EP2180726B2 - Sound localization in binaural hearing aids - Google Patents
Sound localization in binaural hearing aids Download PDFInfo
- Publication number
- EP2180726B2 EP2180726B2 EP10000610.5A EP10000610A EP2180726B2 EP 2180726 B2 EP2180726 B2 EP 2180726B2 EP 10000610 A EP10000610 A EP 10000610A EP 2180726 B2 EP2180726 B2 EP 2180726B2
- Authority
- EP
- European Patent Office
- Prior art keywords
- signal
- hearing aid
- gain
- hearing
- ascertained
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 230000004807 localization Effects 0.000 title 1
- 238000012545 processing Methods 0.000 claims description 56
- 230000008859 change Effects 0.000 claims description 37
- 238000000034 method Methods 0.000 claims description 23
- 230000005540 biological transmission Effects 0.000 claims description 13
- 230000006870 function Effects 0.000 claims description 9
- 238000012360 testing method Methods 0.000 claims description 6
- 230000008054 signal transmission Effects 0.000 claims description 4
- 230000000737 periodic effect Effects 0.000 claims description 3
- 238000004458 analytical method Methods 0.000 description 19
- 210000005069 ears Anatomy 0.000 description 16
- 230000003321 amplification Effects 0.000 description 11
- 238000003199 nucleic acid amplification method Methods 0.000 description 11
- 238000005259 measurement Methods 0.000 description 10
- 230000006978 adaptation Effects 0.000 description 7
- 230000005236 sound signal Effects 0.000 description 7
- 206010011878 Deafness Diseases 0.000 description 6
- 230000006399 behavior Effects 0.000 description 6
- 238000006243 chemical reaction Methods 0.000 description 6
- 230000010370 hearing loss Effects 0.000 description 6
- 231100000888 hearing loss Toxicity 0.000 description 6
- 208000016354 hearing loss disease Diseases 0.000 description 6
- 238000013459 approach Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 230000010355 oscillation Effects 0.000 description 3
- 238000012805 post-processing Methods 0.000 description 3
- 238000007781 pre-processing Methods 0.000 description 3
- 230000008569 process Effects 0.000 description 3
- 230000009467 reduction Effects 0.000 description 3
- MOVRNJGDXREIBM-UHFFFAOYSA-N aid-1 Chemical compound O=C1NC(=O)C(C)=CN1C1OC(COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C(NC(=O)C(C)=C2)=O)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C(NC(=O)C(C)=C2)=O)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C(NC(=O)C(C)=C2)=O)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)COP(O)(=O)OC2C(OC(C2)N2C3=C(C(NC(N)=N3)=O)N=C2)CO)C(O)C1 MOVRNJGDXREIBM-UHFFFAOYSA-N 0.000 description 2
- 238000010219 correlation analysis Methods 0.000 description 2
- 238000011156 evaluation Methods 0.000 description 2
- 230000010363 phase shift Effects 0.000 description 2
- 230000000717 retained effect Effects 0.000 description 2
- 230000001629 suppression Effects 0.000 description 2
- 238000012546 transfer Methods 0.000 description 2
- 230000003044 adaptive effect Effects 0.000 description 1
- 210000000481 breast Anatomy 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000005265 energy consumption Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 210000000653 nervous system Anatomy 0.000 description 1
- 239000013307 optical fiber Substances 0.000 description 1
- 230000004044 response Effects 0.000 description 1
Images
Classifications
-
- 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
- H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
- H04R25/552—Binaural
Definitions
- the invention relates to a hearing aid system and a method for setting a hearing aid system having at least one first and one second hearing aid device, each having at least one input transducer for receiving an acoustic input signal and conversion to an electrical signal, a signal processing unit for processing the electrical signal and an output transducer for conversion comprise the electrical signal in an output signal and between which a signal path for data transmission is provided.
- Directional hearing is the ability of a person to distinguish the direction in which a sound source is located. If a sound source is not in front of or behind the person, the finite propagation speed of the sound inevitably results in a difference in transit time between the two ears, and thus a time difference with which the ears perceive a sound wave coming from one direction. If a sound is e.g. from the perspective of the peson comes from the right, this reaches the right ear by a fraction of a second rather than the left ear. This time difference is much shorter than the person concerned can consciously recognize. The effect occurs through an automatic integration process in the acoustic nervous system.
- the former solution has the disadvantage that a further assembly is necessary and the hearing aid wearer now requires three instead of two devices, which means a significant limitation of wearing comfort, maintenance and handling.
- the second solution requires that all signal processing must be done by a single signal processing unit on a single page. While in the solution with a third device enough space is available to provide a correspondingly powerful signal processing and ensure their energy needs, the space is limited in a hearing aid located on the ear. Therefore, a master-slave solution with two differently designed hearing aids must necessarily have a lower computational capacity than would be available when using both hearing aids.
- Another approach to solving the above problem is to transmit the incoming sound signals on the hearing aids of both sides to the other device and to process both signals on each side. In this way, the acoustic signals received at both ears undergo the same steps of signal processing together and therefore automatically experience the same signal delay.
- This approach is for example from the WO 97/14268 as well as the WO 99/43185 out.
- the transmission of the microphone signals on both sides of a binaural hearing aid system to the other side and the simultaneous processing of both signals on both sides solves the problem of a transit time difference, but is subject to the same limitations as the master-slave approach.
- a method for operating a hearing aid system is known in which sound field characteristics are transmitted from one hearing aid to another. These can be signal levels.
- a hearing aid is known in which a signal transmission from one to the other hearing aid via optical fibers is made. In this case, control signals can be transmitted.
- the object of the present invention is to support the natural directional hearing in a hearing aid system for binaural care and to keep the additional computational effort required for this purpose low.
- a hearing aid system In a hearing aid system, directional hearing in the case of binaural hearing aid supply is improved by matching the signal propagation times of the hearing aid devices attached to the two ears. However, the signal propagation times are only one factor affecting directional hearing.
- an adaptation of the amplitude response of the two hearing aids is also carried out. Differences in the amplitudes of signals that occur from different directions are mainly caused by the shading effect of the head. The differences in the amplitudes are very small and can not be consciously perceived. Only by a very fine adjustment of the hearing aids of a hearing aid system, these minimum differences in amplitude, which are caused by different directions of incidence remain maintained. The exact amount of these differences is rather secondary.
- a gain or gain change of an electrical signal in at least one of the hearing aid devices is determined.
- the gain change may be e.g. be caused by the change of a parameter of the signal processing of the hearing aid.
- data for identifying the current amplification or for characterizing the gain change is transmitted from the hearing aid device to the other hearing aid device of the hearing aid system. Also in this hearing aid then the gain is adjusted accordingly. This may mean that the gain is changed by the same amount.
- the amplification in the second hearing aid device is changed such that the same loudness impression is produced again in the case of a sound signal arriving from the 0 degree direction (directly from the front) on both ears through the supply of the hearing aid devices. Deviating from the 0-degree direction sound signals are then perceived again with different loudness impression, so that the hearing aid wearer can perceive the direction from which the sound signal arrives.
- the value of a gain change in a hearing aid according to the invention may be permanently assigned to certain settings or functions of the hearing aid. For example, in a feedback suppression algorithm, there may always be a 10 dB reduction in gain. Data for identifying this gain change can then, as soon as the algorithm is actively switched, be transferred to the other hearing aid device of the hearing aid system, so that a corresponding gain reduction is also performed in this case. In many applications, however, there is no fixed association between certain functions of the hearing aid and related gain changes. The amplification or gain change is then first determined automatically in the hearing aid. For this purpose, signal amplitudes or signal levels of an electrical signal to points in the signal path of the hearing aid behind one another recorded and evaluated.
- a test signal is preferably fed into the signal path, which at least partially passes through the signal processing unit of the hearing aid.
- the amplification in both hearing aids is determined and related data transferred to the other hearing aid in the gain adjustment.
- filter media are preferably set.
- an adjustment of the amplification of the two hearing aids of a hearing aid system is always carried out even when the gain setting when at least one of the hearing aids a parameter and / or functional change.
- the gain adjustment can also be done at periodic intervals.
- the determination and adaptation of the amplification or of the amplitude transmission behavior in a hearing device system with multi-channel hearing aid devices can in each case only relate to specific frequency bands.
- the transmission behavior of signal amplitudes is also measured.
- a test signal can be fed into the signal path at one point and read out again at the following point.
- this measurement is also carried out for different signal frequencies. If a parameter or function change then takes place in at least one of the hearing aid devices, the transmission behavior with respect to the signal amplitudes can be measured again and differences in the transmission behavior can be ascertained. Data that are characteristic of the signal amplitudes are then transferred to the respective other hearing aid device of the hearing device system for adaptation to the changed transmission behavior.
- the invention applies equally to behind the ear portable (BTE), in the ear portable (ITE) or implantable hearing aid systems application.
- FIG. 1 shows a schematic representation of a hearing aid system with two hearing aids 1 and 1 '.
- the processing of the electrical signal to compensate for the hearing loss of a hearing aid wearer takes place in the signal processing units 3 or 3 '.
- the processed signal is finally converted back into a sound signal by an electric-acoustic output transducer (earphone) 4 or 4 'and fed to the ears of a hearing aid wearer.
- earphone electric-acoustic output transducer
- the adjustment of the hearing aid devices 1 and 1 'to the respective hearing situation takes place by actuation of a control element 7 or 7' on at least one of the hearing aid devices 1 or 1 '.
- signal propagation times of the signal processing units 3 and 3' for the respective hearing programs and taking into account the respective settings of the hearing aid devices 1 and 1 'to compensate for the individual hearing loss of a hearing aid wearer are determined. This can be done, for example, by transit time measurements during the adaptation of the hearing aid devices 1 and 1 '. If the signal propagation times for both hearing aid devices 1 and 1 'are known under the selected settings for the respective hearing programs, the hearing programs are assigned data for characterizing the signal propagation times and are likewise stored in the memory units 6 or 6'. These data can be both the signal propagation times as such and also the respective transit time differences between the individual hearing programs or the hearing aid devices 1 and 1 '.
- the hearing aid device 1 If, for example, the hearing aid device 1 is switched between two hearing programs, then not only the parameters of the new hearing program are read from the memory unit 6, but also the data assigned to the newly set hearing program for characterizing the signal delay time. The latter are then transmitted via a transmitting and receiving unit 8 to the hearing aid 1 '.
- the hearing aid device 1 ' receives in turn by means of the transmitting and receiving unit 8' sent by the hearing aid 1 Data and supplies them to the control unit 5 '. This in turn compares the transmitted data with the information stored in the memory unit 6 'regarding the running time of the currently set hearing program. For example, by controlling a delay means, which is designed in the exemplary embodiment as an all-pass filter 9 or 9 ', then any differences in transit time can be compensated.
- both hearing aid devices 1 and 1 'thus have the same signal propagation delay between the input transducer 2 and the output transducer 4 or the input transducer 2' and the output transducer 4 '.
- both hearing aid devices 1 and 1 'thus have the same signal propagation delay between the input transducer 2 and the output transducer 4 or the input transducer 2' and the output transducer 4 '.
- FIG. 2 Another hearing aid system shows FIG. 2 , Since in this case both hearing aids of the hearing aid system have the same equivalent circuit, is in FIG. 2 only one of the two, namely the hearing aid 11, shown. Also this includes as the hearing aids 1 and 1 'in the embodiment according to FIG. 1 a microphone 12 for receiving an acoustic signal and conversion into an electrical signal, a signal processing unit 13 for frequency-dependent processing of the electrical signal and a receiver 14 for converting the electrical signal into an acoustic output signal.
- the hearing aid device 11 further comprises an A / D converter 15 for converting the output signal of the microphone into a digital signal, and a D / A converter 16 for reconverting the digital signal into an analog signal before the signal output via the receiver 14.
- FIG. 2 a signal analysis of the digital electrical input signal in an analysis and control unit 17. Also, this is connected to a memory unit 18 in which different, the signal processing processing memory sets are stored.
- a complete set of parameters which is stored in the memory unit 18, it is provided in the hearing aid 11, even adaptively change only individual settings and parameters for adjusting the signal processing to the respective hearing situation.
- certain functions or algorithms can be switched on or off.
- an algorithm for speech enhancement can be set in the hearing aid device, or an algorithm for noise suppression can be activated when detected noises.
- the hearing aid device 11 has a transit time determination unit 19.
- the fed-in signal passes through the signal processing unit 13 and is tapped before the output via the handset 14 and fed to the transit time determination unit 19.
- the generated signal lies in a frequency range which is not audible acoustically by the hearing aid wearer.
- the transit time measurement is advantageously carried out whenever a parameter or functional change has occurred in the hearing aid device 11.
- the determined data relating to the signal transit time are finally transmitted via a transmitting and receiving unit 20 to the second hearing aid device (not shown) of the hearing aid system.
- the hearing aid device 11 also receives the instantaneous signal transit time by means of the transmitting and receiving unit 20 through the signal processing unit of the second hearing aid device.
- the analysis and control unit 17 is thus the information regarding the signal propagation times of both hearing aids of the hearing aid system.
- a signal delay is subsequently performed by the difference of the signal propagation times determined in both hearing aid devices.
- the hearing aid device 11 comprises a delay unit designed as a shift register 21.
- the number of delay clocks by the analysis and control unit 17 is adjustable.
- FIG. 3 Another hearing aid is in FIG. 3 shown.
- a hearing aid 22 shows a hearing aid according to FIG. 2 very similar construction.
- the hearing aid 22 has a clock generator 23 with adjustable clock frequency.
- the system clock of the hearing aid 22 is adjustable.
- the clock frequency is increased so far to compensate for the delay difference until the delay difference is compensated. Accordingly, the clock frequency of the hearing aid device 22 is reduced so far that the signal propagation times are equalized at a shorter signal propagation time determined for the hearing aid device 22.
- Gain values are determined and related data stored in the memory units 6 and 6 '. In a gain change in one of the two hearing aids as a result of a parameter and / or functional change (eg changing the hearing program) then the gain in the other hearing aid is adjusted accordingly.
- an amplitude compensation can be done.
- a test signal is advantageously fed via the measuring device 19 into the signal path and picked up again at a later point in the signal path, preferably after the signal processing unit 13.
- the signal transmission behavior with regard to the signal amplitudes is also measured so advantageously.
- the measurement is carried out at different frequencies.
- a different gain value can be determined for different frequencies.
- Data relating to the amplification values thus determined are then transmitted to the respective other hearing aid device of the hearing aid system. Subsequently, an adjustment of the signal amplitudes takes place, with at least one of the hearing aid devices changing the gain or setting filter means.
- the adjustment of the signal amplitudes follows, taking into account the audiograms measured in both ears. Data regarding these audiograms may also be stored in the storage units 18.
- the loudness compensation then takes place in relation to the audiograms, which ensures that, for example, a slight loudness change caused by a parameter change on a hearing aid device causes a loudness change subjectively the same for the hearing aid wearer on the other hearing aid.
- a slight loudness change caused by a parameter change on a hearing aid device causes a loudness change subjectively the same for the hearing aid wearer on the other hearing aid.
- slight loudness differences in the two ears of a hearing aid wearer are always perceived the same regardless of the current hearing aid settings.
- FIG. 4 shows only a hearing aid 24 of a hearing aid system with two identically constructed hearing aids.
- the hearing aid device 24 comprises two microphones 25 and 26 whose output signals are fed to a signal preprocessing unit 27.
- the signal pre-processing unit 27 an A / D conversion and an electrical connection of the microphone signals to produce a directional microphone characteristic.
- a filter bank 28 serves to split the electrical signal into frequency bands.
- signal processing units 29A, 29B, 29C and 29D a frequency band-specific signal processing of the electrical signals in the individual frequency bands then takes place.
- the output signals of the signal processing units 29A to 29D are added and post-processed in a signal post-processing unit 30.
- the signal post-processing may include, for example, an end gain and D / A conversion.
- the analog electrical output signal is converted back into an acoustic output signal by a receiver 31.
- the individual signal processing blocks of the hearing aid device that is to say the signal preprocessing unit 27, the filter bank 28, the signal processing units 29A to 29D in the individual channels, and the signal postprocessing unit 30, are collectively referred to as signal processing unit 29 in the exemplary embodiment.
- the hearing aid device 24 has a signal analysis and control unit 33, into which the electrical input signal before dividing into different frequency bands and the electrical output signal after passing through the signal processing units 29A to 29D.
- the signal analysis and control unit 33 for example, feedback-related oscillations in the electrical input signal can be detected.
- the gain may be reduced.
- Data relating to this gain change in the relevant channel are then acquired by the signal analysis and control unit 33 and transmitted by means of a transmitting and receiving unit 34 to the second hearing aid (not shown). This receives the transmitted data and in turn lowers the gain in the corresponding channel by means of a signal analysis and control unit of the hearing aid 24 corresponding signal analysis and control unit.
- data relating to a change in gain in the second hearing aid device of the hearing aid system can also be transmitted to the hearing aid device 24, which acts by means of the signal analysis and control unit 33 on components (for example the signal processing units 29A to 29D in the individual channels) and the gain in the hearing aid device 24 adapts accordingly.
- the gain change can be made in both hearing aids by the same amount. Preferably, however, it takes place taking into account the individual hearing loss of the hearing device wearer and the signal transmission characteristics of the hearing aid devices. The hearing aid wearer then subjectively perceives the same gain reduction on both hearing aids. Natural loudness differences in the acoustic input signals remain largely preserved for the hearing aid wearer.
- parameter or functional changes in hearing aids result as a result of the current hearing situation not to predetermined gain changes. This is the case, for example, with hearing aid devices in which complete sets of parameters for adaptation to different listening situations are not predetermined, but in which an adaptive and continuous adaptation of individual parameters takes place.
- a gain change is then advantageously determined by a hearing aid internal measurement.
- the gain change can be determined from measurements of the gain before and after a parameter change.
- the electrical input signal and the electrical output signal in the signal analysis and control unit 33 are evaluated.
- Both an evaluation of the total input or output signal and the electrical input and output signals of the signal processing units 29A to 29D of the individual channels is possible, depending on whether a change in the parameter affects the entire frequency range or only signal frequencies within a frequency band.
- Analogous to the adjustment of the amplification can in a hearing aid system with two hearing aids with a schematic block diagram according to the exemplary hearing aid device 24, as in FIG. 4 represented, the signal amplitudes or the signal propagation times of the two hearing aids are adapted to each other, so that the natural directional hearing is maintained even with worn hearing aids.
- only other signal analysis methods in the signal analysis and control unit 33 are provided for the amplitude or delay compensation over the gain compensation.
- the amplitude compensation is preceded by amplitude or level measurements or the delay compensation phase or signal propagation time measurements on the overall signal or in the individual channels of the hearing aid device 24.
- the compensation is then preferably carried out by adjustable filter means within the signal processing unit 29, which are set by the signal analysis and control unit 33.
- a correlation analysis is performed for the transit time measurement.
- the signal analysis and control unit 33 electrical signals from successive points in the signal path between the microphones 25 and 26 and the handset 31 are supplied.
- the phase shift and thus the signal propagation time can then be determined in a simple manner.
- the envelopes of the supplied signals are first determined in the signal analysis and control unit.
- the comparison of the envelopes in the signal analysis and evaluation unit 33 also makes it easy to deduce the phase shift of the relevant signals and thus the signal propagation time between the points of interest in the signal path of the hearing aid device 24.
- the measurements are carried out in each case shortly before and shortly after parameter or functional changes in the hearing aid device 24 in order to detect the resulting amplification and / or amplitude and / or signal propagation time changes in the hearing aid device 24, related data to the second hearing aid device of the hearing aid system transmit, receive there, evaluate and finally compensate for the changes.
- the invention proposes in each case to measure signal amplitudes and / or amplifications of an electrical signal in a signal path between an input transducer and an output transducer of a hearing aid device and to transmit data relating to the measured signal amplitudes and / or amplifications to the respective other hearing aid device.
- the signal amplitudes of the electrical signals can be matched to each other by the two hearing aids.
- no amplitude distortion is caused by the hearing aids and the natural amplitude difference of an incident from a particular direction sound signal is maintained.
- the direction information for the hearing aid wearer is retained.
Landscapes
- Engineering & Computer Science (AREA)
- Computer Networks & Wireless Communication (AREA)
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Physics & Mathematics (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Circuit For Audible Band Transducer (AREA)
Description
Die Erfindung betrifft ein Hörgerätesystem sowie ein Verfahren zum Einstellen eines Hörgerätesystems mit wenigstens einem ersten und einem zweiten Hörhilfegerät, die jeweils wenigstens einen Eingangswandler zur Aufnahme eines akustischen Eingangssignals und Wandlung in ein elektrisches Signal, eine Signalverarbeitungseinheit zur Verarbeitung des elektrischen Signals und einen Ausgangswandler zur Wandlung des elektrischen Signals in ein Ausgangssignal umfassen und zwischen denen ein Signalpfad zur Datenübertragung vorgesehen ist.The invention relates to a hearing aid system and a method for setting a hearing aid system having at least one first and one second hearing aid device, each having at least one input transducer for receiving an acoustic input signal and conversion to an electrical signal, a signal processing unit for processing the electrical signal and an output transducer for conversion comprise the electrical signal in an output signal and between which a signal path for data transmission is provided.
Unter dem Richtungshören versteht man die Fähigkeit einer Person zur Unterscheidung der Richtung, in welcher sich eine Schallquelle befindet. Wenn sich eine Schallquelle nicht frontal vor oder hinter der Person befindet, ergibt sich durch die endliche Ausbreitungsgeschwindigkeit des Schalls zwangsläufig ein Laufzeitunterschied zwischen den beiden Ohren und damit eine zeitliche Differenz, mit der die Ohren eine aus einer Richtung kommende Schallwelle wahrnehmen. Wenn ein Schall z.B. aus der Sicht der Peson von rechts kommt, erreicht dieser das rechte Ohr um einen Bruchteil einer Sekunde eher als das linke Ohr. Diese Zeitdifferenz ist weitaus kürzer als der Betreffende bewusst erkennen kann. Die Wirkung tritt durch einen automatischen Integrationsprozess im akustischen Nervensystem ein.Directional hearing is the ability of a person to distinguish the direction in which a sound source is located. If a sound source is not in front of or behind the person, the finite propagation speed of the sound inevitably results in a difference in transit time between the two ears, and thus a time difference with which the ears perceive a sound wave coming from one direction. If a sound is e.g. from the perspective of the peson comes from the right, this reaches the right ear by a fraction of a second rather than the left ear. This time difference is much shorter than the person concerned can consciously recognize. The effect occurs through an automatic integration process in the acoustic nervous system.
Neben der zeitlichen Differenz ergibt sich weiterhin auch ein Unterschied in der Lautstärke, mit der die Ohren einen Ton wahrnehmen, der von einer Seite kommt. Eine Schallquelle auf einer Seite des Kopfes übermittelt dem Ohr auf dieser Seite einen etwas lauteren Ton. Auch dieser minimale Unterschied in der Lautstärke reicht aus, damit die Schallquelle aus der Sicht der Person links oder rechts lokalisiert werden kann.In addition to the time difference, there is still a difference in the volume with which the ears perceive a sound coming from one side. A sound source on one side of the head gives the ear a slightly louder sound on that side. Also, this minimal difference in volume is sufficient so that the sound source from the perspective of the person can be located on the left or right.
Bei binauraler Hörgeräte-Versorgung tritt häufig ein Verlust des Richtungshörens auf. Dies ist vor allem dadurch begründet, dass je nach Hörsituation, die von dem jeweiligen Hörhilfegerät detektiert wird, die Signalverarbeitung der beiden Hörhilfegeräte unterschiedliche Schritte umfassen kann. Weiterhin ist bei einem Hörgeräteträger in der Regel der Hörverlust beider Ohren unterschiedlich stark ausgeprägt. Entsprechend sind auch die Einstellungen der Hörgeräte zum Ausgleich des Hörverlustes des jeweiligen Ohres unterschiedlich eingestellt. Unterschiedliche Einstellungen der Signalverarbeitung beider Hörgeräte haben jedoch zumeist unterschiedliche Signallaufzeiten innerhalb der Hörhilfegeräte zur Folge. Es kommt daher zu einer unnatürlichen Verschiebung der für das Richtungshören wichtigen Phase eines akustischen Eingangssignals. Wie eingangs bereits erwähnt, ist die Laufzeit eines Schallsignals zwischen den beiden Ohren neben dem Unterschied in der Lautstärke für das Richtungshören von großer Bedeutung. Bereits geringfügige Veränderungen dieser natürlichen Laufzeitverschiebung, wie sie beispielsweise von unterschiedlichen Signallaufzeiten innerhalb der Hörhilfegeräte verursacht werden, können daher zu einem Verlust des Richtungshörens führen.In binaural hearing aid care, loss of directional hearing often occurs. This is mainly due to the fact that depending on the hearing situation, which is detected by the respective hearing aid, the signal processing of the two hearing aids may include different steps. Furthermore, in a hearing aid wearer usually the hearing loss of both ears is pronounced to different degrees. Accordingly, the settings of the hearing aids to compensate for the hearing loss of each ear are set differently. However, different settings of the signal processing of both hearing aids usually result in different signal propagation times within the hearing aid devices. There is therefore an unnatural shift in the important for directional listening phase of an acoustic input signal. As already mentioned, the transit time of a sound signal between the two ears in addition to the difference in the volume for the directional hearing of great importance. Even slight changes in this natural transit time shift, as caused for example by different signal propagation times within the hearing aid devices, can therefore lead to a loss of directional hearing.
Zur Lösung dieses Problems ist bekannt, die an den beiden Ohren aufgenommenen akustischen Signale in einer gemeinsamen zentralen Signalverarbeitungseinrichtung zu verarbeiten. So sieht die
Aus der
Die erstgenannte Lösung hat den Nachteil, dass eine weitere Baugruppe notwendig wird und der Hörgeräteträger nun drei statt zwei Geräte benötigt, was eine erhebliche Einschränkung des Tragekomforts, der Wartung und der Handhabung bedeutet. Die zweite Lösung bedingt, dass die gesamte Signalverarbeitung von einer einzigen Signalverarbeitungseinheit auf nur einer Seite geleistet werden muss. Während bei der Lösung mit einem dritten Gerät genügend Platz vorhanden ist, um eine entsprechend leistungsfähige Signalverarbeitung vorzusehen und deren Energiebedarf sicherzustellen, ist der Platz in einer am Ohr befindlichen Hörhilfe begrenzt. Daher muss eine Master-Slave-Lösung mit zwei unterschiedlich ausgebildeten Hörhilfegeräten notgedrungen eine geringere rechnerische Kapazität besitzen als bei der Ausnutzung beider Hörhilfegeräte zur Verfügung stünde.The former solution has the disadvantage that a further assembly is necessary and the hearing aid wearer now requires three instead of two devices, which means a significant limitation of wearing comfort, maintenance and handling. The second solution requires that all signal processing must be done by a single signal processing unit on a single page. While in the solution with a third device enough space is available to provide a correspondingly powerful signal processing and ensure their energy needs, the space is limited in a hearing aid located on the ear. Therefore, a master-slave solution with two differently designed hearing aids must necessarily have a lower computational capacity than would be available when using both hearing aids.
Ein weiterer Ansatz zur Lösung des genannten Problems besteht darin, die eingehenden Schallsignale an den Hörhilfegeräten beider Seiten zu dem jeweils anderen Gerät zu übertragen und auf jeder Seite beide Signale zu verarbeiten. Auf diese Weise durchlaufen die an beiden Ohren aufgenommenen akustischen Signale gemeinsam die gleichen Schritte der Signalverarbeitung und erfahren daher automatisch die gleiche Signalverzögerung. Dieser Lösungsansatz geht beispielsweise aus der
Ein weiterer wesentlicher Nachteil aller genannter Lösungen liegt in der Tatsache, dass sie alle die Übermittlung großer Datenmengen erfordern. Dies bedingt einen erheblichen Zeit-, Platz- und Energieverbrauch. Insbesondere bei dṙahtlosem Datentransfer, wie er beim gegenwärtigen Stand der Technik geboten ist, stellt dies einen erheblichen Nachteil dar.Another major disadvantage of all mentioned solutions lies in the fact that they all require the transmission of large amounts of data. This requires a considerable amount of time, space and energy consumption. Especially in the case of seamless data transfer, such as he is offered in the current state of the art, this represents a significant disadvantage.
Aus der
Aus der
Aus der
Aufgabe der vorliegenden Erfindung ist es, bei einem Hörgerätesystem zur binauralen Versorgung das natürliche Richtungshören zu unterstützen und den hierfür erforderlichen zusätzlichen Rechenaufwand gering zu halten.The object of the present invention is to support the natural directional hearing in a hearing aid system for binaural care and to keep the additional computational effort required for this purpose low.
Diese Aufgabe wird gelöst durch Verfahren mit den Verfahrensschritten gemäß den Ansprüchen 1 oder 10.This object is achieved by methods with the method steps according to
Ferner wird die Aufgabe durch ein Hörgerätesystem mit den Merkmalen gemäß den Ansprüchen 17 oder 19 gelöst.Furthermore, the object is achieved by a hearing aid system having the features according to
Bei einem aus dem eingangs zitierten Stand der Technik bekannten Hörgerätesystem mit zwei Hörgeräten wird eine gleiche Signallaufzeit in den Signalpfaden beider Hörgeräte zwischen jeweils dem Mikrofon und dem Hörer erzeugt, ohne diese Signallaufzeit explizit zu kennen. Nachteilig sind der hohe Rechenaufwand und die hohen erforderlichen Datenübertragungsraten.In a known from the cited prior art hearing aid system with two hearing aids a same signal propagation time in the signal paths of both hearing aids between each of the microphone and the listener is generated, without knowing this signal propagation time explicitly. Disadvantages are the high computational effort and the high data transfer rates required.
Bei einem Hörgerätesystem wird das Richtungshören bei binauraler Hörgeräteversorgung dadurch verbessert, dass die Signallaufzeiten der an den beiden Ohren angebrachten Hörhilfegeräte angeglichen werden. Die Signallaufzeiten sind jedoch nur ein Faktor, der das Richtungshören betrifft. Bei einem Hörgerätesystem gemäß der Erfindung erfolgt auch eine Anpassung des Amplitudenganges der beiden Hörhilfegeräte. Unterschiede in den Amplituden von Signalen, die aus unterschiedlichen Richtungen einfallen, werden vor allem durch die Abschattungswirkung des Kopfes hervorgerufen. Dabei sind die Unterschiede in den Amplituden sehr gering und können nicht bewusst wahrgenommen werden. Nur durch eine sehr feine Anpassung der Hörhilfegeräte eines Hörgerätesystems können diese minimalen Amplitudenunterschiede, die durch unterschiedliche Einfallsrichtungen hervorgerufen werden, aufrechterhalten bleiben. Dabei ist die exakte Höhe dieser Unterschiede eher zweitrangig. Wichtig ist vor allem, dass eine Amplitudendifferenz bei einem Signal aus einer bestimmten Richtung weitgehend erhalten bleibt, auch wenn sich bei einem oder bei beiden Hörhilfegeräten Einstellungen ändern. Wird z.B. bei einem Hörhilfegerät die Lautstärke erhöht, so sollte auch bei dem anderen Hörhilfegerät eine Anpassung der Lautstärke erfolgen. Da jedoch häufig nicht beide Ohren eines Hörgeräteträgers gleichermaßen von einem Hörverlust betroffen sind, kann die Lautstärkenanpassung in der Regel nicht bei beiden Hörhilfegeräten gleichermaßen erfolgen. Vielmehr hat die Anpassung unter Berücksichtigung der individuellen Hörkurven, die an den beiden Ohren eines Hörgeräteträgers gemessen wurden, zu erfolgen. Entscheidend ist also, dass einem Hörgeräteträger bei einem Signal, das aus einer bestimmten Richtung kommt, an dem Ohr mit der kürzeren Entfernung zu der Signalquelle stets eine etwas höhere Lautstärke vermittelt wird.In a hearing aid system, directional hearing in the case of binaural hearing aid supply is improved by matching the signal propagation times of the hearing aid devices attached to the two ears. However, the signal propagation times are only one factor affecting directional hearing. In a hearing aid system according to the invention, an adaptation of the amplitude response of the two hearing aids is also carried out. Differences in the amplitudes of signals that occur from different directions are mainly caused by the shading effect of the head. The differences in the amplitudes are very small and can not be consciously perceived. Only by a very fine adjustment of the hearing aids of a hearing aid system, these minimum differences in amplitude, which are caused by different directions of incidence remain maintained. The exact amount of these differences is rather secondary. It is important above all that an amplitude difference in a signal from a certain direction is largely retained, even if change in one or both hearing aids settings. If e.g. If the volume increases in a hearing aid, then the volume should also be adjusted in the case of the other hearing aid. However, since often both ears of a hearing aid wearer are equally affected by hearing loss, the volume adjustment usually can not be done equally in both hearing aids. Rather, the adjustment has to be done taking into account the individual hearing curves that were measured on the two ears of a hearing aid wearer. So it is crucial that a hearing aid wearer is always given a slightly higher volume at the ear with the shorter distance to the signal source at a signal that comes from a certain direction.
Bei einer Ausführungsform der Erfindung wird bei einem Hörgerätesystem mit zwei am Kopf tragbaren Hörhilfegeräten eine Verstärkung bzw. Verstärkungsänderung eines elektrischen Signals in wenigstens einem der Hörhilfegeräte ermittelt. Die Verstärkungsänderung kann z.B. durch die Änderung eines Parameters der Signalverarbeitung des Hörhilfegerätes hervorgerufen worden sein. Dann werden Daten zur Kennzeichnung der aktuellen Verstärkung bzw. zur Kennzeichnung der Verstärkungsänderung von dem Hörhilfegerät auf das andere Hörhilfegerät des Hörgerätesystems übertragen. Auch in diesem Hörhilfegerät wird dann die Verstärkung entsprechend angepasst. Dies kann bedeuten, dass die Verstärkung um den gleichen Betrag geändert wird. Vorzugsweise wird die Verstärkung bei dem zweiten Hörhilfegerät jedoch so geändert, dass bei einem aus der 0-Gradrichtung (direkt von vorne) eintreffenden Schallsignal an beiden Ohren durch die Versorgung mit den Hörhilfegeräten wieder der gleiche Lautheitseindruck entsteht. Von der 0-Gradrichtung abweichende Schallsignale werden dann wieder mit unterschiedlichem Lautheitseindruck wahrgenommen, so dass der Hörgeräteträger die Richtung, aus dem das Schallsignal eintrifft, wahrnehmen kann.In one embodiment of the invention, in a hearing aid system having two hearing aid devices that can be worn on the head, a gain or gain change of an electrical signal in at least one of the hearing aid devices is determined. The gain change may be e.g. be caused by the change of a parameter of the signal processing of the hearing aid. Then, data for identifying the current amplification or for characterizing the gain change is transmitted from the hearing aid device to the other hearing aid device of the hearing aid system. Also in this hearing aid then the gain is adjusted accordingly. This may mean that the gain is changed by the same amount. Preferably, however, the amplification in the second hearing aid device is changed such that the same loudness impression is produced again in the case of a sound signal arriving from the 0 degree direction (directly from the front) on both ears through the supply of the hearing aid devices. Deviating from the 0-degree direction sound signals are then perceived again with different loudness impression, so that the hearing aid wearer can perceive the direction from which the sound signal arrives.
Der Wert einer Verstärkungsänderung bei einem Hörhilfegerät gemäß der Erfindung kann bestimmten Einstellungen oder Funktionen des Hörhilfegerätes fest zugeordnet sein. So kann beispielsweise bei einem Algorithmus zur Rückkopplungsunterdrückung stets eine Verringerung der Verstärkung um 10 dB vorgesehen sein. Daten zur Kennzeichnung dieser Verstärkungsänderung können dann, sobald der Algorithmus aktiv geschaltet wird, auf das andere Hörhilfegerät des Hörgerätesystems übertragen werden, damit auch bei diesem eine entsprechende Verstärkungsabsenkung durchgeführt wird. In vielen Anwendungsfällen steht jedoch keine feste Zuordnung zwischen bestimmten Funktionen des Hörhilfegerätes und damit verbundenen Verstärkungsänderungen. Die Verstärkung bzw. Verstärkungsänderung wird dann zunächst automatisch im Hörhilfegerät ermittelt. Hierzu können Signalamplituden oder Signalpegel eines elektrischen Signals an im Signalpfad des Hörhilfegerätes hintereinander liegenden Punkten erfasst und ausgewertet werden. Auch hierfür wird vorzugsweise ein Testsignal in den Signalpfad eingespeist, das die Signalverarbeitungseinheit des Hörhilfegerätes zumindest teilweise durchläuft. Vorzugweise wird auch bei der Verstärkungsanpassung die Verstärkung in beiden Hörhilfegeräten ermittelt und diesbezügliche Daten auf das jeweils andere Hörhilfegerät übertragen. Zur Anpassung der Verstärkung in einem Hörhilfegerät an eine Verstärkungsänderung bei einem zweiten Hörhilfegerät eines Hörgerätesystems werden vorzugsweise Filtermittel eingestellt. Vorzugsweise wird auch bei der Verstärkungseinstellung immer dann, wenn sich bei wenigstens einem der Hörhilfegeräte eine Parameter- und/oder Funktionsänderung ergibt, eine Anpassung der Verstärkung der beiden Hörhilfegeräte eines Hörgerätesystems durchgeführt. Auch die Verstärkungsanpassung kann jedoch in periodischen Zeitabständen erfolgen. Ebenso wie die Ermittlung und Anpassung der Signallaufzeit kann auch die Ermittlung und Anpassung der Verstärkung bzw. des Amplitudenübertragungsverhaltens bei einem Hörgerätesystem mit Mehrkanal-Hörhilfegeräten jeweils nur auf bestimmte Frequenzbänder bezogen sein.The value of a gain change in a hearing aid according to the invention may be permanently assigned to certain settings or functions of the hearing aid. For example, in a feedback suppression algorithm, there may always be a 10 dB reduction in gain. Data for identifying this gain change can then, as soon as the algorithm is actively switched, be transferred to the other hearing aid device of the hearing aid system, so that a corresponding gain reduction is also performed in this case. In many applications, however, there is no fixed association between certain functions of the hearing aid and related gain changes. The amplification or gain change is then first determined automatically in the hearing aid. For this purpose, signal amplitudes or signal levels of an electrical signal to points in the signal path of the hearing aid behind one another recorded and evaluated. For this, too, a test signal is preferably fed into the signal path, which at least partially passes through the signal processing unit of the hearing aid. Preferably, the amplification in both hearing aids is determined and related data transferred to the other hearing aid in the gain adjustment. To adapt the gain in a hearing aid to a gain change in a second hearing aid of a hearing aid system filter media are preferably set. Preferably, an adjustment of the amplification of the two hearing aids of a hearing aid system is always carried out even when the gain setting when at least one of the hearing aids a parameter and / or functional change. However, the gain adjustment can also be done at periodic intervals. As well as the determination and adaptation of the signal propagation time, the determination and adaptation of the amplification or of the amplitude transmission behavior in a hearing device system with multi-channel hearing aid devices can in each case only relate to specific frequency bands.
Bei einer vorteilhaften Ausführungsform der Erfindung wird neben der Ermittlung von Signallaufzeiten bei den Hörhilfegeräten eines Hörgerätesystems auch das Übertragungsverhalten von Signalamplituden gemessen. Auch hierbei kann ein Testsignal an einer Stelle in den Signalpfad eingespeist und an nachfolgender Stelle wieder ausgelesen werden. Vorzugsweise erfolgt auch diese Messung für unterschiedliche Signalfrequenzen. Erfolgt anschließend eine Parameter- oder Funktionsänderung bei wenigstens einem der Hörhilfegeräte, so können das Übertragungsverhalten bezüglich der Signalamplituden erneut gemessen und Unterschiede im Übertragungsverhalten festgestellt werden. Für die Signalamplituden charakteristische Daten werden dann auf das jeweils andere Hörhilfegerät des Hörgerätesystems übertragen zur Anpassung an das geänderte Übertragungsverhalten.In an advantageous embodiment of the invention, in addition to the determination of signal propagation times in the hearing aid devices of a hearing aid system, the transmission behavior of signal amplitudes is also measured. Here, too, a test signal can be fed into the signal path at one point and read out again at the following point. Preferably, this measurement is also carried out for different signal frequencies. If a parameter or function change then takes place in at least one of the hearing aid devices, the transmission behavior with respect to the signal amplitudes can be measured again and differences in the transmission behavior can be ascertained. Data that are characteristic of the signal amplitudes are then transferred to the respective other hearing aid device of the hearing device system for adaptation to the changed transmission behavior.
Die Erfindung findet gleichermaßen bei hinter dem Ohr tragbaren (HdO), in dem Ohr tragbaren (IdO) oder implantierbaren Hörgerätesystemen Anwendung.The invention applies equally to behind the ear portable (BTE), in the ear portable (ITE) or implantable hearing aid systems application.
Weitere Einzelheiten der Erfindung werden nachfolgend anhand von Ausführungsbeispielen näher erläutert. Es zeigen:
-
ein Hörgerätesystem mit zwei Hörhilfegeräten, zwischen denen ein Signalpfad vorgesehen ist und bei denen unterschiedliche Hörprogramme einstellbar sind,Figur 1 -
ein Hörhilfegerät mit einer Signallaufzeit-Messeinrichtung und einem einstellbaren Verzögerungselement,Figur 2 -
ein Hörhilfegerät mit einem Signallaufzeit- und Amplituden- Messelement und einstellbarer Taktfrequenz undFigur 3 -
ein Hörhilfegerät, bei dem die Signalverarbeitung parallel in mehreren Frequenzkanälen erfolgt, mit einer Signalanalyse- und Steuereinheit.Figur 4
-
FIG. 1 a hearing aid system with two hearing aids, between which a signal path is provided and in which different hearing programs can be set, -
FIG. 2 a hearing aid device with a signal transit time measuring device and an adjustable delay element, -
FIG. 3 a hearing aid with a signal delay and amplitude measuring element and adjustable clock frequency and -
FIG. 4 a hearing aid, in which the signal processing takes place in parallel in several frequency channels, with a signal analysis and control unit.
Zur Anpassung an unterschiedliche Hörsituationen, wie beispielsweise "Sprache in ruhiger Umgebung", "Sprache mit Störgeräusch", "Fahrt im Auto" usw., umfassen die Hörhilfegeräte 1 und 1' je eine Steuereinheit 5 bzw. 5'. Die Steuereinheiten 5 und 5' sind mit Speichereinheiten 6 bzw. 6' verbunden, in denen unterschiedliche Parametersätze zur Anpassung der Signalverarbeitungseinheiten 3 bzw. 3' an unterschiedliche Hörsituationen gespeichert sind.To adapt to different listening situations, such as "speech in a quiet environment", "speech with noise", "driving in the car", etc., the
Die Einstellung der Hörhilfegeräte 1 und 1' an die jeweilige Hörsituation erfolgt durch Betätigung eines Bedienelementes 7 bzw. 7' an wenigstens einem der Hörhilfegeräte 1 bzw. 1'.The adjustment of the
Bei den Hörhilfegeräten 1 und 1' werden Signallaufzeiten der Signalverarbeitungseinheiten 3 bzw. 3' für die jeweiligen Hörprogramme und unter Berücksichtigung der jeweiligen Einstellungen der Hörhilfegeräte 1 und 1' zum Ausgleich des individuellen Hörverlustes eines Hörgeräteträgers ermittelt. Dies kann beispielsweise durch Laufzeitmessungen während der Anpassung der Hörhilfegeräte 1 und 1' erfolgen. Sind die Signallaufzeiten für beide Hörhilfegeräte 1 und 1' unter den gewählten Einstellungen für die jeweiligen Hörprogramme bekannt, so werden den Hörprogrammen Daten zur Kennzeichnung der Signallaufzeiten zugeordnet und ebenfalls in den Speichereinheiten 6 bzw. 6' abgelegt. Bei diesen Daten kann es sich sowohl um die Signallaufzeiten als solche als auch um die jeweiligen Laufzeitunterschiede zwischen den einzelnen Hörprogrammen oder den Hörhilfegeräten 1 und 1' handeln. Wird nun z.B. bei dem Hörhilfegerät 1 zwischen zwei Hörprogrammen umgeschaltet, so werden aus der Speichereinheit 6 nicht nur die Parameter des neuen Hörprogrammes ausgelesen, sondern auch die dem neu eingestellten Hörprogramm zugeordneten Daten zur Kennzeichnung der Signallaufzeit. Letztere werden dann über eine Sende- und Empfangseinheit 8 an das Hörhilfegerät 1' übertragen. Das Hörhilfegerät 1' empfängt seinerseits mittels der Sende- und Empfangseinheit 8' die von dem Hörhilfegerät 1 gesendeten Daten und führt sie der Steuereinheit 5' zu. Diese wiederum vergleicht die übertragenen Daten mit der in der Speichereinheit 6' gespeicherten Information bezüglich der Laufzeit des aktuell eingestellten Hörprogramms. Beispielsweise durch Steuerung eines Verzögerungsmittels, das im Ausführungsbeispiel als Allpassfilter 9 bzw. 9' ausgeführt ist, lassen sich dann etwaige Laufzeitunterschiede ausgleichen. Vorteilhaft weisen somit beide Hörhilfegeräte 1 bzw. 1' die gleiche Signallaufzeit zwischen dem Eingangswandler 2 und dem Ausgangswandler 4 bzw. dem Eingangswandler 2' und dem Ausgangswandler 4' auf. So wird mit dem Hörgerätesystem 1, 1' stets das Richtungshören ermöglicht, unabhängig von der gerade aktiven Programmpaarung der Hörprogramme beider Hörhilfegeräte 1 und 1'.In the
Eine anderes Hörgerätesystem zeigt
Im Unterschied zu
Ein weiteres Hörhilfegerät ist in
Bei einer bevorzugten Ausführungsform der Erfindung erfolgt neben dem Ausgleich der Signallaufzeiten bei geänderten Einstellungen und Funktionen wenigstens eines Hörhilfegerätes auch ein Amplitudenausgleich. Hierzu können z.B. analog zum Ausgleich der Signallaufzeiten bei den Hörhilfegeräten 1 und 1' gemäß
Auch bei den beispielhaft in den
Ein weiteres Ausführungsbeispiel der Erfindung ist in
Auch bei dem Hörhilfegerät 24 in diesem Ausführungsbeispiel sind unterschiedliche Hörprogramme zur Anpassung der Signalverarbeitung im Hörhilfegerät an unterschiedliche Hörsituationen vorgesehen. Entsprechende Parametersätze sind in einer Speichereinheit 32 hinterlegt. Zum Erkennen der augenblicklichen Hörsituation weist das Hörhilfegerät 24 eine Signalanalyse- und Steuereinheit 33 auf, in die das elektrische Eingangssignal vor der Aufteilung in unterschiedliche Frequenzbänder sowie das elektrische Ausgangssignal nach Durchlauf der Signalverarbeitungseinheiten 29A bis 29D eingehen. Mittels der Signalanalyse- und Steuereinheit 33 können beispielsweise rückkopplungsbedingte Oszillationen in dem elektrischen Eingangssignal erkannt werden. Als Gegenmaßnahme gegen erkannte rückkopplungsbedingte Oszillationen kann dann in einem Frequenzband, in dem die Oszillationsfrequenz liegt, beispielsweise die Verstärkung herabgesetzt werden. Daten bezüglich dieser Verstärkungsänderung in dem betreffenden Kanal werden dann von der Signalanalyse- und Steuereinheit 33 erfasst und mittels einer Sende- und Empfangseinheit 34 auf das zweite Hörhilfegerät (nicht dargestellt) übertragen. Dieses empfängt die übertragenen Daten und senkt seinerseits die Verstärkung in dem entsprechenden Kanal mittels einer der Signalanalyse- und Steuereinheit des Hörhilfegerätes 24 entsprechenden Signalanalyse- und Steuereinheit. Ebenso können auch Daten bezüglich einer Verstärkungsänderung in dem zweiten Hörhilfegerät des Hörgerätesystems auf das Hörhilfegerät 24 übertragen werden, das mittels der Signalanalyse- und Steuereinheit 33 auf Komponenten (beispielsweise die Signalverarbeitungseinheiten 29A bis 29D in den einzelnen Kanälen) steuernd einwirkt und die Verstärkung bei dem Hörhilfegerät 24 entsprechend anpasst.Also in the
Die Verstärkungsänderung kann in beiden Hörhilfegeräten um den gleichen Betrag erfolgen. Vorzugsweise erfolgt sie jedoch unter Berücksichtigung des individuellen Hörverlustes des Hörgeräteträgers sowie der Signalübertragungskennlinien der Hörhilfegeräte. Der Hörgeräteträger nimmt dann subjektiv die gleiche Verstärkungsreduzierung an beiden Hörhilfegeräten wahr. Natürliche Lautheitsunterschiede in den akustischen Eingangssignalen bleiben dadurch für den Hörgeräteträger weitgehend erhalten.The gain change can be made in both hearing aids by the same amount. Preferably, however, it takes place taking into account the individual hearing loss of the hearing device wearer and the signal transmission characteristics of the hearing aid devices. The hearing aid wearer then subjectively perceives the same gain reduction on both hearing aids. Natural loudness differences in the acoustic input signals remain largely preserved for the hearing aid wearer.
Häufig führen Parameter- oder Funktionsänderungen bei Hörhilfegeräten infolge der aktuellen Hörsituation nicht zu vorbestimmten Verstärkungsänderungen. Dies ist beispielsweise bei Hörhilfegeräten der Fall, bei denen nicht komplette Parametersätze zur Anpassung an unterschiedliche Hörsituationen vorgegeben sind, sondern bei denen eine adaptive und kontinuierliche Anpassung einzelner Parameter erfolgt. Eine Verstärkungsänderung wird dann vorteilhaft durch eine Hörhilfegeräte interne Messung ermittelt. So kann bei dem Hörhilfegerät gemäß
Analog zu der Anpassung der Verstärkung können bei einem Hörgerätesystem mit zwei Hörhilfegeräten mit einem schematischen Blockschaltbild gemäß dem beispielhaften Hörhilfegerät 24, wie in
Bei einer bevorzugten Variante wird zur Laufzeitmessung eine Korrelationsanalyse durchgeführt. Hierzu sind der Signalanalyse- und Steuereinheit 33 elektrische Signale aus hintereinanderliegenden Punkten in dem Signalpfad zwischen den Mikrofonen 25 und 26 und dem Hörer 31 zugeführt. Mittels der Korrelationsanalyse kann dann die Phasenverschiebung und damit die Signallaufzeit auf einfache Weise ermittelt werden.In a preferred variant, a correlation analysis is performed for the transit time measurement. For this purpose, the signal analysis and
Bei einer weiteren bevorzugten Variante werden in der Signalanalyse- und Steuereinheit zunächst die Einhüllenden der zugeführten Signale ermittelt. Auch aus dem Vergleich der Einhüllenden in der Signalanalyse- und Auswerteeinheit 33 kann leicht auf die Phasenverschiebung der betreffenden Signale und damit auf die Signallaufzeit zwischen den betrachteten Punkten in dem Signalpfad des Hörhilfegerätes 24 rückgeschlossen werden.In a further preferred variant, the envelopes of the supplied signals are first determined in the signal analysis and control unit. The comparison of the envelopes in the signal analysis and
Die Messungen erfolgen insbesondere jeweils kurz vor sowie kurz nach Parameter- oder Funktionsänderungen in dem Hörhilfegerät 24, um die dadurch bedingten Verstärkungs- und/oder Amplituden- und/oder Signallaufzeitänderungen bei dem Hörhilfegerät 24 zu erfassen, diesbezügliche Daten auf das zweite Hörhilfegerät des Hörgerätesystems zu übertragen, dort zu empfangen, auszuwerten und schließlich die Änderungen auszugleichen.The measurements are carried out in each case shortly before and shortly after parameter or functional changes in the
Zusammenfassend wird festgehalten:
Bei der binauralen Versorgung eines Hörgeräteträgers mit zwei am Ohren tragbaren Hörhilfegeräten soll das Richtungshören verbessert werden. Hierzu schlägt die Erfindung vor, jeweils Signalamplituden und/oder Verstärkungen eines elektrischen Signals in einem Signalpfad zwischen einem Eingangswandler und einem Ausgangswandler eines Hörhilfegerätes zu messen und Daten bezüglich der gemessenen Signalamplituden und/oder Verstärkungen auf das jeweils andere Hörhilfegerät zu übertragen. Dadurch können die Signalamplituden der elektrischen Signale durch die beiden Hörhilfegeräte aneinander angepasst werden. Damit wird durch die Hörhilfegeräte keine Amplitudenverzerrung verursacht und der natürliche Amplitudenunterschied eines aus einer bestimmten Richtung einfallenden Schallsignals bleiben erhalten. Somit bleibt auch die Richtungsinformation für den Hörgeräteträger erhalten.In summary, it is stated:
In the binaural care of a hearing aid wearer with two hearing aids that can be worn on the ear, directional hearing should be improved. For this purpose, the invention proposes in each case to measure signal amplitudes and / or amplifications of an electrical signal in a signal path between an input transducer and an output transducer of a hearing aid device and to transmit data relating to the measured signal amplitudes and / or amplifications to the respective other hearing aid device. As a result, the signal amplitudes of the electrical signals can be matched to each other by the two hearing aids. Thus, no amplitude distortion is caused by the hearing aids and the natural amplitude difference of an incident from a particular direction sound signal is maintained. Thus, the direction information for the hearing aid wearer is retained.
Claims (22)
- Method for the adjustment of a hearing aid system having at least one first (1, 11, 22, 24) and a second (1') hearing aid which each comprise at least one input transducer (2, 2' , 12, 25, 26) for picking up an audible input signal and converting it into an electrical signal, a signal processing unit (3, 3', 13, 29) for processing the electrical signal, and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal, and between which a signal path (10) is provided for the purpose of data transmission, a gain or gain change of the electrical signal being ascertained in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) and a signal being transmitted via the signal path (10) to the second hearing aid (1') for the purpose of matching the gain of the electrical signal in the signal path between the input transducer (2') and the output transducer (4') of the second hearing aid (1') to the ascertained gain of the electrical signal in the first hearing aid (1, 11, 22, 24) characterized in that the gain or gain change is ascertained by ascertaining signal amplitudes and/or signal levels of the electrical signal.
- Method according to Claim 1, characterized in that the gain or gain change of the electrical signal is ascertained for a subregion of the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24).
- Method according to Claim 1 or 2, characterized in that the gain or gain change of the electrical signal is automatically ascertained in the first hearing aid (1, 11, 22, 24) and a signal is transmitted to the second hearing aid (1').
- Method according to one of Claims 1 to 3,
characterized in that the gain or gain change is ascertained by producing a test signal which at least partially transits the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24). - Method according to one of Claims 1 to 4,
characterized in that the gain or gain change is ascertained in the first (1, 11, 22, 24) and the second (1') hearing aid and a respective signal is transmitted to the other hearing aid. - Method according to one of Claims 1 to 5,
characterized in that the gain is matched by adjusting filter means (9, 9'). - Method according to one of Claims 1 to 6,
characterized in that the gain or gain change is ascertained and matched at periodic intervals. - Method according to one of Claims 1 to 7,
characterized in that the gain is ascertained and matched subsequent to a parameter and/or function change in at least one of the hearing aids (1, 1', 11, 22, 24). - Method according to one of Claims 1 to 8,
characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1') hearing aid is effected in a plurality of parallel frequency channels of the respective signal processing unit (3, 13, 29), and the gain is ascertained and matched in at least one frequency channel in each case. - Method for the adjustment of a hearing aid system having at least one first (1, 11, 22, 24) and a second (1') hearing aid which each comprise at least one input transducer (2, 2', 12, 25, 26) for picking up an audible input signal and converting it into an electrical signal, a signal processing unit (3, 3', 13, 29) for processing the electrical signal, and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal, and between which a signal path (10) is provided for the purpose of data transmission, a signal amplitude of the electrical signal being ascertained in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24), and a signal being transmitted via the signal path (10) to the second hearing aid (1') for the purpose of matching the signal amplitude of the electrical signal in the signal path between the input transducer (2') and the output transducer (4') of the second hearing aid (1') to the ascertained signal amplitude of the electrical signal in the first hearing aid (1, 11, 22, 24), characterized in that the signal amplitude is ascertained by producing a test signal which at least partially transits the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24).
- Method according to Claim 10, characterized in that the signal amplitude of the electrical signal is automatically ascertained in the first hearing aid (1, 11, 22, 24) and a signal is transmitted to the second hearing aid (1').
- Method according to one of Claims 10 to 11,
characterized in that the signal amplitude is ascertained in the first (1, 11, 22, 24) and the second (1') hearing aid and a respective signal is transmitted to the other hearing aid. - Method according to one of Claims 10 to 12,
characterized in that the signal amplitude is matched by adjusting filter means (9, 9'). - Method according to one of Claims 10 to 13,
characterized in that the signal amplitude is ascertained and matched at periodic intervals. - Method according to one of Claims 10 to 14,
characterized in that the signal amplitude is ascertained and matched subsequent to a parameter and/or function change in at least one of the hearing aids (1, 1', 11, 22, 24). - Method according to one of Claims 10 to 15,
characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1') hearing aid is effected in a plurality of parallel frequency channels of the respective signal processing unit (3, 13, 29), and the signal amplitudes are ascertained and matched in at least one frequency channel in each case. - Hearing aid system having at least one first (1, 11, 22, 24) and a second (1') hearing aid which each comprise at least one input transducer (2, 2', 12, 25, 26) for picking up an audible input signal and converting it into an electrical signal, a signal processing unit (3, 3', 13, 29) for processing the electrical signal, and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal, and between which a signal path (10) is provided for the purpose of data transmission,
characterized in that the first hearing aid (1, 11, 22, 24) comprises means for measuring and means for sending data regarding a gain or gain change of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24), and the second hearing aid (1') comprises means for receiving the sent data and means for matching a gain in the signal path between the input transducer (2') and the output transducer (4') of the second hearing aid (1') to the gain or gain change of the electrical signal in the first hearing aid (1, 11, 22, 24). - Hearing aid system according to Claim 17, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1') hearing aid is effected in a plurality of parallel frequency channels of the respective signal processing unit (3, 3', 13, 29), and at least the first hearing aid (1, 11, 22, 24) comprises means for ascertaining the gain or gain change, and at least the second hearing aid (1') comprises means for matching the gain in at least one frequency channel.
- Hearing aid system having at least one first (1, 11, 22, 24) and a second (1') hearing aid which each comprise at least one input transducer (2, 2', 12, 25, 26) for picking up an audible input signal and converting it into an electrical signal, a signal processing unit (3, 3', 13, 29) for processing the electrical signal, and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal, and between which a signal path (10) is provided for the purpose of data transmission,
characterized in that the first hearing aid (1, 11, 22, 24) comprises means for measuring and means for sending data regarding a signal amplitude of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24), and the second hearing aid (1') comprises means for receiving the sent data and means for matching a signal amplitude in the signal path between the input transducer (2') and the output transducer (4') of the second hearing aid (1') to the signal amplitude of the electrical signal in the first hearing aid (1, 11, 22, 24). - Hearing aid system according to Claim 19, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1') hearing aid is effected in a plurality of parallel frequency channels of the respective signal processing unit (3, 3', 13, 29), and at least the first hearing aid (1, 11, 22, 24) comprises means for ascertaining the signal amplitude, and at least the second hearing aid (1') comprises means for matching the signal amplitude in at least one frequency channel.
- Hearing aid system according to Claim 19 or 20,
characterized in that the first hearing aid (1, 11, 22, 24) comprises at least one transmission unit (8, 8', 20, 34), and the second hearing aid (1') comprises at least one reception unit (8'), for the wireless signal transmission between the first (1, 11, 22, 24) hearing aid and the second (1') hearing aid. - Hearing aid system according to one of Claims 19 to 21, characterized in that at least the first (1, 11, 22, 24) hearing aid comprises means for producing a test signal.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE10228632A DE10228632B3 (en) | 2002-06-26 | 2002-06-26 | Directional hearing with binaural hearing aid care |
EP03013553A EP1379102B1 (en) | 2002-06-26 | 2003-06-13 | Sound localization in binaural hearing aids |
Related Parent Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP03013553A Division EP1379102B1 (en) | 2002-06-26 | 2003-06-13 | Sound localization in binaural hearing aids |
EP03013553.7 Division | 2003-06-13 |
Publications (3)
Publication Number | Publication Date |
---|---|
EP2180726A1 EP2180726A1 (en) | 2010-04-28 |
EP2180726B1 EP2180726B1 (en) | 2011-02-23 |
EP2180726B2 true EP2180726B2 (en) | 2014-11-05 |
Family
ID=29719413
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP03013553A Expired - Lifetime EP1379102B1 (en) | 2002-06-26 | 2003-06-13 | Sound localization in binaural hearing aids |
EP10000610.5A Expired - Lifetime EP2180726B2 (en) | 2002-06-26 | 2003-06-13 | Sound localization in binaural hearing aids |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP03013553A Expired - Lifetime EP1379102B1 (en) | 2002-06-26 | 2003-06-13 | Sound localization in binaural hearing aids |
Country Status (4)
Country | Link |
---|---|
US (1) | US7474758B2 (en) |
EP (2) | EP1379102B1 (en) |
DE (3) | DE10228632B3 (en) |
DK (2) | DK2180726T4 (en) |
Families Citing this family (52)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP4336458B2 (en) * | 1999-10-15 | 2009-09-30 | フォーナック アーゲー | Binaural hearing aid synchronization method |
EP1658754B1 (en) * | 2003-06-24 | 2011-10-05 | GN ReSound A/S | A binaural hearing aid system with coordinated sound processing |
US7496205B2 (en) * | 2003-12-09 | 2009-02-24 | Phonak Ag | Method for adjusting a hearing device as well as an apparatus to perform the method |
DE102004055738B4 (en) * | 2004-11-18 | 2010-11-04 | Fachhochschule Jena | Signal processing unit and signal processing method |
US7545944B2 (en) | 2005-04-18 | 2009-06-09 | Phonak Ag | Controlling a gain setting in a hearing instrument |
DE102006020832B4 (en) | 2006-05-04 | 2016-10-27 | Sivantos Gmbh | Method for suppressing feedback in hearing devices |
US7876906B2 (en) | 2006-05-30 | 2011-01-25 | Sonitus Medical, Inc. | Methods and apparatus for processing audio signals |
US8150542B2 (en) * | 2006-06-14 | 2012-04-03 | Phonak Ag | Positioning and orienting a unit of a hearing device relative to individual's head |
US8483416B2 (en) | 2006-07-12 | 2013-07-09 | Phonak Ag | Methods for manufacturing audible signals |
US7764798B1 (en) * | 2006-07-21 | 2010-07-27 | Cingular Wireless Ii, Llc | Radio frequency interference reduction in connection with mobile phones |
US8291912B2 (en) * | 2006-08-22 | 2012-10-23 | Sonitus Medical, Inc. | Systems for manufacturing oral-based hearing aid appliances |
EP2064916B1 (en) * | 2006-09-08 | 2018-12-05 | SoundMed, LLC | Methods and apparatus for treating tinnitus |
EP2103179A1 (en) * | 2007-01-10 | 2009-09-23 | Phonak AG | System and method for providing hearing assistance to a user |
DE102007017761B4 (en) | 2007-04-16 | 2016-08-11 | Sivantos Gmbh | Method for adapting a binaural hearing aid system |
US8270638B2 (en) * | 2007-05-29 | 2012-09-18 | Sonitus Medical, Inc. | Systems and methods to provide communication, positioning and monitoring of user status |
US20080304677A1 (en) * | 2007-06-08 | 2008-12-11 | Sonitus Medical Inc. | System and method for noise cancellation with motion tracking capability |
US20090028352A1 (en) * | 2007-07-24 | 2009-01-29 | Petroff Michael L | Signal process for the derivation of improved dtm dynamic tinnitus mitigation sound |
DE102007035173A1 (en) * | 2007-07-27 | 2009-02-05 | Siemens Medical Instruments Pte. Ltd. | Method for adjusting a hearing system with a perceptive model for binaural hearing and hearing aid |
DE102007035174B4 (en) * | 2007-07-27 | 2014-12-04 | Siemens Medical Instruments Pte. Ltd. | Hearing device controlled by a perceptive model and corresponding method |
US20120235632A9 (en) * | 2007-08-20 | 2012-09-20 | Sonitus Medical, Inc. | Intra-oral charging systems and methods |
US8433080B2 (en) * | 2007-08-22 | 2013-04-30 | Sonitus Medical, Inc. | Bone conduction hearing device with open-ear microphone |
US8224013B2 (en) * | 2007-08-27 | 2012-07-17 | Sonitus Medical, Inc. | Headset systems and methods |
US7682303B2 (en) | 2007-10-02 | 2010-03-23 | Sonitus Medical, Inc. | Methods and apparatus for transmitting vibrations |
US20090105523A1 (en) * | 2007-10-18 | 2009-04-23 | Sonitus Medical, Inc. | Systems and methods for compliance monitoring |
US8795172B2 (en) * | 2007-12-07 | 2014-08-05 | Sonitus Medical, Inc. | Systems and methods to provide two-way communications |
EP2071873B1 (en) * | 2007-12-11 | 2017-05-03 | Bernafon AG | A hearing aid system comprising a matched filter and a measurement method |
US8270637B2 (en) * | 2008-02-15 | 2012-09-18 | Sonitus Medical, Inc. | Headset systems and methods |
US7974845B2 (en) | 2008-02-15 | 2011-07-05 | Sonitus Medical, Inc. | Stuttering treatment methods and apparatus |
US8023676B2 (en) | 2008-03-03 | 2011-09-20 | Sonitus Medical, Inc. | Systems and methods to provide communication and monitoring of user status |
US8150075B2 (en) | 2008-03-04 | 2012-04-03 | Sonitus Medical, Inc. | Dental bone conduction hearing appliance |
US20090226020A1 (en) * | 2008-03-04 | 2009-09-10 | Sonitus Medical, Inc. | Dental bone conduction hearing appliance |
WO2009131755A1 (en) * | 2008-04-24 | 2009-10-29 | Sonitus Medical, Inc. | Microphone placement for oral applications |
US20090270673A1 (en) * | 2008-04-25 | 2009-10-29 | Sonitus Medical, Inc. | Methods and systems for tinnitus treatment |
DK2148527T3 (en) * | 2008-07-24 | 2014-07-14 | Oticon As | Acoustic feedback reduction system in hearing aids using inter-aural signal transmission, method and application |
JP5617133B2 (en) | 2008-11-05 | 2014-11-05 | ヒア アイピー ピーティーワイ リミテッド | Directional output signal generation system and method |
ATE521198T1 (en) * | 2008-11-20 | 2011-09-15 | Oticon As | BINAURAL HEARING INSTRUMENT |
JP5409656B2 (en) * | 2009-01-22 | 2014-02-05 | パナソニック株式会社 | Hearing aid |
AU2010301027B2 (en) | 2009-10-02 | 2014-11-06 | Soundmed, Llc | Intraoral appliance for sound transmission via bone conduction |
US9420385B2 (en) * | 2009-12-21 | 2016-08-16 | Starkey Laboratories, Inc. | Low power intermittent messaging for hearing assistance devices |
US8825037B2 (en) * | 2009-12-22 | 2014-09-02 | Starkey Laboratories, Inc. | FM radio system for digital and analog communications for hearing assistance devices |
US8855324B2 (en) | 2011-06-29 | 2014-10-07 | Cochlear Limited | Systems, methods, and article of manufacture for configuring a hearing prosthesis |
EP2544462B1 (en) * | 2011-07-04 | 2018-11-14 | GN Hearing A/S | Wireless binaural compressor |
DK3396980T3 (en) | 2011-07-04 | 2021-04-26 | Gn Hearing As | Binaural compressor for directions |
US10299047B2 (en) | 2012-08-15 | 2019-05-21 | Meyer Sound Laboratories, Incorporated | Transparent hearing aid and method for fitting same |
DK2885872T3 (en) | 2012-08-15 | 2019-06-11 | Meyer Sound Laboratories Incorporated | Hearing aid with level and frequency dependent gain |
DE102013207080B4 (en) * | 2013-04-19 | 2019-03-21 | Sivantos Pte. Ltd. | Binaural microphone adaptation using your own voice |
US9807519B2 (en) * | 2013-08-09 | 2017-10-31 | The United States Of America As Represented By The Secretary Of Defense | Method and apparatus for analyzing and visualizing the performance of frequency lowering hearing aids |
WO2016067754A1 (en) * | 2014-10-30 | 2016-05-06 | ソニー株式会社 | Acoustic output device |
US9749755B2 (en) | 2014-12-29 | 2017-08-29 | Gn Hearing A/S | Hearing device with sound source localization and related method |
EP3386216B1 (en) * | 2017-04-06 | 2021-08-25 | Oticon A/s | A hearing system comprising a binaural level and/or gain estimator, and a corresponding method |
CN111857041A (en) * | 2020-07-30 | 2020-10-30 | 东莞市易联交互信息科技有限责任公司 | Motion control method, device, equipment and storage medium of intelligent equipment |
DE102020209907A1 (en) * | 2020-08-05 | 2022-02-10 | Sivantos Pte. Ltd. | Method of operating a hearing aid and hearing aid |
Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4049930A (en) † | 1976-11-08 | 1977-09-20 | Nasa | Hearing aid malfunction detection system |
US4484345A (en) † | 1983-02-28 | 1984-11-20 | Stearns William P | Prosthetic device for optimizing speech understanding through adjustable frequency spectrum responses |
US5016280A (en) † | 1988-03-23 | 1991-05-14 | Central Institute For The Deaf | Electronic filters, hearing aids and methods |
US5434924A (en) † | 1987-05-11 | 1995-07-18 | Jay Management Trust | Hearing aid employing adjustment of the intensity and the arrival time of sound by electronic or acoustic, passive devices to improve interaural perceptual balance and binaural processing |
WO1997014267A1 (en) † | 1995-10-12 | 1997-04-17 | Audiologic, Inc. | Hearing aid with in situ testing capability |
WO1999026453A1 (en) † | 1997-11-18 | 1999-05-27 | Audiologic Hearing Systems, L.P. | Feedback cancellation apparatus and methods |
WO1999043185A1 (en) † | 1998-02-18 | 1999-08-26 | Tøpholm & Westermann APS | A binaural digital hearing aid system |
EP0941014A2 (en) † | 1998-03-03 | 1999-09-08 | Siemens Audiologische Technik GmbH | Hearing aid system with two hearing aid devices and method of operation of such an hearing aid system |
DE10046098C1 (en) † | 2000-09-18 | 2002-04-04 | Siemens Audiologische Technik | Hearing aid testing method incorporates testing of pressure sensor between seal integrity testing cycles |
Family Cites Families (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4531229A (en) * | 1982-10-22 | 1985-07-23 | Coulter Associates, Inc. | Method and apparatus for improving binaural hearing |
US5757932A (en) * | 1993-09-17 | 1998-05-26 | Audiologic, Inc. | Digital hearing aid system |
US5479522A (en) * | 1993-09-17 | 1995-12-26 | Audiologic, Inc. | Binaural hearing aid |
EP0814636A1 (en) * | 1996-06-21 | 1997-12-29 | Siemens Audiologische Technik GmbH | Hearing aid |
DE19704119C1 (en) * | 1997-02-04 | 1998-10-01 | Siemens Audiologische Technik | Binaural hearing aid |
NL1009485C2 (en) * | 1998-06-24 | 2000-01-11 | Wilhelm Henricus Jurriaan Van | Acoustic runtime measurement. |
AU753295B2 (en) * | 1999-02-05 | 2002-10-17 | Widex A/S | Hearing aid with beam forming properties |
AU2001278418A1 (en) * | 2000-07-14 | 2002-01-30 | Gn Resound A/S | A synchronised binaural hearing system |
DE10048354A1 (en) * | 2000-09-29 | 2002-05-08 | Siemens Audiologische Technik | Method for operating a hearing aid system and hearing aid system |
-
2002
- 2002-06-26 DE DE10228632A patent/DE10228632B3/en not_active Expired - Fee Related
-
2003
- 2003-06-13 DE DE50313499T patent/DE50313499D1/en not_active Expired - Lifetime
- 2003-06-13 DE DE50312941T patent/DE50312941D1/en not_active Expired - Lifetime
- 2003-06-13 DK DK10000610.5T patent/DK2180726T4/en active
- 2003-06-13 EP EP03013553A patent/EP1379102B1/en not_active Expired - Lifetime
- 2003-06-13 EP EP10000610.5A patent/EP2180726B2/en not_active Expired - Lifetime
- 2003-06-13 DK DK03013553.7T patent/DK1379102T3/en active
- 2003-06-26 US US10/607,281 patent/US7474758B2/en not_active Expired - Fee Related
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4049930A (en) † | 1976-11-08 | 1977-09-20 | Nasa | Hearing aid malfunction detection system |
US4484345A (en) † | 1983-02-28 | 1984-11-20 | Stearns William P | Prosthetic device for optimizing speech understanding through adjustable frequency spectrum responses |
US5434924A (en) † | 1987-05-11 | 1995-07-18 | Jay Management Trust | Hearing aid employing adjustment of the intensity and the arrival time of sound by electronic or acoustic, passive devices to improve interaural perceptual balance and binaural processing |
US5016280A (en) † | 1988-03-23 | 1991-05-14 | Central Institute For The Deaf | Electronic filters, hearing aids and methods |
WO1997014267A1 (en) † | 1995-10-12 | 1997-04-17 | Audiologic, Inc. | Hearing aid with in situ testing capability |
WO1999026453A1 (en) † | 1997-11-18 | 1999-05-27 | Audiologic Hearing Systems, L.P. | Feedback cancellation apparatus and methods |
WO1999043185A1 (en) † | 1998-02-18 | 1999-08-26 | Tøpholm & Westermann APS | A binaural digital hearing aid system |
EP0941014A2 (en) † | 1998-03-03 | 1999-09-08 | Siemens Audiologische Technik GmbH | Hearing aid system with two hearing aid devices and method of operation of such an hearing aid system |
DE10046098C1 (en) † | 2000-09-18 | 2002-04-04 | Siemens Audiologische Technik | Hearing aid testing method incorporates testing of pressure sensor between seal integrity testing cycles |
Also Published As
Publication number | Publication date |
---|---|
EP2180726B1 (en) | 2011-02-23 |
DK2180726T4 (en) | 2015-02-16 |
EP1379102A3 (en) | 2009-03-04 |
DE10228632B3 (en) | 2004-01-15 |
DE50313499D1 (en) | 2011-04-07 |
EP2180726A1 (en) | 2010-04-28 |
US7474758B2 (en) | 2009-01-06 |
DK1379102T3 (en) | 2010-11-08 |
DE50312941D1 (en) | 2010-09-16 |
DK2180726T3 (en) | 2011-06-14 |
US20040057591A1 (en) | 2004-03-25 |
EP1379102B1 (en) | 2010-08-04 |
EP1379102A2 (en) | 2004-01-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP2180726B2 (en) | Sound localization in binaural hearing aids | |
EP3451705B1 (en) | Method and apparatus for the rapid detection of own voice | |
EP1489885B1 (en) | 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 | |
DE10331956C5 (en) | Hearing aid and method for operating a hearing aid with a microphone system, in which different Richtcharaktistiken are adjustable | |
EP1377118B1 (en) | Hearing aid system with hearing aid and external processing unit | |
DE102007017761B4 (en) | Method for adapting a binaural hearing aid system | |
EP2506603B1 (en) | Hearing aid system with a directional microphone system and method for operating such a hearing aid system with said directional microphone system | |
DE102005020317A1 (en) | Automatic gain adjustment on a hearing aid | |
EP2437258B1 (en) | Method and device for frequency compression with selective frequency shifting | |
DE102011006129B4 (en) | Hearing device with feedback suppression device and method for operating the hearing device | |
EP2811762B1 (en) | Logic-based binaural beam forming system | |
DE10334396B3 (en) | Electrical hearing aid has individual microphones combined to provide 2 microphone units in turn combined to provide further microphone unit with same order directional characteristic | |
EP2822300B1 (en) | Detection of listening situations with different signal sources | |
DE102014218672B3 (en) | Method and apparatus for feedback suppression | |
DE102009004182B3 (en) | Method for wireless sensing of right and/or left hearing device e.g. concha hearing device, utilized by hearing impaired person, involves sensing hearing device transmitting radio signals based on difference of signals | |
EP2793488A1 (en) | Binaural microphone adjustment by means of the userýs own voice | |
DE102021103769B4 (en) | Methods for signal processing | |
EP2648424B1 (en) | Method for limiting the output level in hearing aids | |
DE102007030067B4 (en) | Hearing aid with passive, input-level-dependent noise reduction and method | |
DE102008036803B3 (en) | Arrangement and method for controlling a feedback suppression in hearing devices | |
EP3240307B1 (en) | Method for transmitting an audio signal | |
EP1909534A2 (en) | Hearing device with asymmetric audio balance and corresponding adjusting method | |
DE102021210098A1 (en) | Method of operating a hearing aid | |
EP3926983A2 (en) | Hearing system with at least one hearing instrument worn in or on the ear of the user and method for operating such a hearing system | |
EP4311269A1 (en) | Method for operating a binaural hearing aid, binaural hearing aid, and computer program |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AC | Divisional application: reference to earlier application |
Ref document number: 1379102 Country of ref document: EP Kind code of ref document: P |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): CH DE DK FR GB LI |
|
17P | Request for examination filed |
Effective date: 20100406 |
|
GRAP | Despatch of communication of intention to grant a patent |
Free format text: ORIGINAL CODE: EPIDOSNIGR1 |
|
RIC1 | Information provided on ipc code assigned before grant |
Ipc: H04R 25/00 20060101AFI20100824BHEP |
|
GRAS | Grant fee paid |
Free format text: ORIGINAL CODE: EPIDOSNIGR3 |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
AC | Divisional application: reference to earlier application |
Ref document number: 1379102 Country of ref document: EP Kind code of ref document: P |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): CH DE DK FR GB LI |
|
REG | Reference to a national code |
Ref country code: GB Ref legal event code: FG4D Free format text: NOT ENGLISH |
|
REG | Reference to a national code |
Ref country code: CH Ref legal event code: EP Ref country code: CH Ref legal event code: NV Representative=s name: SIEMENS SCHWEIZ AG |
|
REF | Corresponds to: |
Ref document number: 50313499 Country of ref document: DE Date of ref document: 20110407 Kind code of ref document: P |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R096 Ref document number: 50313499 Country of ref document: DE Effective date: 20110407 |
|
REG | Reference to a national code |
Ref country code: DK Ref legal event code: T3 |
|
PLBI | Opposition filed |
Free format text: ORIGINAL CODE: 0009260 |
|
PLAX | Notice of opposition and request to file observation + time limit sent |
Free format text: ORIGINAL CODE: EPIDOSNOBS2 |
|
26 | Opposition filed |
Opponent name: GN RESOUND A/S (DK)/WIDEX A/S (DK)/ PHONAK AG (CH) Effective date: 20111123 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R026 Ref document number: 50313499 Country of ref document: DE Effective date: 20111123 |
|
PLBB | Reply of patent proprietor to notice(s) of opposition received |
Free format text: ORIGINAL CODE: EPIDOSNOBS3 |
|
PLAB | Opposition data, opponent's data or that of the opponent's representative modified |
Free format text: ORIGINAL CODE: 0009299OPPO |
|
R26 | Opposition filed (corrected) |
Opponent name: GN RESOUND A/S (DK)/WIDEX A/S (DK)/ PHONAK AG (CH) Effective date: 20111123 |
|
PLAB | Opposition data, opponent's data or that of the opponent's representative modified |
Free format text: ORIGINAL CODE: 0009299OPPO |
|
R26 | Opposition filed (corrected) |
Opponent name: GN RESOUND A/S (DK)/WIDEX A/S (DK)/ PHONAK AG (CH) Effective date: 20111123 |
|
PUAH | Patent maintained in amended form |
Free format text: ORIGINAL CODE: 0009272 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: PATENT MAINTAINED AS AMENDED |
|
27A | Patent maintained in amended form |
Effective date: 20141105 |
|
AK | Designated contracting states |
Kind code of ref document: B2 Designated state(s): CH DE DK FR GB LI |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R102 Ref document number: 50313499 Country of ref document: DE |
|
REG | Reference to a national code |
Ref country code: CH Ref legal event code: AELC |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R102 Ref document number: 50313499 Country of ref document: DE Effective date: 20141105 |
|
REG | Reference to a national code |
Ref country code: DK Ref legal event code: T4 Effective date: 20150213 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R082 Ref document number: 50313499 Country of ref document: DE Representative=s name: MAIER, DANIEL OLIVER, DIPL.-ING. UNIV., DE Ref country code: DE Ref legal event code: R081 Ref document number: 50313499 Country of ref document: DE Owner name: SIVANTOS GMBH, DE Free format text: FORMER OWNER: SIEMENS AUDIOLOGISCHE TECHNIK GMBH, 91058 ERLANGEN, DE |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 14 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 15 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 16 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DK Payment date: 20190624 Year of fee payment: 17 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: FR Payment date: 20190626 Year of fee payment: 17 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: CH Payment date: 20190624 Year of fee payment: 17 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DE Payment date: 20190624 Year of fee payment: 17 Ref country code: GB Payment date: 20190624 Year of fee payment: 17 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R119 Ref document number: 50313499 Country of ref document: DE |
|
REG | Reference to a national code |
Ref country code: DK Ref legal event code: EBP Effective date: 20200630 |
|
REG | Reference to a national code |
Ref country code: CH Ref legal event code: PL |
|
GBPC | Gb: european patent ceased through non-payment of renewal fee |
Effective date: 20200613 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: FR Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20200630 Ref country code: GB Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20200613 Ref country code: LI Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20200630 Ref country code: CH Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20200630 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20210101 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DK Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20200630 |