des von dem Mikrofonsystem erzeugten Mikrofonsignals die Richtwirkung wegen der psychoakustischen Verdeckung des Mikrofonrauschens durch das laute Eingangssignal nicht eingeschränkt werden.In a hearing aid according to the invention, the admitted microphone noise is adapted to the individual hearing loss of the hearing aid wearer by allowing a change in the directional characteristic only to the extent microphone noise, in which this is not perceived by the hearing aid wearer as disturbing. In this case, the microphone noise is perceived as disturbing, in particular in the case of quiet output signals of the hearing aid device, since it is not covered (masked) by these signals due to the useful signal. By contrast, the microphone noise is obscured and thus inaudible at a loud output of the hearing aid. Therefore, in situations with a relatively high signal level of the microphone signal generated by the microphone system, the directivity due to the psychoacoustic masking of the microphone noise by the loud input signal need not be restricted.

Um nicht unnötig Richtwirkung zu verschenken, sondern diese individuell optimal auszunutzen, sieht die Erfindung vor, die individuelle Ruhehörschwelle des Hörhilfegeräteträgers bei der Einstellung der Richtwirkung mit zu berücksichtigen.In order not to unnecessarily give away directivity, but to make optimal use of it individually, the invention provides for the individual hearing threshold of the hearing aid wearer to be taken into account when setting the directivity.

Hierzu wird zunächst die Ruhehörschwelle des Hörhilfegeräteträgers in Abhängigkeit von der Frequenz eines dem Gehör des Hörhilfegeräteträgers zugeführten Testsignals ermittelt. Anhand aktueller Hörhilfegeräteeinstellungen, die insbesondere das Signalübertragungsverhalten des Hörhilfegerätes und das Mikrofonsystem betreffen, kann das von dem Mikrofonsystem ausgehende und dem Gehör des Hörhilfegeräteträgers zugeführte Mikrofonrauschen über der Frequenz ziemlich genau berechnet werden. Als Alternative zu der Berechnung ist es ebenfalls möglich, das Mikrofonrauschen unter den gegebenen Einstellungen des Hörhilfegerätes in Abhängigkeit von der Frequenz zu messen. Ein Vergleich mit der zuvor gemessenen individuellen Ruhehörschwelle des Hörhilfegeräteträgers zeigt nun, ob das Mikrofonrauschen zumindest in bestimmten Frequenzbereichen über der Ruhehörschwelle liegt und damit vom Hörhilfegeräteträger wahrgenommen wird. Gemäß der Erfindung wird dann für die mit dem Hörhilfegerät übertragbaren Frequenzen ein möglichst hohes Maß an Richtwirkung eingestellt, ohne dass dabei das durch das Mikrofonsystem verursachte Mikrofonrauschen die Ruhehörschwelle übersteigt.For this purpose, the rest hearing threshold of the hearing aid wearer is first determined as a function of the frequency of a test signal supplied to the hearing aid wearer's ear. Based on current hearing aid settings, which relate in particular to the signal transmission behavior of the hearing aid and the microphone system, the microphone noise emanating from the microphone system and supplied to the hearing aid wearer's hearing can be calculated fairly accurately over the frequency. As an alternative to the calculation, it is also possible to measure the microphone noise under the given settings of the hearing aid as a function of the frequency. A comparison with the previously measured individual rest hearing threshold of the hearing aid wearer now shows whether the microphone noise is at least in certain frequency ranges above the rest hearing threshold and thus perceived by the hearing aid wearer. According to the invention, the highest possible level of directivity is then set for the frequencies that can be transmitted with the hearing aid device, without the microphone noise caused by the microphone system exceeding the threshold hearing threshold.

Bei einer Ausführungsform der Erfindung wird die Richtcharakteristik des Mikrofonsystems so eingestellt, dass das von dem Mikrofonsystem verursachte und dem Gehör des Hörhilfegeräteträgers zugeführte Mikrofonrauschen zumindest in einem bestimmten Frequenzbereich zwar oberhalb der Ruhehörschwelle liegt, jedoch ein von dem Hörhilfegeräteträger individuell als tolerierbar erachtetes Maß nicht übersteigt. Insbesondere kann durch eine Veränderung der Richtcharakteristik in Abhängigkeit der Frequenz eines akustischen Eingangssignals das Mikrofonrauschen so eingestellt werden, dass dieses zumindest näherungsweise über den gesamten, durch das Hörhilfegerät übertragbaren Frequenzbereich mit der Ruhehörschwelle bzw. dem als tolerierbar erachteten Maß an Rauschen übereinstimmt.In one embodiment of the invention, the directional characteristic of the microphone system is set so that the microphone noise caused by the microphone system and supplied to the hearing aid wearer microphone noise is at least in a certain frequency range above the rest hearing threshold, but one of the hearing aid wearer individually considered tolerable measure does not exceed. In particular, by changing the directional characteristic as a function of the frequency of an acoustic input signal, the microphone noise can be adjusted so that it is at least approximately over the entire, transferable by the hearing aid Frequency range coincides with the quiet auditory threshold or deemed tolerable level of noise.

Eine Ausführungsform der Erfindung sieht vor, dass die Einstellung des Richtmikrofonsystems während des Betriebes des Hörhilfegerätes an die aktuelle Umgebungssituation angepasst wird. Insbesondere wird bei einem Mikrofonsignal mit hohem Signalpegel ein höheres Maß an Richtwirkung zugelassen als dies bei alleiniger Berücksichtigung der Ruhehörschwelle der Fall wäre. Allerdings ist es hierfür erforderlich, den Signalpegel des von dem Mikrofonsystem erzeugten Mikrofonsignals zu messen. Eine Optimierung der Richtwirkung wird insbesondere dann erreicht, wenn die individuelle Maskierungsschwelle des Hörhilfegeräteträgers bezüglich des Mikrofonrauschens bestimmt wird. Diese zeigt an, bei welchem Signalpegel eines von einem akustischen Eingangssignal herrührenden Anteil in dem Ausgangssignal des Mikrofonsystems der Anteil des Mikrofonrauschens in diesem Ausgangssignal maskiert, d.h. verdeckt und damit nicht mehr von dem Hörhilfegeräteträger wahrnehmbar ist. Die Maskierungsschwelle ist abhängig von der Frequenz und dem Signalpegel des Mikrofonrauschens und gibt an, welche Mikrofonsignale dazu geeignet sind, das Mikrofonrauschen zu verdecken. Das Maß an Richtwirkung des Mikrofonsystems wird dann derart variiert, dass in Abhängigkeit der Frequenz eines akustischen Eingangssignals eine möglichst hohe Richtwirkung erreicht wird, ohne dass dabei das Mikrofonrauschen die Maskierungsschelle übersteigt. Analog zu der Ruhehörschwelle kann auch hierbei ein von dem Hörhilfegeräteträger individuell als tolerierbar erachtetes Maß an Mikrofonrauschen zugelassen werden, was bedeutet, dass die Richtwirkung so eingestellt wird, dass das Mikrofonrauschen zumindest in einem bestimmten Frequenzbereich die Maskierungsschwelle auch um ein bestimmtes Maß übersteigen darf. Prinzipiell kann bei der Programmierung des Hörhilfegerätes eine beliebige Funktion festgelegt werden, die angibt, um welchen Wert das Mikrofonrauschen in Abhängigkeit von der Frequenz die Ruhehörschwelle übersteigen oder auch unterschreiten soll. In der Praxis wird man jedoch zumindest für einen bestimmten Frequenzbereich (z.B. von 2 kHz bis 4 kHz) einen konstanten Wert (z.B. 5 dB über der in diesem Frequenzbereich gemessenen Ruhehörschwelle) für das zulässige Mikrofonrauschen festlegen.An embodiment of the invention provides that the setting of the directional microphone system during operation of the hearing aid is adapted to the current environment situation. In particular, in the case of a microphone signal with a high signal level, a higher degree of directivity is permitted than would be the case if only the quiescent hearing threshold were taken into account. However, it is necessary to measure the signal level of the microphone signal generated by the microphone system. An optimization of the directivity is achieved in particular when the individual masking threshold of the hearing aid wearer is determined with respect to the microphone noise. This indicates at which signal level of a component of the microphone system resulting from an acoustic input signal, the proportion of the microphone noise in this output signal is masked, ie hidden, and thus no longer perceptible by the hearing aid wearer. The masking threshold is dependent on the frequency and signal level of the microphone noise and indicates which microphone signals are suitable for masking the microphone noise. The degree of directivity of the microphone system is then varied so that the highest possible directivity is achieved as a function of the frequency of an acoustic input signal, without causing the microphone noise exceeds the Maskierungsschelle. Analogous to the rest hearing threshold, a measure of microphone noise that is individually tolerated by the hearing aid wearer can also be permitted here, which means that the directivity is set such that the microphone noise can exceed the masking threshold by a certain amount, at least in a certain frequency range. In principle, during the programming of the hearing aid device, any function can be specified which indicates by what value the microphone noise should exceed or also fall below the threshold hearing threshold as a function of the frequency. In practice it will However, at least for a certain frequency range (eg from 2 kHz to 4 kHz) a constant value (eg 5 dB above the rest hearing threshold measured in this frequency range) for the permissible microphone noise is set.

Die Einstellung der Richtwirkung des Hörhilfegerätes gemäß der Erfindung in Abhängigkeit von der Ruhehörschwelle bzw. der Maskierungsschwelle kann beispielsweise während der Anpassung des Hörhilfegerätes an den individuellen Hörverlust eines Hörhilfegeräteträgers durch den Akustiker erfolgen. Vorteilhaft erfolgt diese Anpassung jedoch automatisch durch das Programmiergerät, gesteuert durch eine entsprechende Programmiersoftware. Als Eingangsgrößen bei der Berechnung dienen audiometrischen Daten des Hörhilfegeräteträgers, insbesondere die Ruhehörschwelle bzw. die Maskierungsschwelle, Kennwerte des Hörhilfegerätes sowie die Hörhilfegeräteeinstellungen zum Ausgleich des individuellen Hörverlustes des Hörhilfegeräteträgers. Das Programmiergerät errechnet aus diesen Daten dann Werte der Einstellparameter, die die Einstellung der Richtwirkung in Abhängigkeit der Frequenz betreffen. Bei der Einstellung der Richtwirkung in Abhängigkeit der Maskierungsschwelle erfolgt die Einstellung der Richtwirkung zusätzlich in Abhängigkeit des Signalpegels des Ausgangssignals, das dem Gehör des Hörhilfegeräteträgers zugeführt wird. Auch diesbezüglich werden durch das Programmiergerät Einstellparameter errechnet und auf das Hörhilfegerät übertagen, die die Richtwirkung des Mikrofonsystems in Abhängigkeit dieses Signalpegels während des laufenden Betriebes des Hörhilfegerätes regeln.The adjustment of the directivity of the hearing aid according to the invention as a function of the rest hearing threshold or the masking threshold can be done for example during the adaptation of the hearing aid to the individual hearing loss of a hearing aid wearer by the acoustician. However, this adaptation is advantageously carried out automatically by the programming device, controlled by a corresponding programming software. Serving as input variables in the calculation are audiometric data of the hearing aid wearer, in particular the rest hearing threshold or the masking threshold, characteristic values of the hearing aid and the hearing aid settings to compensate for the individual hearing loss of the hearing aid wearer. The programmer then uses these data to calculate values of the setting parameters which relate to the setting of the directivity as a function of the frequency. In the adjustment of the directivity as a function of the masking threshold, the adjustment of the directivity additionally takes place as a function of the signal level of the output signal which is fed to the hearing aid wearer's ear. Also in this regard, setting parameters are calculated by the programmer and transmitted to the hearing aid, which regulate the directivity of the microphone system as a function of this signal level during operation of the hearing aid.

Die Erfindung kann bei allen bekannten Hörhilfegeräte-Typen mit einem einstellbaren Richtmikrofon angewendet werden, beispielsweise bei hinter dem Ohr tragbaren Hörhilfegeräten, in dem Ohr tragbaren Hörhilfegeräten, implantierbaren Hörhilfegeräten oder Taschenhörhilfegeräten. Weiterhin kann das Hörhilfegerät gemäß der Erfindung auch Teil eines mehrere Geräte zur Versorgung eines Schwerhörigen umfassenden Hörhilfegerätesystems sein, z.B. Teil eines Hörgerätesystems mit zwei am Kopf getragenen Hörhilfegeräten zur binauralen Versorgung oder Teil eines Hörgerätesystem, bestehend aus einem am Kopf tragbaren Gerät und einer am Körper tragbaren Prozessoreinheit.The invention can be applied to all known hearing aid types with an adjustable directional microphone, for example, in behind the ear portable hearing aids, in the ear portable hearing aids, implantable hearing aids or Taschenhörhilfegeräten. Furthermore, the hearing aid device according to the invention may also be part of a plurality of devices for supplying a hearing aid device system comprising a hearing-impaired person be part of a hearing aid system with two worn on the head hearing aids for binaural care or part of a hearing aid system consisting of a portable on the head device and a wearable processor unit.

Die Erfindung wird nachfolgend anhand von Ausführungsbeispielen beschrieben. Es zeigen:

  • Figur 1 ein Hörhilfegerät mit einem drei omnidirektionale Mikrofone umfassenden Richtmikrofonsystem,
  • Figur 2 ein Blockschaltbild zur Einstellung eines Richtmikrofonsystems unter Berücksichtigung einer individuellen Ruhehörschwelle,
  • Figur 3 ein Blockschaltbild zur Einstellung eines Richtmikrofons unter Berücksichtigung der individuellen Maskierungsschwelle und
  • Figur 4 ein Blockschaltbild zur Einstellung eines Mikrofonsystems unter Berücksichtigung der individuellen Maskierungsschwelle sowie des von dem Mikrofonsystem erzeugten Ausgangssignals.
The invention will be described below with reference to exemplary embodiments. Show it:
  • FIG. 1 a hearing aid with a directional microphone system comprising three omnidirectional microphones,
  • FIG. 2 a block diagram for setting a directional microphone system taking into account an individual rest hearing threshold,
  • FIG. 3 a block diagram for setting a directional microphone, taking into account the individual masking threshold and
  • FIG. 4 a block diagram for adjusting a microphone system taking into account the individual masking threshold and the output signal generated by the microphone system.

Figur 1 zeigt ein Prinzipschaltbild eines Hörhilfegerätes mit einem Richtmikrofonsystem gemäß der Erfindung. Das Mikrofonsystem umfasst drei omnidirektionale Mikrofone 1, 2 und 3. Das von dem Mikrofon 2 ausgehende Mikrofonsignal wird in einer Verzögerungseinheit 4A verzögert, durch einen Inverter 5A invertiert und in einem Summierer 6A zu dem von dem Mikrofon 1 ausgehenden Mikrofonsignal R0 addiert. Die beiden omnidirektionalen Mikrofone 1 und 2 bilden dadurch ein Richtmikrofon 1, 2 mit Richtcharakteristik erster Ordnung, von dem das Mikrofonsignal R1 ausgeht. Ebenso wird das von dem Mikrofon 3 ausgehende Mikrofonsignal in einer Verzögerungseinheit 4B verzögert, durch einen Inverter 5B invertiert und in einem Summierer 6B zu dem von dem Mikrofon 2 ausgehenden Mikrofonsignal addiert. Auch die Mikrofone 2 und 3 bilden dadurch ein Richtmikrofonsystem 2, 3 mit Richtcharakteristik erster Ordnung, dessen Mikrofonsignal am Ausgang des Summierers 6B anliegt. Wird wiederum das von dem Richtmikrofonsystem 2, 3 ausgehende Mikrofonsignal in einer Verzögerungseinheit 7 verzögert und in einem Inverter 8 invertiert und in einem Summierer 9 zu dem von dem Richtmikrofonsystem 1, 2 ausgehenden Mikrofonsignal R1 addiert, so entsteht aus den Mikrofonen 1, 2 und 3 ein Richtmikrofonsystem 1, 2, 3 mit Richtcharakteristik zweiter Ordnung, dessen Mikrofonsignal R2 am Ausgang des Summierers 9 anliegt. Die drei Mikrofonsignale R0, R1 und R2 sind schließlich einer Schaltungseinheit 10 zugeführt, in der zwischen den unterschiedlichen Mikrofonsignalen umgeschaltet werden kann oder in der die unterschiedlichen Mikrofonsignale R0, R1 und R2 unterschiedlich gewichtet und addiert werden. Das resultierende und am Ausgang der Schaltungseinheit 10 abgegebene Mikrofonausgangssignal RA wird schließlich einer Signalverarbeitungseinheit 11 zugeführt, in der die Weiterverarbeitung und frequenzabhängige Verstärkung des Mikrofonausgangssignals RA zum Ausgleich des individuellen Hörverlustes eines Hörhilfegeräteträgers erfolgt. Schließlich wird das verarbeitete Mikrofonsignal zur Abgabe in einen Gehörgang des Hörhilfegeräteträgers durch einen Hörer 12 in ein akustisches Signal gewandelt. FIG. 1 shows a schematic diagram of a hearing aid with a directional microphone system according to the invention. The microphone system comprises three omnidirectional microphones 1, 2 and 3. The microphone signal emanating from the microphone 2 is delayed in a delay unit 4A, inverted by an inverter 5A and summed in a summer 6A to the microphone signal R0 emanating from the microphone 1. The two omnidirectional microphones 1 and 2 thereby form a directional microphone 1, 2 with directivity of the first order, from which the microphone signal R1 starts. Likewise, the microphone signal emanating from the microphone 3 is delayed in a delay unit 4B, inverted by an inverter 5B and in one Totalizer 6B added to the output from the microphone 2 microphone signal. The microphones 2 and 3 thereby form a directional microphone system 2, 3 with directivity of the first order, the microphone signal is applied to the output of the summer 6B. If, in turn, the microphone signal emitted by the directional microphone system 2, 3 is delayed in a delay unit 7 and inverted in an inverter 8 and added in a summer 9 to the microphone signal R1 emanating from the directional microphone system 1, 2, the result is the microphones 1, 2 and 3 a directional microphone system 1, 2, 3 with directivity second order, the microphone signal R2 is applied to the output of the summer 9. The three microphone signals R0, R1 and R2 are finally fed to a circuit unit 10 in which it is possible to switch between the different microphone signals or in which the different microphone signals R0, R1 and R2 are weighted and added differently. The resulting and output at the output of the circuit unit 10 microphone output signal RA is finally fed to a signal processing unit 11, in which the further processing and frequency-dependent amplification of the microphone output signal RA takes place to compensate for the individual hearing loss of a hearing aid wearer. Finally, the processed microphone signal is converted by an earphone 12 into an acoustic signal for delivery into an auditory canal of the hearing aid wearer.

Moderne Hörhilfegeräte lassen sich in besonderer Weise an unterschiedliche Hörsituationen anpassen. Hierzu weist das Hörhilfegerät im Ausführungsbeispiel eine Steuereinheit 13 auf, in der unterschiedliche Parametersätze, sogenannte Hörprogramme, zur Steuerung der Signalverarbeitung im Hörhilfegerät speicherbar und abrufbar sind. Zwischen den unterschiedlichen Hörprogrammen kann mittels eines Programmwahltasters 14 umgeschaltet werden. Ferner verfügt das Hörhilfegerät über eine automatische Situationserkennung, mittels derer die die Signalverarbeitung betreffenden Parameter des Hörhilfegerätes während des laufenden Betriebes des Hörhilfegerätes angepasst werden können. Zur Signalanalyse ist der Steuereinheit 13 das von dem omnidirektionalen Mikrofon 1 ausgehende Mikrofonsignal zugeführt. Auch die Richtcharakteristik des Mikrofonsystems wird an die erkannte Umgebungssituation bzw. an das eingestellte Hörprogramm angepasst, wobei im Ausführungsbeispiel eine Mikrofonsteuereinheit 15 vorgesehen ist, die ebenfalls durch die Steuereinheit 13 gesteuert wird. Abhängig von der erkannten Umgebungssituation bzw. dem eingestellten Hörprogramm kann somit über die Mikrofonsteuereinheit 15 zwischen Richtmikrofonsystemen mit Richtcharakteristik nullter, erster oder zweiter Ordnung umgeschaltet werden oder es können die von den Richtmikrofonen unterschiedlicher Ordnung ausgehenden Mikrofonsignale, gesteuert durch die Mikrofonsteuereinheit 15, unterschiedlich gewichtet und addiert werden.Modern hearing aids can be adapted in a special way to different listening situations. For this purpose, in the exemplary embodiment, the hearing aid has a control unit 13 in which different parameter sets, so-called hearing programs, can be stored and retrieved in the hearing aid to control the signal processing. Between the different hearing programs can be switched by means of a program selection button 14. Furthermore, the hearing aid has an automatic situation detection, by means of which the signal processing related parameters of the hearing aid adjusted during operation of the hearing aid can be. For signal analysis, the control unit 13 is supplied with the microphone signal emitted by the omnidirectional microphone 1. The directional characteristic of the microphone system is adapted to the detected environmental situation or to the set hearing program, wherein in the embodiment, a microphone control unit 15 is provided, which is also controlled by the control unit 13. Depending on the detected environmental situation or the set hearing program can thus be switched over the microphone control unit 15 between directional microphone systems with directional characteristics zeroth, first or second order or it can be outgoing from the directional microphones of different order microphone signals, controlled by the microphone control unit 15, weighted differently and added become.

Bei dem Hörhilfegerät gemäß dem Ausführungsbeispiel ist vorgesehen, dass die Einstellung der Richtcharakteristik unter Berücksichtigung der individuellen Ruhehörschwelle eines Hörhilfegeräteträgers erfolgt. Diese wird durch einen Gehörtest ermittelt, der in der Regel von einem Hörgeräte-Akustiker durchgeführt wird. Ferner wird bei dem Hörhilfegerät gemäß dem Ausführungsbeispiel das Mikrofonrauschen für unterschiedliche Richtcharakteristiken ermittelt, z.B. gemessen oder unter Berücksichtigung der Mikrofon-Kenndaten, der unterschiedlichen Verschaltungen der Mikrofone sowie der Signalverarbeitung im Hörhilfegerät bei den jeweiligen Hörhilfegeräte-Einstellungen errechnet. Anschließend wird bei dem Hörhilfegerät die Richtwirkung in Abhängigkeit der Frequenz, der Ruhehörschwelle sowie des Mikrofonrauschens bei der jeweiligen Frequenz eingestellt. Liegt z.B. in einem Frequenzbereich die individuelle Ruhehörschwelle des Hörhilfegeräteträgers bei 30dB SPL, so wird die Richtcharakteristik so eingestellt, dass das von dem Mikrofonsystem erzeugte und dem Gehör des Hörhilfegeräteträgers zugeführte Mikrofonrauschen in der Größenordnung dieser Ruhehörschwelle liegt, so dass ein möglichst hohes Maß an Richtwirkung erreicht wird, ohne dass dabei das durch das Mikrofonsystem erzeugte Mikrofonrauschen von dem Hörhilfegeräteträger als störend empfunden wird. Liegt in einem anderen Frequenzbereich die Ruhehörschwelle des Hörhilfegeräteträgers z.B. bei 50dB SPL, so kann in diesem Frequenzbereich ein höheres Maß an Richtwirkung zugelassen werden, beispielsweise eine Richtcharakteristik zweiter Ordnung, ohne dass dabei das Mikrofonrauschen von dem Hörhilfegeräteträger wahrgenommen wird.In the hearing aid device according to the exemplary embodiment, it is provided that the adjustment of the directional characteristic takes place taking into account the individual rest hearing threshold of a hearing aid wearer. This is determined by an auditory test, which is usually performed by a hearing care professional. Further, in the hearing aid according to the embodiment, the microphone noise for different directional characteristics is determined, for example, measured or calculated taking into account the microphone characteristics, the different interconnections of the microphones and the signal processing in the hearing aid at the respective hearing aid settings. Subsequently, in the hearing aid, the directivity is set as a function of the frequency, the rest hearing threshold and the microphone noise at the respective frequency. If, for example, the individual resting hearing threshold of the hearing aid wearer is at 30 dB SPL in a frequency range, the directional characteristic is set such that the microphone noise generated by the microphone system and supplied to the hearing aid wearer's hearing is of the order of magnitude of this rest hearing threshold, so that the highest possible directivity is achieved without the microphone noise generated by the microphone system is perceived by the hearing aid wearer as disturbing. If the rest hearing threshold of the hearing aid wearer lies in another frequency range, for example at 50 dB SPL, a higher degree of directivity can be allowed in this frequency range, for example a second order directivity, without the microphone noise being perceived by the hearing aid wearer.

Bei der Einstellung des Hörhilfegerätes wird somit das Ziel verfolgt, ein möglichst hohes Maß an Richtwirkung zuzulassen, ohne dass dabei das von dem Mikrofonsystem erzeugte Mikrofonrauschen unter Berücksichtigung der aktuellen Hörhilfegeräteeinstellungen oberhalb der individuellen Ruhehörschwelle des Hörhilfegeräteträgers liegt.In the setting of the hearing aid device, the goal is thus pursued to allow the highest possible level of directivity without causing the microphone noise generated by the microphone system, taking into account the current hearing aid settings above the individual rest hearing threshold of the hearing aid wearer.

Eine andere Strategie der Hörhilfegeräteeinstellung kann darin bestehen, dass ein von dem Hörhilfegeräteträger wahrnehmbares Mikrofonrauschen ein bestimmtes Maß nicht übersteigt. Das Mikrofonsystem wird dann so eingestellt, dass in dem Ausgangssignal des Hörhilfegerätes das von dem Mikrofonsystem hervorgerufene Mikrofonrauschen maximal um eben dieses Maß die Ruhehörschwelle des Hörhilfegeräteträgers übersteigt. Dabei kann sich dieses von dem Hörhilfegeräteträger als tolerierbar erachtete Maß an Mikrofonrauschen über den gesamten, durch das Hörhilfegerät übertragbaren Frequenzbereich beziehen oder nur auf einen bestimmten Frequenzbereich beschränken.Another strategy of hearing aid setting may be that a microphone noise perceivable by the hearing aid wearer does not exceed a certain level. The microphone system is then adjusted so that in the output signal of the hearing aid device, the microphone noise caused by the microphone system exceeds the rest hearing threshold of the hearing aid wearer by a maximum of just this degree. In the process, this amount of microphone noise, which is considered tolerable by the hearing aid wearer, can relate to the entire frequency range which can be transmitted by the hearing aid device or can only be limited to a specific frequency range.

Eine Weiterentwicklung der Erfindung sieht vor, dass der Mikrofonsteuereinheit 15 auch das Ausgangssignal der Steuereinheit 10 und damit das zur Weiterverarbeitung bestimmte Mikrofonausgangssignal RA zugeführt ist. Dies hat den Vorteil, dass neben der individuellen Ruhehörschwelle auch der Signalpegel dieses Mikrofonsignals bei der Einstellung der Richtcharakteristik berücksichtigt werden kann. Das Mikrofonrauschen wird nämlich nur bei verhältnismäßig niedrigen Signalpegeln dieses Mikrofonausgangssignals RA als störend empfunden. Bei einem verhältnismäßig hohen Pegel dieses Mikrofonausgangssignals RA nimmt das Mikrofonrauschen nur einen kleinen Anteil an diesem Signal ein und der überwiegende Anteil des Mikrofonausgangssignals RA wird durch das akustische Eingangssignal bestimmt. Dies führt jedoch dazu, dass das Mikrofonrauschen ohnehin durch das akustische Eingangssignal verdeckt (maskiert) und somit durch den Hörhilfegeräteträger nicht wahrgenommen wird. Es kann somit in einer derartigen Hörsituation ein höheres Maß an Richtwirkung zugelassen werden als dies bei der reinen Berücksichtigung der Ruhehörschwelle der Fall wäre. Bei einem Mikrofonausgangssignal RA mit sehr hohem Signalpegel kann somit stets die größtmögliche Richtwirkung des Mikrofonsystems eingestellt werden, ohne dass hierdurch das Mikrofonrauschen von dem Hörhilfegeräteträger als störend empfunden wird. Die Anpassung der Richtcharakteristik des Mikrofonsystems an die Ruhehörschwelle ist daher besonders bei Mikrofonausgangssignalen RA mit niedrigem Signalpegel wichtig, da bei diesen das Mikrofonrauschen in dem Mikrofonsignal überwiegt und somit als störend empfunden werden kann.A further development of the invention provides that the microphone control unit 15 is also supplied with the output signal of the control unit 10 and thus with the microphone output signal RA intended for further processing. This has the advantage that, in addition to the individual rest threshold, the signal level of this microphone signal can also be taken into account when setting the directional characteristic. The microphone noise is perceived as disturbing only at relatively low signal levels of this microphone output signal RA. At a relatively high level of this microphone output signal RA, the microphone noise takes up only a small portion of this signal and the majority of the microphone output signal RA is determined by the acoustic input signal. However, this leads to the fact that the microphone noise anyway covered by the acoustic input signal (masked) and thus is not perceived by the hearing aid wearer. It can thus be allowed in such a hearing situation, a higher degree of directivity than would be the case with the pure consideration of the rest hearing threshold. In the case of a microphone output signal RA with a very high signal level, it is therefore always possible to set the maximum directivity of the microphone system without the microphone noise from the hearing aid device carrier being perceived as disturbing. The adaptation of the directional characteristic of the microphone system to the rest hearing threshold is therefore particularly important for microphone output signals RA with low signal level, since in these the microphone noise predominates in the microphone signal and thus can be distracting.

Eine weitere Optimierung des Richtmikrofonsystems wird dadurch erreicht, dass bei dem Hörhilfegeräteträger die individuelle Maskierungsschwelle für das Mikrofonrauschen bestimmt wird. Dann kann die Richtwirkung in Abhängigkeit der Frequenz der von den Mikrofonen 1-3 ausgehenden Mikrofonsignale R0, R1 und R2 so eingestellt werden, dass stets die maximale Richtwirkung eingestellt ist, bei der das Mikrofonrauschen gerade noch verdeckt wird. Im Falle eines sehr leisen akustischen Eingangssignals bzw. ohne akustisches Eingangssignal wird dann automatisch zumindest im Wesentlichen nur das von dem omnidirektionalen Mikrofon 1 ausgehende Mikrofonsignal R0 an die Signalverarbeitungseinheit 11 weitergeleitet. Mit zunehmendem Signalpegel in dem Mikrofonsignal wird dann stufenweise auf Richtcharakteristiken höherer Ordnung umgeschaltet oder kontinuierlich das Gewicht des Mikrofonsignals R1 bzw. R2 gegenüber R0 erhöht.Further optimization of the directional microphone system is achieved by determining the individual masking threshold for the microphone noise in the hearing aid wearer. Then, the directivity depending on the frequency of outgoing from the microphones 1-3 microphone signals R0, R1 and R2 can be set so that always the maximum directivity is set, in which the microphone noise is barely concealed. In the case of a very quiet acoustic input signal or without acoustic input signal, at least substantially only the microphone signal R0 emanating from the omnidirectional microphone 1 is then automatically forwarded to the signal processing unit 11. As the signal level in the microphone signal increases, the directional characteristics of higher order are gradually switched or the weight of the microphone signal R1 or R2 is increased continuously relative to R0.

Ebenso wie bei der Ruhehörschwelle kann auch bei der Berücksichtigung der Maskierungsschwelle ein bestimmtes Maß an Mikrofonrauschen von dem individuellen Hörhilfegeräteträger als tolerierbar erachtet werden. Dann wird die Richtcharakteristik des Mikrofonsystems so eingestellt, dass dieses Maß an Mikrofonrauschen entweder über den gesamten übertragbaren Frequenzbereich oder lediglich in wenigstens einem Frequenzband von dem Hörhilfegeräteträger wahrnehmbar bleibt.As with the rest hearing threshold, a certain level of microphone noise from the individual hearing aid wearer can also be considered tolerable when the masking threshold is taken into account. Then, the directional characteristic of the microphone system is adjusted so that this level of microphone noise remains perceptible either over the entire transmittable frequency range or only in at least one frequency band of the hearing aid wearer.

In dem Ausführungsbeispiel gemäß Figur 1 ist der Mikrofonsteuereinheit 15 das Mikrofonausgangssignal RA zugeführt um die Richtwirkung des Mikrofonsystems so einzustellen, dass das dem Gehör des Hörhilfegeräteträger zugeführte Mikrofonrauschen unterhalb der Ruhehörschwelle liegt bzw. durch ein Nutzsignal verdeckt wird. Da die Rückkopplung somit vor der eigentlichen Signalverarbeitung im Hörhilfegerät mittels der Signalverarbeitungseinheit 11 erfolgt, sind der Mikrofonsteuereinheit 15 zusätzlich auch die aktuellen Steuerparameter der Steuereinheit 13 zugeführt, so dass die Weiterverarbeitung des Mikrofonausgangssignals RA durch die Signalverarbeitungseinheit 11 berücksichtigt werden kann. Alternativ könnte der Mikrofonsteuereinheit 15 auch das Ausgangsignal der Signalverarbeitungseinheit 11 zugeführt werden.In the embodiment according to FIG. 1 the microphone control unit 15 is supplied with the microphone output signal RA in order to set the directivity of the microphone system such that the microphone noise supplied to the hearing aid wearer's hearing lies below the rest hearing threshold or is concealed by a useful signal. Since the feedback thus takes place before the actual signal processing in the hearing aid by means of the signal processing unit 11, the microphone control unit 15 is additionally supplied with the current control parameters of the control unit 13, so that the further processing of the microphone output signal RA by the signal processing unit 11 can be taken into account. Alternatively, the microphone control unit 15 could also be supplied with the output signal of the signal processing unit 11.

Die Signalverarbeitung bei dem Hörhilfegerät gemäß dem Ausführungsbeispiel kann in analoger, digitaler oder in kombinierter Schaltungstechnik erfolgen. Weiterhin kann die Signalverarbeitung auch parallel in aneinandergrenzenden Frequenzbändern (Kanälen) erfolgen. Vorzugsweise erfolgt auch die Einstellung der Richtcharakteristik des Mikrofonsystems in Frequenzbändern.The signal processing in the hearing aid device according to the exemplary embodiment can take place in analog, digital or in combined circuit technology. Furthermore, the signal processing can also take place in parallel in adjoining frequency bands (channels). Preferably, the adjustment of the directional characteristic of the microphone system in frequency bands.

Nachfolgend werden in den Figuren 2 bis 4 die wesentlichen Schritte bei der Einstellung eines Hörhilfegerätes gemäß der Erfindung in verallgemeinerter Darstellung nochmals veranschaulicht. Dabei zeigt Figur 2 ein Blockschaltbild zur Einstellung eines Richtmikrofonsystems unter Berücksichtigung einer individuellen Ruhehörschwelle. Das Mikrofonsystem des Hörhilfegerätes umfasst ein Mikrofon-Array 20 mit mehreren Mikrofonen, von denen jeweils ein Mikrofonsignal abgegeben wird. Zur Einstellung der Richtcharakteristik sind die Mikrofonsignale einer Schaltungseinheit 21 zugeführt. Diese liefert an ihrem Signalausgang ein Mikrofonsignal, das zur Weiterverarbeitung in dem Hörhilfegerät vorgesehen ist. Ziel der Hörhilfegeräteeinstellung ist es, ein möglichst hohes Maß an Richtwirkung zu erzielen, ohne dabei das Mikrofonrauschen derart ansteigen zu lassen, dass dies von einem Hörhilfegeräteträger als störend empfunden wird. Um eine derartige Einstellung des Mikrofonsystems zu erreichen, wird zunächst mit einer Testeinrichtung die individuelle Ruhehörschwelle des Hörhilfegeräteträgers in Abhängigkeit der Frequenz eines dem Gehör des Hörhilfegeräteträgers zugeführten Testsignals ermittelt und in einer Speichereinrichtung 22 gespeichert. Die Messung der Ruhehörschwelle kann von einem Hörgeräte-Akustiker durchgeführt werden, sie kann aber auch mit einer geeigneten Messeinrichtung (PC mit entsprechender Software) bzw. einem Hörhilfegerät mit integriertem Tongenerator von dem Hörhilfegeräteträger selbst durchgeführt werden. Ist die individuelle Ruhehörschwelle eines Hörhilfegeräteträgers in Abhängigkeit der Frequenz bekannt, so lässt sich daraus auch die erforderliche Verstärkung leiser Eingangssignale in Abhängigkeit von der Frequenz durch das Hörhilfegerät ermitteln, um den Hörverlust auszugleichen. In der Regel wird der Hörverlust durch das Hörhilfegerät jedoch nicht vollständig ausgeglichen, sondern bezogen auf die Ruhehörschwelle eines Normalhörenden lediglich um beispielsweise 50% vermindert. Aus der notwendigen Verstärkung leiser Eingangssignale wiederum kann das dem Gehör des Hörhilfegeräteträgers zugeführte Mikrofonrauschen bei leisen Eingangssignalen bzw. beim Fehlen eines akustischen Eingangssignals bestimmt werden. Zum Bestimmen des Mikrofonrauschens in Abhängigkeit der Frequenz und unterschiedlicher Einstellungen bezüglich der Richtcharakteristik werden entweder Messungen an dem Hörhilfegerät durchgeführt oder das jeweilige Mikrofonrauschen wird anhand von Hörhilfegeräte- sowie Mikrofon-Kenndaten errechnet. Unter Berücksichtigung der so gewonnenen Kenndaten wird nun eine optimierte Richtcharakteristik des Mikrofon-Arrays in Abhängigkeit der Frequenz eines akustischen Eingangssignals und der individuellen Ruhehörschwelle des Hörhilfegeräteträgers bei der jeweiligen Frequenz ermittelt, wobei hierzu die Werte von Einstellparametern des Hörhilfegerätes und insbesondere der Schaltungseinheit 21 zur Einstellung eben dieser Richtcharakteristik errechnet und bei dem Hörhilfegerät eingestellt werden. Die Berechnung erfolgt in einer Recheneinrichtung 23, die vorzugsweise als Programmiergerät oder PC mit einer entsprechenden Software ausgebildet ist und die Speichereinrichtung 22 umfasst. Die errechneten Parameter werden dann auf das Hörhilfegerät übertragen. Die Recheneinrichtung 23 kann aber auch innerhalb des Hörhilfegerätes angeordnet sein. Vorteilhaft erfolgt die Einstellung des Hörhilfegerätes und insbesondere der Schaltungseinheit 21 derart, dass das dem Gehör des Hörhilfegeräteträgers zugeführte Mikrofonrauschen zumindest näherungsweise mit dessen Ruhehörschwelle übereinstimmt oder diese zumindest nicht übersteigt. Weiterhin kann die Richtwirkung des Mikrofon-Arrays auch so eingestellt werden, dass das resultierende Mikrofonrauschen zumindest in einem bestimmten Frequenzbereich die Ruhehörschwelle des Hörhilfegeräteträgers um ein von diesem tolerierbares Maß übersteigt. Vorzugsweise ist dieses Maß in Abhängigkeit von der Frequenz frei wählbar.Below are in the FIGS. 2 to 4 the essential steps in the setting of a hearing aid according to the invention in a generalized representation again illustrated. It shows FIG. 2 a block diagram for setting a directional microphone system taking into account an individual rest threshold. The microphone system of the hearing aid comprises a microphone array 20 with a plurality of microphones, from each of which a microphone signal is emitted. To adjust the directional characteristic, the microphone signals are fed to a circuit unit 21. This provides at its signal output a microphone signal, which is provided for further processing in the hearing aid. The aim of the hearing aid setting is to achieve the highest possible level of directivity, without causing the microphone noise to rise so that this is perceived by a hearing aid wearer as disturbing. In order to achieve such an adjustment of the microphone system, the individual resting hearing threshold of the hearing aid wearer is first determined with a test device as a function of the frequency of a test signal supplied to the hearing aid wearer's hearing device and stored in a memory device 22. The measurement of the rest hearing threshold can be carried out by a hearing aid acoustician, but it can also be carried out by the hearing aid wearer himself with a suitable measuring device (PC with corresponding software) or a hearing aid device with integrated tone generator. If the individual rest hearing threshold of a hearing aid wearer is known as a function of the frequency, the required amplification of quiet input signals as a function of the frequency by the hearing aid can also be determined therefrom in order to compensate for the hearing loss. In general, the hearing loss is not completely compensated by the hearing aid, but based on the resting hearing threshold of a normal hearing only by 50%, for example. From the necessary amplification of quiet input signals, in turn, the microphone noise supplied to the hearing aid wearer's hearing aid can be determined with quiet input signals or in the absence of an acoustic input signal. To determine the microphone noise as a function of the frequency and different settings with respect to the directional characteristic, either measurements are made on the hearing aid performed or the respective microphone noise is calculated based on Hearing aid and microphone characteristics. Taking into account the characteristic data thus obtained, an optimized directional characteristic of the microphone array is now determined as a function of the frequency of an acoustic input signal and the individual rest hearing threshold of the hearing aid wearer at the respective frequency, for which purpose the values of adjustment parameters of the hearing aid and in particular of the circuit unit 21 for adjustment this directional characteristic calculated and adjusted in the hearing aid. The calculation takes place in a computing device 23, which is preferably designed as a programming device or PC with a corresponding software and includes the memory device 22. The calculated parameters are then transferred to the hearing aid. However, the computing device 23 can also be arranged within the hearing aid. Advantageously, the adjustment of the hearing aid and in particular of the circuit unit 21 is such that the hearing aid supplied to the hearing aid carrier microphone noise at least approximately coincides with the rest hearing threshold or at least does not exceed. Furthermore, the directivity of the microphone array can also be adjusted so that the resulting microphone noise exceeds the rest hearing threshold of the hearing aid wearer by a tolerable measure of this at least in a certain frequency range. Preferably, this measure is freely selectable depending on the frequency.

Eine gegenüber dem Ausführungsbeispiel gemäß Figur 2 verbesserte Einstellung der Richtwirkung des Mikrofonsystems lässt sich mit der Einstellung des Mikrofon-Arrays gemäß Figur 3 erreichen. Auch hierbei sind die Mikrofonsignale einer Anzahl an Mikrofonen 30 zur Einstellung der Richtcharakteristik zunächst einer Schaltungseinheit 31 zugeführt. Anders als im vorhergehenden Ausführungsbeispiel erfolgt dabei die Einstellung jedoch nicht statisch, z.B. einmalig während der Anpassung des Hörhilfegerätes durch den Akustiker, sondern adaptiv während des laufenden Betriebes des Hörhilfegerätes. Zur Einstellung der Richtwirkung wird das von dem Mikrofonsystem erzeugte Mikrofonsignal oder ein daraus hervorgehendes Signal ebenfalls berücksichtigt. Weist das Mikrofonsignal zumindest in einem bestimmten Frequenzbereich einen hohen Signalpegel auf, so kann zumindest in diesem Frequenzbereich ein höheres Mikrofonrauschen und damit ein höheres Maß an Richtwirkung toleriert werden. Die Richtwirkung wird dann zumindest in diesem Frequenzbereich derart erhöht, bis der Anteil des Mikrofonrauschens in dem Ausgangssignal gerade noch durch den aus dem akustischen Eingangssignal hervorgehenden Anteil des Ausgangssignals verdeckt wird oder die maximale Richtwirkung erreicht ist. Dadurch wird gewährleistet, dass stets die maximale Richtwirkung eingestellt ist, bei der das Mikrofonrauschen nicht als störend empfunden wird. Auch die Maskierungsschwelle für das Mikrofonrauschen wird anhand von Testsignalen ermittelt, die dem Gehör des Hörhilfegeräteträgers z.B. während der Anpassung des Hörhilfegerätes zugeführt werden. Als Testsignale werden bevorzugt Sinussignale, weißes Rauschen oder ein dem Mikrofonrauschen ähnliches Rauschen verwendet. Daten bezüglich der gemessenen, individuellen Maskierungsschwelle in Abhängigkeit der Frequenz werden dann in einer Speichereinrichtung 32 im Hörhilfegerät gespeichert. Eine Recheneinrichtung 33 errechnet aus diesen Daten und dem Ausgangssignal der Schaltungseinheit 31 adaptiv eine optimierte Einstellung der Schaltungseinheit 31, so dass so viel Richtwirkung wie möglich eingestellt ist und dennoch kein Mikrofonrauschen von dem Hörhilfegeräteträger wahrgenommen wird. Auch bei diesem Ausführungsbeispiel kann man eine alternative Ausführungsform dadurch realisieren, dass die Richtwirkung des Mikrofon-Arrays so eingestellt wird, dass das resultierende Mikrofonrauschen zumindest in einem bestimmten Frequenzbereich die Ruhehörschwelle des Hörhilfegeräteträgers um ein von diesem tolerierbares Maß übersteigt. Vorzugsweise ist auch dieses Maß in Abhängigkeit von der Frequenz frei wählbar.One over the embodiment according to FIG. 2 improved adjustment of the directivity of the microphone system can be adjusted with the microphone array according to FIG. 3 to reach. Here, too, the microphone signals of a number of microphones 30 for adjusting the directional characteristic are first supplied to a circuit unit 31. Unlike the previous embodiment, however, the setting is not static, for example, once during the adaptation of the hearing aid by the acoustician, but adaptive during operation of the hearing aid. To adjust the directivity of the microphone signal generated by the microphone system or a signal resulting from it is also taken into account. If the microphone signal has a high signal level at least in a certain frequency range, then a higher microphone noise and thus a higher degree of directivity can be tolerated at least in this frequency range. The directivity is then increased at least in this frequency range until the proportion of the microphone noise in the output signal is just concealed by the portion of the output signal resulting from the acoustic input signal, or the maximum directivity is achieved. This ensures that the maximum directivity is always set at which the microphone noise is not perceived as disturbing. The masking threshold for the microphone noise is also determined on the basis of test signals which are supplied to the hearing aid wearer's hearing, for example during the adaptation of the hearing aid. As test signals, sinusoidal signals, white noise, or noise similar to microphone noise are preferably used. Data relating to the measured, individual masking threshold as a function of the frequency are then stored in a memory device 32 in the hearing aid. A computing device 33 calculates adaptively an optimized setting of the circuit unit 31 from these data and the output signal of the circuit unit 31, so that as much directivity as possible is set and nevertheless no microphone noise is perceived by the hearing aid device carrier. In this exemplary embodiment, too, an alternative embodiment can be realized in that the directivity of the microphone array is adjusted so that the resulting microphone noise exceeds the rest hearing threshold of the hearing aid wearer by a tolerable amount, at least in a certain frequency range. Preferably, this measure is freely selectable depending on the frequency.

Eine weitere Ausführungsform zur Einstellung der Richtwirkung eines Mikrofonsystems mit mehreren Mikrofonen 40 zeigt Figur 4. Auch hierbei erfolgt die Einstellung wie bei der vorhergehenden Ausführungsform adaptiv unter Berücksichtigung der individuellen Maskierungsschwelle. Im Unterschied zum Ausführungsbeispiel gemäß Figur 3 wird dabei jedoch das zur Weiterverarbeitung in einer Signalverarbeitungseinheit des Hörhilfegerätes vorgesehene Ausgangssignal einer Schaltungseinheit 41 nicht berücksichtigt. Das Mikrofonsystem umfasst stattdessen eine zweite Schaltungseinheit 42, in die ebenfalls die von den omnidirektionalen Mikrofonen 40 erzeugten Mikrofonsignale eingehen und aus der das zur Weiterverarbeitung vorgesehene Ausgangssignal des Mikrofonsystems hervorgeht. Dabei sind die Einstellungen der ersten Schaltungseinheit 41 statisch, d.h., sie werden allenfalls bei der Anpassung des Hörhilfegerätes, jedoch nicht während des normalen Betriebes eingestellt. Das Ausgangssignal dieser ersten Schaltungseinheit 41 wird dann zusammen mit den Daten bzgl. der individuellen Maskierungsschwelle des Hörhilfegeräteträgers, die in einer Speichereinrichtung 43 im Hörhilfegerät hinterlegt sind, dazu verwendet, die zweite Schaltungseinheit 42 zu Steuern. Ergibt sich z.B., dass in der momentanen Hörsituation bei den statischen Einstellungen der ersten Schaltungseinheit 41 das Mikrofonrauschen von dem akustischen Eingangssignal verdeckt werden würde, so kann bei der adaptiven Schaltungseinheit 42 ein höheres Maß an Richtwirkung eingestellt werden. Die Einstellparameter der Schaltungseinheit 42 werden dabei während das laufenden Betriebes des Hörhilfegerätes aus dem in der Speichereinrichtung 43 hinterlegten Verlauf der Maskierungsschwelle in Abhängigkeit der Frequenz und der Signalpegel des Mikrofonrauschens und des Nutzsignals sowie des Ausgangssignals der Schaltungseinheit 41 mittels der Recheneinrichtung 44 ermittelt. Insbesondere wird bei dieser Berechnung auch das Maß der Verdeckung, d.h. der Unterschied des Signalpegels des Mikrofonrauschens im Vergleich zum Signalpegel des von dem akustischen Eingangssignal herrührenden Anteils in dem Ausgangssignal der Schaltungseinheit 41, mit berücksichtigt. Bei einem großen Unterschied dieser beiden Signalpegel kann durch die Recheneinrichtung 44 bei der Schaltungseinheit 42 eine verhältnismäßig große Zunahme der Richtwirkung gegenüber der durch die Schaltungseinheit 41 erzeugten Richtwirkung eingestellt werden. Der Vorteil dieser Ausführungsform liegt darin, dass eine Rückkopplungsschleife wie im vorhergehenden Ausführungsbeispiel vermieden wird.Another embodiment for adjusting the directivity of a microphone system with multiple microphones 40 shows FIG. 4 , Again, as in the previous embodiment, the adjustment is adaptive taking into account the individual masking threshold. In contrast to the embodiment according to FIG. 3 However, the output signal of a circuit unit 41 provided for further processing in a signal processing unit of the hearing aid device is not considered. Instead, the microphone system comprises a second circuit unit 42, into which the microphone signals generated by the omnidirectional microphones 40 also enter and from which the output signal of the microphone system provided for further processing emerges. In this case, the settings of the first circuit unit 41 are static, ie, they are adjusted at best during the adaptation of the hearing aid, but not during normal operation. The output signal of this first circuit unit 41 is then used together with the data relating to the individual masking threshold of the hearing aid wearer, which are stored in a memory device 43 in the hearing aid, to control the second circuit unit 42. If, for example, it results that in the current listening situation in the static settings of the first circuit unit 41 the microphone noise would be obscured by the acoustic input signal, a higher degree of directivity can be set in the adaptive circuit unit 42. The setting parameters of the circuit unit 42 are thereby determined during operation of the hearing aid from the stored in the memory device 43 course of the masking threshold depending on the frequency and the signal level of the microphone noise and the desired signal and the output signal of the circuit unit 41 by means of the computing device 44. In particular, in this calculation also the degree of occlusion, ie the difference of the signal level of the microphone noise in comparison to the signal level of the signal originating from the acoustic input signal in the output signal of the circuit unit 41, with considered. With a large difference of these two signal levels can be set by the computing device 44 in the circuit unit 42, a relatively large increase in the directivity against the directivity generated by the circuit unit 41. The advantage of this embodiment is that a feedback loop as in the previous embodiment is avoided.

Als Alternative zu der individuell am Träger des einzustellenden Hörhilfegerätes gemessenen Maskierungsschwelle kann der adaptiven Einstellung eines Richtmikrofonsystems gemäß der Erfindung auch ein Maskierungsmodell zugrunde liegen, das auf Messungen an einer Vielzahl an Probanden beruht. In den Speichereinrichtungen 32 bzw. 43 der Ausführungsbeispiele gemäß den Figuren 3 und 4 sind dann Daten bezüglich dieses allgemeinen Maskierungsmodells abgelegt, das bei der Berechnung von Einstellparametern des Richtmikrofonsystems in der Regel ebenfalls gute Ergebnisse liefert. Die aufwendige Messung der individuellen Maskierungsschwelle kann dadurch entfallen.As an alternative to the masking threshold measured individually on the wearer of the hearing aid to be set, the adaptive setting of a directional microphone system according to the invention can also be based on a masking model based on measurements on a large number of test persons. In the memory devices 32 and 43 of the embodiments according to the Figures 3 and 4 are then stored data relating to this general masking model, which usually also provides good results in the calculation of setting parameters of the directional microphone system. The complex measurement of the individual masking threshold can thereby be omitted.

Zusammenfassend soll durch die Erfindung bei einem Hörhilfegerät mit einem mehrere Mikrofone umfassenden Mikrofonsystem die Richtwirkung verbessert werden, ohne dass hierbei eine von einem Hörhilfegeräteträger als störend empfundene Zunahme des Mikrofonrauschens entsteht. Hierzu schlägt die Erfindung vor, dass die Einstellung des Mikrofonsystems statisch oder adaptiv unter Berücksichtigung der individuellen Ruhehörschwelle bzw. unter Berücksichtigung der individuellen Maskierungsschwelle für das von dem Mikrofonsystem erzeugte Mikrofonrauschen erfolgt. Somit kann stets das größtmögliche Maß an Richtwirkung zugelassen werden, ohne dass dabei der Hörhilfegeräteträger das von dem Mikrofonsystem erzeugte Mikrofonrauschen als störend empfindet.In summary, the directivity is to be improved by the invention in a hearing aid with a microphone system comprising several microphones, without this one of a hearing aid wearer perceived as disturbing increase in microphone noise. For this purpose, the invention proposes that the adjustment of the microphone system takes place statically or adaptively taking into account the individual rest hearing threshold or taking into account the individual masking threshold for the microphone noise generated by the microphone system. Thus, the greatest possible degree of directivity can always be allowed without the hearing aid wearer perceiving the microphone noise generated by the microphone system as disturbing.

Claims (14)

  1. Method for adjustment of a hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of at least one microphone output signal (RA), having a signal processing unit (11) and having an output transducer (12), having the following steps:
    a) determination of a rest hearing threshold of a hearing aid wearer as a function of the signal frequency of a test signal which is supplied to the hearing of the hearing aid wearer, and
    b) adjustment of the directional characteristic of the microphone system (1, 2, 3) of the hearing aid as a function of the frequency of the acoustic input signal and of the rest hearing threshold.
  2. Method according to Claim 1, wherein the directional characteristic is adjusted as a function of the frequency of the acoustic input signal and of the signal level of the microphone output signal (RA) that is produced by the microphone system (1, 2, 3) such that the signal level of the microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer at least essentially matches the rest hearing threshold at the respective frequency.
  3. Method according to Claim 1, wherein the directional characteristic is adjusted as a function of the frequency of the acoustic input signal and of the signal level of the microphone output signal (RA) that is produced by the microphone system (1, 2, 3) such that the signal level of the microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer differs at least essentially by an adjustable value from the rest hearing threshold at the respective frequency.
  4. Method according to one of Claims 1 to 3, wherein the parameters for adjustment of the directional characteristic of the microphone system (1, 2, 3) of the hearing aid are determined automatically as a function of the frequency of the acoustic input signal and of the rest hearing threshold.
  5. Method for adjustment of a hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of at least one microphone output signal (RA), having a signal processing unit (9) and having an output transducer (10), having the following steps:
    a) determination of a masking threshold of a hearing aid wearer in order to mask the microphone noise that is produced by the microphone system (1, 2, 3), as a function of the signal frequency and of the signal level of a test signal which is supplied to the hearing of the hearing aid wearer,
    b) determination of the signal level of a microphone output signal (RA) that is produced by the microphone system (1, 2, 3), as a function of the frequency of the microphone output signal (RA),
    c) adjustment of the directional characteristic of the hearing aid as a function of the frequency of the microphone output signal (RA), of the masking threshold and of the determined signal level.
  6. Method according to Claim 5, wherein the directional characteristic is adjusted as a function of the frequency of the microphone output signal (RA) and of the signal level of the microphone output signal (RA) that is produced by the microphone system (1, 2, 3) such that the signal level of the microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer at least essentially matches the masking threshold at the respective frequency.
  7. Method according to Claim 5, wherein the directional characteristic is adjusted as a function of the frequency of the microphone output signal (RA) and of the signal level of the microphone output signal (RA) that is produced by the microphone system (1, 2, 3) such that the signal level of the microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer differs at least essentially by a constant value from the masking threshold at the respective frequency.
  8. Method according to one of Claims 5 to 7, wherein the parameters for the adjustment of the directional characteristic of the hearing aid are determined automatically as a function of the frequency of the microphone output signal (RA), of the masking threshold and of the determined signal level.
  9. Hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of a microphone output signal (RA), having a signal processing unit (11) and having an output transducer (12), wherein the directional characteristic of the microphone system (1, 2, 3) is adjusted as a function of the frequency of the acoustic input signal and a residual hearing threshold of a hearing aid wearer such that a signal level of a microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer at least essentially matches the rest hearing threshold of the hearing aid wearer at the respective frequency.
  10. Hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of a a microphone output signal (RA), having a signal processing unit (11) and having an output transducer (12), wherein the directional characteristic of the microphone system (1, 2, 3) is adjusted as a function of the frequency of the microphone output signal (RA) as a function of the frequency of the acoustic input signal and a residual hearing threshold of a hearing aid wearer such that the signal level of a microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer differs at least essentially by an adjustable value from the rest hearing threshold of the hearing aid wearer at the respective frequency.
  11. Hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of at least one microphone output signal (RA), having a signal processing unit (11) and having an output transducer (12), wherein the directional characteristic of the microphone system (1, 2, 3) is adjusted as a function of the frequency of the microphone output signal (RA) and a masking threshold of the hearing aid wearer at the respective frequency such that the signal level of a microphone noise which is produced by the microphone system (1, 2, 3) and is supplied to the hearing of the hearing aid wearer at least essentially matches the masking threshold of the hearing aid wearer at the respective frequency.
  12. Hearing aid having a microphone system (1, 2, 3) with a variable directional characteristic for reception of an acoustic input signal and emission of a microphone output signal (RA), having a signal processing unit (11) and having an output transducer (12), wherein the directional characteristic of the microphone system (1, 2, 3) is adjusted as a function of the frequency of the microphone output signal (RA) and a masking threshold of the hearing aid wearer at the respective frequency such that the signal level of the microphone noise which is produced by the microphone system and is supplied to the hearing of the hearing aid wearer, differs at least essentially by an adjustable value from the masking threshold of the hearing aid wearer of the hearing aid wearer at the respective frequency.
  13. Programmer for programming a hearing aid according to Claim 9 or 10, having a memory device (22) for storage of data relating to the individual rest hearing threshold of a hearing aid wearer as a function of the frequency of a test signal which is supplied to the hearing of the hearing aid, and having a computation device (23) for calculation of parameters for adjustment of the directional characteristic of the microphone system of the hearing aid as a function of this data.
  14. Programmer for programming a hearing aid according to Claim 11 or 12 having a memory device (32, 43) for storage of data relating to the masking threshold of a hearing aid wearer as a function of the frequency and of the signal level of a test signal which is supplied to the hearing of the hearing aid, and having a computation device (33, 44) for calculation of parameters for adjustment of the directional characteristic of the microphone system of the hearing aid as a function of this data.
EP04013290A 2003-06-20 2004-06-04 Method for operating a hearing aid system as well as a hearing aid system with a microphone system in which different directional characteristics are selectable Expired - Lifetime EP1489885B1 (en)

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