EP2200341B1 - Method for operating a hearing aid and hearing aid with a source separation device - Google Patents
Method for operating a hearing aid and hearing aid with a source separation device Download PDFInfo
- Publication number
- EP2200341B1 EP2200341B1 EP09175951.4A EP09175951A EP2200341B1 EP 2200341 B1 EP2200341 B1 EP 2200341B1 EP 09175951 A EP09175951 A EP 09175951A EP 2200341 B1 EP2200341 B1 EP 2200341B1
- Authority
- EP
- European Patent Office
- Prior art keywords
- signals
- source
- hearing aid
- signal
- specific reception
- 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.)
- Active
Links
- 238000000034 method Methods 0.000 title claims description 20
- 238000000926 separation method Methods 0.000 title claims description 16
- 238000012545 processing Methods 0.000 claims description 30
- 238000004458 analytical method Methods 0.000 claims description 21
- 230000006870 function Effects 0.000 claims description 8
- 230000009467 reduction Effects 0.000 claims description 4
- 230000000694 effects Effects 0.000 claims description 3
- 238000012512 characterization method Methods 0.000 claims 4
- 230000001944 accentuation Effects 0.000 claims 1
- 230000002452 interceptive effect Effects 0.000 description 8
- 230000001629 suppression Effects 0.000 description 5
- 206010011878 Deafness Diseases 0.000 description 4
- 230000008859 change Effects 0.000 description 4
- 230000010370 hearing loss Effects 0.000 description 4
- 231100000888 hearing loss Toxicity 0.000 description 4
- 208000016354 hearing loss disease Diseases 0.000 description 4
- 230000008901 benefit Effects 0.000 description 3
- 230000005236 sound signal Effects 0.000 description 2
- 230000003595 spectral effect Effects 0.000 description 2
- 230000001960 triggered effect Effects 0.000 description 2
- 230000009471 action Effects 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 230000002238 attenuated effect Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 239000002131 composite material Substances 0.000 description 1
- 230000001934 delay Effects 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 238000003379 elimination reaction Methods 0.000 description 1
- 230000007613 environmental effect Effects 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
- 238000010183 spectrum analysis Methods 0.000 description 1
- 238000013179 statistical model Methods 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
- 230000007704 transition 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
- H04R25/40—Arrangements for obtaining a desired directivity characteristic
- H04R25/407—Circuits for combining signals of a plurality of transducers
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
Definitions
- the present invention relates to a method for operating a hearing aid and a hearing aid.
- Hearing aids detect ambient sound and provide it compressed and amplified to a user.
- the useful signal is the sound that the user wants to perceive.
- Interference signals are all other sound impressions, regardless of whether they are generated by the hearing aid itself (microphone noise, feedback whistles, acoustic artifacts) or if they are part of the environmental situation (traffic, machine sounds, conversations of speakers in which the user does not want to listen ).
- the user Since the user essentially wants to perceive only the useful signals, but not the interference signals, the problem arises of distinguishing the useful signals from the interference signals, so that the useful signals can be emphasized by a corresponding signal processing with respect to the interference signals.
- notch filters For example, to suppress the feedback whistle algorithms for feedback compensation, notch filters, etc. can be used.
- noise suppression algorithms based on the Wiener filter are used.
- the difficulty with these traditional methods is that they do not allow unambiguous identification of the interference signal and thus always reduce not only the interference signal but also an often not inconsiderable part of the useful signal.
- the publication DE 101 140 15 A1 describes a method in which the hearing aid wearer can mark a specific sound signal from his listening environment actively (eg by pressing a button) as an interference or useful signal.
- the disadvantage here is that the excluded from the microphone sound signal is an acoustic composite signal containing signal components of all active sound sources in the environment of the user.
- no clear identification as interference or useful signal is possible with simultaneously occurring interference and useful signals.
- the identification of such a mixed signal as interference signal in addition to a reduction of the interference signal contained therein would inevitably lead to an undesirable reduction of the useful signal.
- a hearing aid with a directional microphone system is known, which is suitable for determining the directions of incidence emanating from different sound sources acoustic signals. This makes it possible to emphasize or suppress certain sound sources from others.
- a hearing aid with a source separation device for generating source-specific received signals known.
- the separation of the acoustic signals emanating from different signal sources takes place for example by algorithms for so-called "blind source separation" (BSS).
- BSS blind source separation
- the acoustic signals received by the different signal sources can then be subdivided into interfering or useful signals, possibly taking into account manual user inputs. Only the signals identified as useful signals are then further processed and amplified.
- a method for processing an input signal in a hearing aid, wherein the input signal is dependent on an acoustic signal and is decomposed into an input signal for a source, the individual signals being assigned a spatial position of the source and wherein the individual signals are output depending on the spatial position or spent attenuated.
- a disadvantage of the known hearing aid devices with a source separation device is the high computing power required to separate the signal sources. This has, for example, a negative effect on the running time of a hearing aid operated with a small battery.
- Object of the present invention is to provide a hearing aid device system and a method for operating a hearing aid device system in which a different signal processing of interfering and useful signals with relatively little computational effort is possible.
- each of the microphones In a hearing aid device having a plurality of microphones, each of the microphones generally receives another mixed acoustic signal, which results in each case as a superimposition of the acoustic signals generated by different sound sources at the location of the respective microphone.
- Each of the microphones converts the mixed acoustic signal entering the respective microphone into an electrical mixed signal, which is then further processed and amplified to compensate for a user's individual hearing loss. This results in an electrical output signal that converts an output transducer of the hearing aid, usually a listener, into an output signal that is perceived by the user as an acoustic signal.
- the signal processing within a hearing aid can be adjusted by a variety of adjustable parameter settings to the individual user or the listening situation in which the user is currently located.
- suitable parameter settings critical to the user's success in using the hearing aid to improve their hearing.
- Decisive for this success is how the hearing aid in question suppressed interference signals and payloads - especially against the interference signals - highlights.
- the corresponding parameter settings for this determine, for example, the transfer functions of certain filters or they determine whether certain algorithms, for example for noise suppression or speech signal increase, are active or not.
- the basic idea of the invention consists in not directly processing or suppressing the source-specific received signals, as is currently the case, but the source-specific received signals are now used to generate parameters which cause an emphasis or a suppression of the respective source-specific received signal, even then even if the source-specific reception signals do not enter directly into the output signal of the hearing aid in question.
- the invention offers the advantage that the generation of the source-specific reception signals can now take place in a structure which is ancillary to the signal path of a hearing aid device, starting from the microphones via the signal processing unit to the listener.
- time delays in the sibling structure only play a minor role, since in the invention the acoustic output signal does not emerge directly from one or more source-specific received signals during the normal operation of the relevant hearing aid , The computing power required for generating the source-specific received signals can thus be reduced.
- the computation-intensive generation of the source-specific received signals takes place only in sections and not during the entire operation a relevant hearing aid.
- the separation of the different sound sources ultimately serves in particular to extract certain characteristics of the interfering as well as the useful signals, on the basis of which the interference signals can be suppressed or the useful signals can be emphasized. If such characteristics have been established, the generation of the source-specific received signals can be dispensed with, at least for a limited period of time, for which the detected interferers of the useful signals are at least largely stationary.
- the required for the operation of a hearing aid computing power can be significantly reduced.
- the hearing aid device system additionally comprises, in addition to at least one hearing aid device, an external processor unit.
- an external processor unit This preferably also serves for the remote control of a relevant hearing aid device of the hearing aid system.
- the external processor unit is equipped for this purpose with at least two microphones for generating electrical mixed signals.
- the analysis of the source-specific received signals and the determination of parameter settings for the hearing aid in the external processor unit are also advantageously carried out. The parameter settings determined in this case can then be transmitted wirelessly from the external processor unit to the relevant hearing aid device.
- the size of the device and its power consumption play a minor role in the external processor unit.
- the external processor unit can be equipped, for example, with a display and a keyboard, with the help of which, for example, the spatial distribution of several signal sources in space graphically displayed and the distinction between noise and useful sound sources can also be done taking into account user input.
- FIG. 1 has only a single hearing aid on.
- this includes the microphones M1, M2, ..., Mn.
- two signal sources S1 and S2 are also present in the environment of the hearing aid. This generates a first mixed acoustic signal at the input of the microphone M1, a second mixed acoustic signal at the input of the microphone M2, etc.
- the microphone M1 converts the first mixed acoustic signal into a first mixed electric signal E1
- the microphone M2 converts the second mixed acoustic signal into a second mixed electric signal E2, etc.
- the electrical mixed signals E1, E2, ..., En are further processed and amplified in a signal processing unit 1, so that an electrical output signal results, which is converted by a receiver 2 into an acoustic output signal and the hearing of a user.
- the signal processing in the signal processing unit 1 can be adapted to the individual hearing loss of the user and the current listening environment in which the hearing aid is currently located by a multiplicity of parameter settings.
- the hearing aid according to the invention comprises in one to the signal path between the microphones M1 to Mn and the handset. 2 sibling signal path, a source separation device, in particular a BSS unit 3, for generating a plurality of source-specific received signals.
- a source separation device in particular a BSS unit 3, for generating a plurality of source-specific received signals.
- the BSS unit 3 generates a first source-specific received signal Q1, which essentially results from the acoustic signal emitted by the signal source S1, and a second source-specific received signal Q2, which is essentially that from the signal source S2 emitted acoustic signal results.
- the source-specific received signals Q1, Q2,..., Qn are fed to a marking device 6, by means of which a classification of the source-specific received signals Q1 to Qn into interfering or useful signals takes place.
- the marking device 6 is connected to a control element 7, by which the source-specific received signals Q1 to Qn can be presented to the user in succession. It then takes place for each individual source-specific received signal an identification as interference or useful signal by manual operation of the control element 7 by the user.
- the source-specific received signals classified as interference or useful signal are then fed to an analysis device 4, in which they are automatically analyzed with regard to specific characteristics.
- the signal analysis in the signal analysis device 4 can determine, for example, a spectral analysis, an estimate of parameters of a statistical model, the probability densities of the spectral components (eg real part, imaginary part and magnitude of the Fourier coefficients) at different frequencies or the direction of incidence of acoustic signals in the microphone system.
- the automatic determination of suitable parameters for the operation of the signal processing unit 1 for suppressing the source-specific received signals marked as interference signals or for highlighting the source-specific received signals designated as useful signals takes place in a parameter determination device 5.
- the parameters thus defined can be applied in a variety of ways to the processing of electrical Mixed signals E1 to En by the signal processing unit 1 impact.
- the microphones M1 to Mm in the signal processing unit 1 can be electronically connected to directional microphones, the directivity being then influenced by the parameters determined in the parameter determination device 5.
- the parameters can be used, for example, to switch on or off noise-elimination algorithms or to change their mode of operation. Furthermore, it can be used to set certain filter parameters that highlight or suppress certain frequency bands, for example.
- parameters based on the analysis of the spurious or useful signals may affect the operation of an MMSE (Minimum Mean Square Error) algorithm or Ephraim-Malah non-Gaussian algorithm.
- parameters determined in the parameter determination device 5 control an algorithm for restoring a speech signal in which a certain frequency range is missing or disturbed and in which this frequency range is synthesized from undisturbed frequency ranges.
- the determined parameter settings have a direct influence on the signal processing in the signal path between the microphones M1, M2,..., Mn and the handset 2, such that at least one interference signal is suppressed or at least one useful signal is emphasized. As a rule, however, they have no direct influence on the source-specific received signals Q1, Q2,..., Qm.
- the parameter settings determined in this way influence the signal processing until a recalculation takes place. This can for example be triggered manually by the user.
- the generation of source-specific received signals Q1, Q2, ..., Qm by the hearing aid is not necessary for the period of time after a parameter determination until the time at which a recalculation of the parameter settings is triggered.
- the computation-intensive generation of the source-specific received signals Q1, Q2,..., Qm is omitted for this period during normal operation of the hearing aid.
- these are only required for the classification into interference and useful signals and for the determination of the parameters for their suppression or emphasis, but not for the normal operation of the hearing aid device in which these parameter settings are then effective.
- the invention has the advantage that the computation-intensive determination of the source-specific received signals, the analysis of the same and the determination of parameters based thereon need only be performed on a periodic basis. As long as the external situation remains substantially stationary (for example, the frequency of an input signal classified as a noise signal does not change) it is not necessary to adapt once determined parameter settings.
- the operation of the source separation device 3, the analysis device 4 and the parameter determination device 5 can accordingly be omitted in sections during the operation of the hearing aid device.
- the recalculation of corresponding parameters then takes place, for example, after the hearing aid is switched on, after a program changeover, after an automatically determined change in the listening environment or as requested by a corresponding manual user input.
- a further advantage of the invention results from the fact that the source-specific received signals also do not have to be generated in real time. This would only be the case if the acoustic output signal of the relevant hearing aid device emerged directly from one or more source-specific received signals. However, the latter in the invention is not the case, plays a time delay in generating the source-specific received signals only a minor role.
- the source-specific received signals Q1, Q2,..., Qm can also be advantageously determined in chronological succession and subsequently presented to the user.
- only one source-specific received signal must be determined at any time. This also contributes to the reduction of the required computing power compared to a conventional hearing aid device with a source separation device.
- an alternative embodiment provides for the arrangement of the analysis device 4 FIG. 1 in immediate connection to the source separation device 3. Unlike the embodiment shown in FIG. 1 thus, an automatic classification of the source-specific received signals Q1 to Qn in interference or useful signals on the basis of carried out in the analysis device 4 signal analysis done. Manual user inputs to distinguish between interfering or useful signals are no longer required.
- the illustrated hearing aid device system comprises not only a hearing aid device 10 but also an external processor unit 20.
- the basic mode of operation of the hearing aid device 10 is similar to that of the hearing aid device in the exemplary embodiment according to FIG FIG. 1 ,
- the hearing aid device 10 in the exemplary embodiment comprises the two microphones M1 'and M2', in which received by the signal sources S1 'and S2' generated acoustic signals in the form of mixed acoustic signals.
- the microphones M1 'and M2' generate the mixed electrical signals E1 'and E2' from the mixed acoustic signals.
- the latter are processed in the signal processing unit 11 to compensate for the individual hearing loss of a user and strengthened.
- the resulting electrical output signal is converted by a receiver 12 into an acoustic signal and fed to the user's ear.
- the signal processing within the signal processing unit 11 can be adapted to the individual hearing loss of the user or the instantaneous hearing situation in which the hearing aid device 10 is currently located.
- the hearing aid device system in the embodiment according to FIG. 2 also the external processor unit 20, which is designed in particular as a remote control for operating the hearing aid device 10.
- the remote control 20 also includes the microphones M3 ', M4', ..., Mn '. These also receive mixed acoustic signals resulting from the acoustic signals emanating from the signal sources S1 'and S2'. The acoustic mixed signals are converted by the microphones M3 ', M4', ... Mn 'into the electrical mixed signals E3', E4 ', ..., En' and fed to a source separation device 13, in particular a BSS unit.
- the latter generates from the electrical mixed signals E3 ', E4', ..., En 'the source-specific received signals Q1', Q2 ', ..., Qn'.
- the source-specific received signals Q1 'and Q2' In the exemplary embodiment with two signal sources S1 'and S2', therefore, the source-specific received signals Q1 'and Q2'.
- the external processor unit 20 provides the marking device 16, through which, in conjunction with the operating element 17, manual user inputs for the classification of the source-specific received signals into interfering or useful signals possible are.
- further units (not shown) of the external processor unit 20 can be present for this purpose, which facilitate the division into interference or useful signals.
- the external processor unit can determine the spatial distribution of the sound sources in the room and display them graphically on a display.
- the external processor unit 20 may also include a speaker, so that the user can listen to the individual sound sources individually and separately from each other. As a result, the classification into interference or useful signals for the user is much easier.
- the source-specific received signals are analyzed for the presence of certain characteristics. These include in particular the direction of incidence of the acoustic signals generated by the respective sound sources in the external processor unit 20, the frequency spectrum of the signals, possibly present therein modulation frequencies, etc. Based on the thus determined characteristic properties of the source-specific received signals then takes place in the parameter determination device 15, the determination suitable parameters for the operation of the signal processing unit 11 of the hearing aid 10. These parameter settings relate in particular to the mode of action (directivity) of the microphone system of the hearing aid 10 or the operation of certain filters and algorithms. For the determined parameter settings to be effective, they must be transferred from the external processor unit 20 to the hearing aid device 10. For this purpose, both the hearing aid device 10 and the external processor unit 20 each comprise a transmitting and receiving unit 18 and 19, respectively. Furthermore, the external processor unit 20 comprises a controller 21 which controls or monitors processes and states within the external processor unit 20.
- the operation of the hearing aid system differs as well according to FIG. 2 from a conventional hearing aid device with a BSS unit, in particular in that the generated source-specific received signals are used predominantly for determining parameter settings.
- conventional hearing aid devices with a BSS unit directly at least one of the generated source-specific received signals used to directly generate the electrical or acoustic output signal.
- the latter has the disadvantage that thus the BSS unit must be permanently in operation, whereas in the invention a time-wise operation of the BSS unit is sufficient.
- the operation of a hearing aid according to the invention with the determined parameter settings can be carried out without the source-specific reception signals must be continuously generated for this purpose.
- a considerable amount of computing power can be saved compared to a conventional system with a BSS unit.
- the essential method steps in a method according to the invention for operating a hearing aid system in conjunction with FIG. 3 shown again.
- the operation is initially in the state Z1, in which the signal processing in the hearing aid works with certain, predetermined parameter settings. It then checks if recalculation of parameter settings is required. In the flowchart according to FIG. 3 this is illustrated by the symbol E.
- Trigger for a recalculation of Paramter settings are, for example, a program switching in the hearing aid concerned or a detected by the hearing aid change from a first listening situation to a second auditory situation.
- the hearing aid device changes to the state Z2, in which the generation of source-specific received signals takes place.
- the state Z2 takes place in the state Z3 a division of the individual source-specific received signals in interference or useful signals. This classification can be done in particular taking into account manual user input.
- an analysis of the source-specific received signals marked as interference signal or useful signal takes place. In each case certain characteristic properties of the signals in question are determined.
Landscapes
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
- Circuit For Audible Band Transducer (AREA)
- Soundproofing, Sound Blocking, And Sound Damping (AREA)
Description
Die vorliegende Erfindung betrifft ein Verfahren zum Betrieb eines Hörhilfegerätes sowie ein Hörhilfegerät.The present invention relates to a method for operating a hearing aid and a hearing aid.
Hörhilfegeräte erfassen den Umgebungsschall und bieten diesen einem Benutzer komprimiert und verstärkt an. Dabei unterscheidet man zwischen Nutz- und Störsignalen. Das Nutzsignal ist der Schall, den der Benutzer wahrnehmen will. Störsignale sind alle übrigen Schalleindrücke, unabhängig davon, ob sie durch das Hörhilfegerät selbst erzeugt werden (Mikrofonrauschen, Feedback-Pfeifen, akustische Artefakte) oder ob sie Teil der Umgebungssituation sind (Straßenverkehr, Maschinengeräusche, Gespräche von Sprechern, bei denen der Benutzer nicht zuhören möchte).Hearing aids detect ambient sound and provide it compressed and amplified to a user. A distinction is made between useful and interference signals. The useful signal is the sound that the user wants to perceive. Interference signals are all other sound impressions, regardless of whether they are generated by the hearing aid itself (microphone noise, feedback whistles, acoustic artifacts) or if they are part of the environmental situation (traffic, machine sounds, conversations of speakers in which the user does not want to listen ).
Da der Benutzer im Wesentlichen nur die Nutzsignale, nicht jedoch die Störsignale wahrnehmen möchte stellt sich das Problem, die Nutzsignale von den Störsignalen zu unterscheiden, damit die Nutzsignale durch eine entsprechende Signalverarbeitung gegenüber den Störsignalen hervorgehoben werden können.Since the user essentially wants to perceive only the useful signals, but not the interference signals, the problem arises of distinguishing the useful signals from the interference signals, so that the useful signals can be emphasized by a corresponding signal processing with respect to the interference signals.
Zur Lösung dieses Problems gibt es diverse Ansätze: Beispielsweise können zur Unterdrückung des Feedback-Pfeifens Algorithmen zur Feedback-Kompensation, Notch-Filter usw. verwendet werden. Zur Unterdrückung von Störschall aus der Hörumgebung des Benutzers kommen z.B. Störgeräuschunterdrückungsalgorithmen auf Basis des Wiener-Filters zur Anwendung. Die Schwierigkeit bei diesen traditionellen Verfahren besteht darin, dass sie keine eindeutige Identifikation des Störsignals zulassen und somit neben dem Störsignal immer auch einen oft nicht unerheblichen Teil des Nutzsignals reduzieren.To solve this problem, there are various approaches: For example, to suppress the feedback whistle algorithms for feedback compensation, notch filters, etc. can be used. For suppression of background noise from the user's listening environment, for example, noise suppression algorithms based on the Wiener filter are used. The difficulty with these traditional methods is that they do not allow unambiguous identification of the interference signal and thus always reduce not only the interference signal but also an often not inconsiderable part of the useful signal.
Die Offenlegungsschrift
Aus der
Aus der
Aus der
Nachteilig bei den bekannten Hörhilfegeräten mit einer Quellentrennungseinrichtung ist die hohe Rechenleistung, die zum Trennen der Signalquellen erforderlich ist. Dies wirkt sich beispielsweise negativ auf die Laufzeit eines mit einer kleinen Batterie betriebenen Hörhilfegerätes aus.A disadvantage of the known hearing aid devices with a source separation device is the high computing power required to separate the signal sources. This has, for example, a negative effect on the running time of a hearing aid operated with a small battery.
Aus der Offenlegungsschrift
Aufgabe der vorliegenden Erfindung ist es, ein Hörhilfegerätesystem sowie ein Verfahren zum Betrieb eines Hörhilfegerätesystems anzugeben, bei denen eine unterschiedliche Signalverarbeitung von Stör- und Nutzsignalen mit verhältnismäßig wenig Rechenaufwand möglich ist.Object of the present invention is to provide a hearing aid device system and a method for operating a hearing aid device system in which a different signal processing of interfering and useful signals with relatively little computational effort is possible.
Diese Aufgabe wird durch ein Verfahren mit den Verfahrensschritten gemäß Patentanspruch 1 gelöst. Ferner wird die Aufgabe durch ein Hörhilfegerätesystem mit den Merkmalen gemäß Patentanspruch 8 gelöst.This object is achieved by a method with the method steps according to
Bei einem Hörhilfegerät mit mehreren Mikrofonen empfängt jedes der Mikrofone in der Regel ein anderes akustisches Mischsignal, das sich jeweils als Überlagerung der von unterschiedlichen Schallquellen erzeugten akustischen Signale am Ort des jeweiligen Mikrofons ergibt. Jedes der Mikrofone wandelt das in das jeweilige Mikrofon eingehende akustische Mischsignal in ein elektrisches Mischsignal, das dann zum Ausgleich des individuellen Hörverlustes eines Benutzers weiterverarbeitet und verstärkt wird. Daraus resultiert ein elektrisches Ausgangssignal, das ein Ausgangswandler des Hörhilfegerätes, üblicherweise ein Hörer, in ein von dem Benutzer als akustisches Signal wahrnehmbares Ausgangssignal wandelt.In a hearing aid device having a plurality of microphones, each of the microphones generally receives another mixed acoustic signal, which results in each case as a superimposition of the acoustic signals generated by different sound sources at the location of the respective microphone. Each of the microphones converts the mixed acoustic signal entering the respective microphone into an electrical mixed signal, which is then further processed and amplified to compensate for a user's individual hearing loss. This results in an electrical output signal that converts an output transducer of the hearing aid, usually a listener, into an output signal that is perceived by the user as an acoustic signal.
Bei modernen Hörhilfegeräten lässt sich die Signalverarbeitung innerhalb eines Hörhilfegerätes durch eine Vielzahl einstellbarer Parameter-Einstellungen an den individuellen Benutzer oder die Hörsituation, in der sich der Benutzer gerade befindet, anpassen. Dabei ist die Wahl geeigneter Parameter-Einstellungen entscheidend für den Erfolg, den der Benutzer durch die Verwendung des Hörhilfegerätes in Bezug auf eine Verbesserung seines Hörvermögens erfährt. Maßgeblich für diesen Erfolg ist dabei, wie das betreffende Hörhilfegerät Störsignale unterdrückt und Nutzsignale - insbesondere gegenüber den Störsignalen - hervorhebt. Die entsprechenden Parameter-Einstellungen hierfür legen beispielsweise die Übertragungsfunktionen bestimmter Filter fest oder sie bestimmen, ob bestimmte Algorithmen, z.B. zur Störsignalunterdrückung oder zur Sprachsignalanhebung, aktiv sind oder nicht.In modern hearing aid devices, the signal processing within a hearing aid can be adjusted by a variety of adjustable parameter settings to the individual user or the listening situation in which the user is currently located. Here is the choice of suitable parameter settings critical to the user's success in using the hearing aid to improve their hearing. Decisive for this success is how the hearing aid in question suppressed interference signals and payloads - especially against the interference signals - highlights. The corresponding parameter settings for this determine, for example, the transfer functions of certain filters or they determine whether certain algorithms, for example for noise suppression or speech signal increase, are active or not.
Die Grundidee der Erfindung besteht nun darin, nicht wie bisher die quellenspezifischen Empfangssignale wahlweise direkt weiterzuverarbeiten oder zu unterdrücken, sondern die quellenspezifischen Empfangssignale dienen nun dazu, um daraus Parameter zu erzeugen, die eine Hervorhebung bzw. eine Unterdrückung des jeweiligen quellenspezifischen Empfangssignals bewirken, auch dann noch, wenn die quellenspezifischen Empfangsignale nicht direkt in das Ausgangssignal des betreffenden Hörhilfegerätes eingehen.The basic idea of the invention consists in not directly processing or suppressing the source-specific received signals, as is currently the case, but the source-specific received signals are now used to generate parameters which cause an emphasis or a suppression of the respective source-specific received signal, even then even if the source-specific reception signals do not enter directly into the output signal of the hearing aid in question.
Die Erfindung bietet den Vorteil, dass die Erzeugung der quellenspezifischen Empfangsignale nun in einer dem Signalpfad eines Hörhilfegerätes, ausgehend von den Mikrofonen über die Signalverarbeitungseinheit zum Hörer, nebengeordneten Struktur erfolgen kann. Im Unterschied zu dem Signalpfad, in dem die Signalverarbeitung nahezu in Echtzeit erfolgen muss, spielen Zeitverzögerungen in der nebengeordneten Struktur lediglich eine untergeordnete Rolle, da bei der Erfindung das akustische Ausgangssignal während des normalen Betriebes des betreffenden Hörhilfegerätes nicht direkt aus einem oder mehreren quellenspezifischen Empfangssignalen hervorgeht. Die zur Erzeugung der quellenspezifischen Empfangssignale erforderliche Rechenleistung kann damit reduziert werden.The invention offers the advantage that the generation of the source-specific reception signals can now take place in a structure which is ancillary to the signal path of a hearing aid device, starting from the microphones via the signal processing unit to the listener. In contrast to the signal path in which the signal processing must take place almost in real time, time delays in the sibling structure only play a minor role, since in the invention the acoustic output signal does not emerge directly from one or more source-specific received signals during the normal operation of the relevant hearing aid , The computing power required for generating the source-specific received signals can thus be reduced.
Bei einer Weiterbildung der Erfindung erfolgt die rechenaufwendige Erzeugung der quellenspezifischen Empfangssignale nur zeitabschnittsweise und nicht während des gesamten Betriebs eines betreffenden Hörhilfegerätes. Die Separation der unterschiedlichen Schallquellen dient letztendlich insbesondere dazu, bestimmte Charakteristika der Stör- als auch der Nutzsignale zu extrahieren, aufgrund derer die Störsignale unterdrückt bzw. die Nutzsignale hervorgehoben werden können. Wurden derartige Charakteristika festgestellt, so kann zumindest für einen begrenzten Zeitraum, für den die erkannten Störoder Nutzsignale zumindest weitgehend stationär sind, auf die Erzeugung der quellenspezifischen Empfangssignale verzichtet werden. Die für den Betrieb eines Hörhilfegerätes erforderliche Rechenleistung lässt sich dadurch erheblich reduzieren.In a development of the invention, the computation-intensive generation of the source-specific received signals takes place only in sections and not during the entire operation a relevant hearing aid. The separation of the different sound sources ultimately serves in particular to extract certain characteristics of the interfering as well as the useful signals, on the basis of which the interference signals can be suppressed or the useful signals can be emphasized. If such characteristics have been established, the generation of the source-specific received signals can be dispensed with, at least for a limited period of time, for which the detected interferers of the useful signals are at least largely stationary. The required for the operation of a hearing aid computing power can be significantly reduced.
Bei einer vorteilhaften Ausgestaltung der Erfindung umfasst das erfindungsgemäße Hörhilfegerätesystem neben wenigstens einem Hörhilfegerät zusätzlich eine externe Prozessoreinheit. Diese dient vorzugsweise auch zur Fernbedienung eines betreffenden Hörhilfegerätes des Hörhilfegerätesystems. Dabei ist es ferner möglich, dass die rechenaufwendige Erzeugung mehrerer quellenspezifischer Empfangssignale aus den von den Mikrofonen des Hörhilfegerätesystems generierten elektrischen Mischsignalen in der externen Prozessoreinheit erfolgt. Vorteilhaft ist die externe Prozessoreinheit hierfür mit wenigstens zwei Mikrofonen zum Erzeugen elektrischer Mischsignale ausgestattet. Weiterhin vorteilhaft erfolgen dann ebenfalls die Analyse der quellenspezifischen Empfangssignale sowie die Bestimmung von Parameter-Einstellungen für das Hörhilfegerät in der externen Prozessoreinheit. Die dabei ermittelten Parameter-Einstellungen können dann drahtlos von der externen Prozessoreinheit auf das betreffende Hörhilfegerät übertragen werden.In an advantageous embodiment of the invention, the hearing aid device system according to the invention additionally comprises, in addition to at least one hearing aid device, an external processor unit. This preferably also serves for the remote control of a relevant hearing aid device of the hearing aid system. In this case, it is also possible for the computation-intensive generation of a plurality of source-specific received signals to take place from the electrical mixing signals generated by the microphones of the hearing aid system in the external processor unit. Advantageously, the external processor unit is equipped for this purpose with at least two microphones for generating electrical mixed signals. Furthermore, the analysis of the source-specific received signals and the determination of parameter settings for the hearing aid in the external processor unit are also advantageously carried out. The parameter settings determined in this case can then be transmitted wirelessly from the external processor unit to the relevant hearing aid device.
Im Vergleich zum Hörhilfegerät spielen bei der externen Prozessoreinheit die Größe des Gerätes und dessen Stromverbrauch eine untergeordnete Rolle. Um den Bedienkomfort zu erhöhen, kann die externe Prozessoreinheit z.B. mit einem Display und einer Tastatur ausgestattet sein, mit deren Hilfe z.B. die räumliche Verteilung mehrerer Signalquellen im Raum grafisch dargestellt und die Unterscheidung zwischen Stör- und Nutzschallquellen auch unter Berücksichtigung von Benutzereingaben erfolgen kann.In comparison to the hearing aid device, the size of the device and its power consumption play a minor role in the external processor unit. In order to increase the ease of use, the external processor unit can be equipped, for example, with a display and a keyboard, with the help of which, for example, the spatial distribution of several signal sources in space graphically displayed and the distinction between noise and useful sound sources can also be done taking into account user input.
Die Erfindung wird nachfolgend anhand von Ausführungsbeispielen näher erläutert. Es zeigen:
- FIG 1
- ein erstes Hörhilfegerätesystem gemäß der Erfindung
- FIG 2
- ein zweites Hörhilfegerätesystem gemäß der Erfindung und
- FIG 3
- ein Ablaufdiagramm für ein Verfahren zum Betrieb eines Hörhilfegerätesystems gemäß der Erfindung.
- FIG. 1
- a first hearing aid device system according to the invention
- FIG. 2
- a second hearing aid device system according to the invention and
- FIG. 3
- a flowchart for a method for operating a hearing aid system according to the invention.
Das erfindungsgemäße Hörhilfegerätesystem gemäß
Das erfindungsgemäße Hörhilfegerät umfasst in einem zu dem Signalpfad zwischen den Mikrofonen M1 bis Mn und dem Hörer 2 nebengeordneten Signalpfad eine Quellentrennungseinrichtung, insbesondere eine BSS-Einheit 3, zum Erzeugen mehrerer quellenspezifischer Empfangssignale. Im Ausführungsbeispiel mit den beiden Signalquellen S1 und S2 erzeugt die BSS-Einheit 3 ein erstes quellenspezifisches Empfangssignal Q1, das im Wesentlichen aus dem von der Signalquelle S1 abgegebenen akustischen Signal resultiert, und ein zweites quellenspezifisches Empfangssignal Q2, das im Wesentlichen aus dem von der Signalquelle S2 abgegebenen akustischen Signal resultiert. Die quellenspezifischen Empfangssignale Q1, Q2, ..., Qn werden einer Kennzeichnungseinrichtung 6 zugeführt, durch die eine Einteilung der quellenspezifischen Empfangssignale Q1 bis Qn in Stör- oder Nutzsignale erfolgt. Hierfür ist die Kennzeichnungseinrichtung 6 mit einem Bedienelement 7 verbunden, durch die die quellenspezifischen Empfangssignale Q1 bis Qn dem Benutzer nacheinander dargeboten werden können. Es erfolgt dann für jedes einzelne quellenspezifische Empfangssignal eine Kennzeichnung als Stör- oder Nutzsignal durch manuelle Betätigung des Bedienelementes 7 durch den Benutzer. Die so als Stör- oder Nutzsignal klassifizierten quellenspezifischen Empfangssignale werden anschließend einer Analyseeinrichtung 4 zugeführt, in der sie automatisch hinsichtlich bestimmter Charakteristika analysiert werden. Die Signalanalyse in der Signalanalyseeinrichtung 4 kann beispielsweise eine Spektralanalyse, eine Schätzung von Parametern eines statistischen Models, die Wahrscheinlichkeitsdichten der Spektralkomponenten (z.B. Realteil, Imaginärteil und Betrag der Fourier-Koeffizienten) bei unterschiedlichen Frequenzen oder die Einfallsrichtung akustischer Signale in das Mikrofonsystem bestimmen. Nach der Analyse der quellenspezifischen Empfangssignale Q1 bis Qn in der Analyseeinrichtung 4 erfolgt in einer Parameter-Bestimmungseinrichtung 5 die automatische Bestimmung geeigneter Parameter für den Betrieb der Signalverarbeitungseinheit 1 zur Unterdrückung der als Störsignale gekennzeichneten quellenspezifischen Empfangssignale bzw. zur Hervorhebung der als Nutzsignale gekennzeichneten quellenspezifischen Empfangssignale. Die so festgelegten Parameter können sich in vielfältiger Weise auf die Verarbeitung der elektrischen Mischsignale E1 bis En durch die Signalverarbeitungseinheit 1 auswirken. Beispielsweise können die Mikrofone M1 bis Mm in der Signalverarbeitungseinheit 1 elektronisch zu Richtmikrofonen verschaltet sein, wobei die Richtwirkung dann durch die in der Parameter-Bestimmungseinrichtung 5 bestimmten Parameter beeinflusst wird. Weiterhin können durch die Parameter beispielsweise Störgeräuschbefreiungsalgorithmen ein- oder ausgeschaltet oder in ihrer Funktionsweise verändert werden. Ferner können damit bestimmte Filter-Parameter eingestellt werden, die beispielsweise bestimmte Frequenzbänder gegenüber anderen hervorheben bzw. unterdrücken. Zusätzlich können beispielsweise auf der Analyse der Stör- oder Nutzsignale basierende Parameter die Wirkungsweise eines MMSE-(Minimum Mean Square Error-) Algorithmus oder eines Ephraim-Malah-Algorithmus mit nichtgauß'scher Verteilung beeinflussen. Darüber hinaus ist es möglich, dass in der Parameter-Bestimmungseinrichtung 5 ermittelte Parameter einen Algorithmus zur Restauration eines Sprachsignals steuern, bei dem ein bestimmter Frequenzbereich fehlt oder gestört ist und bei dem dieser Frequenzbereich aus ungestörten Frequenzbereichen synthetisiert wird.The hearing aid according to the invention comprises in one to the signal path between the microphones M1 to Mn and the handset. 2 sibling signal path, a source separation device, in particular a
Die aufgezeigten Beispiele geben ohne Beschränkung der Allgemeinheit nur einen kleinen Ausschnitt möglicher Filter, Algorithmen oder Funktionen des Hörhilfegerätes wieder, die durch Parameter, die aus einer Analyse der quellenspezifischen Empfangssignale hervorgehen, beeinflusst oder gesteuert werden.The examples shown give, without limiting the generality, only a small selection of possible filters, algorithms or functions of the hearing aid that are influenced or controlled by parameters resulting from an analysis of the source-specific received signals.
Die ermittelten Parameter-Einstellungen haben direkten Einfluss auf die Signalverarbeitung in dem Signalpfad zwischen den Mikrofonen M1, M2, ..., Mn und dem Hörer 2, derart, dass wenigstens ein Störsignal unterdrückt bzw. wenigstens ein Nutzsignal hervorgehoben wird. Sie haben in der Regel jedoch keinen direkten Einfluss auf die quellenspezifischen Empfangssignale Q1, Q2, ..., Qm. Nach deren Bestimmung beeinflussen die so ermittelten Parameter-Einstellungen die Signalverarbeitung so lange, bis eine Neuberechnung erfolgt. Diese kann beispielsweise manuell durch den Benutzer ausgelöst werden. Die Erzeugung quellenspezifischer Empfangssignale Q1, Q2, ..., Qm durch das Hörhilfegerät ist für die Zeitdauer nach einer Parameter-Bestimmung bis zu dem Zeitpunkt, bei dem eine Neuberechnung der Parameter-Einstellungen ausgelöst wird, nicht erforderlich. Vorteilhaft unterbleibt daher für diesen Zeitraum während des normalen Betriebes des Hörhilfegerätes die rechenaufwendige Erzeugung der quellenspezifischen Empfangssignale Q1, Q2, ..., Qm. Diese werden bei dem Hörhilfegerät gemäß dem Ausführungsbeispiel nur für die Einteilung in Stör- und Nutzsignale sowie zur Bestimmung der Parameter zu deren Unterdrückung bzw. Hervorhebung benötigt, nicht jedoch für den normalen Betrieb des Hörhilfegerätes, in dem diese Parameter-Einstellungen dann wirksam sind.The determined parameter settings have a direct influence on the signal processing in the signal path between the microphones M1, M2,..., Mn and the
Mit der Erfindung ist der Vorteil verbunden, dass die rechenaufwendige Ermittlung der quellenspezifischen Empfangssignale, die Analyse derselben und die darauf basierende Bestimmung von Parametern nur zeitabschnittsweise erfolgen müssen. Solange die äußere Situation im Wesentlichen stationär bleibt (sich beispielsweise die Frequenz eines als Störsignal klassifizierten Eingangssignals nicht ändert) ist eine Anpassung einmal ermittelter Parameter-Einstellungen nicht erforderlich. Der Betrieb der Quellentrennungseinrichtung 3, der Analyseeinrichtung 4 sowie der Parameter-Bestimmungseinrichtung 5 kann demnach zeitabschnittweise während des Betriebes des Hörhilfegerätes unterbleiben. Die Neuberechnung entsprechender Parameter erfolgt dann beispielsweise nach dem Einschalten des Hörhilfegerätes, nach einer Programmumschaltung, nach einer automatisch festgestellten Änderung der Hörumgebung oder nach Anforderung durch eine entsprechende manuelle Benutzereingabe.The invention has the advantage that the computation-intensive determination of the source-specific received signals, the analysis of the same and the determination of parameters based thereon need only be performed on a periodic basis. As long as the external situation remains substantially stationary (for example, the frequency of an input signal classified as a noise signal does not change) it is not necessary to adapt once determined parameter settings. The operation of the
Ein weiterer Vorteil der Erfindung ergibt sich dadurch, dass die quellenspezifischen Empfangssignale auch nicht in Echtzeit erzeugt werden müssen. Dies wäre nur dann der Fall, wenn das akustische Ausgangssignal des betreffenden Hörhilfegerätes direkt aus einem oder mehreren quellenspezifischen Empfangssignalen hervorginge. Da letzteres bei der Erfindung jedoch gerade nicht der Fall ist, spielt eine Zeitverzögerung beim Erzeugen der quellenspezifischen Empfangssignale lediglich eine untergeordnete Rolle.A further advantage of the invention results from the fact that the source-specific received signals also do not have to be generated in real time. This would only be the case if the acoustic output signal of the relevant hearing aid device emerged directly from one or more source-specific received signals. However, the latter in the invention is not the case, plays a time delay in generating the source-specific received signals only a minor role.
Weiterhin vorteilhaft können im Zusammenhang mit der Erfindung die quellenspezifischen Empfangssignale Q1, Q2, ..., Qm auch zeitlich aufeinanderfolgend ermittelt und anschließend dem Benutzer dargeboten werden. Damit muss zu jeder Zeit nur ein quellenspezifisches Empfangssignal bestimmt werden. Auch dies trägt zur Reduzierung der erforderlichen Rechenleistung gegenüber einem herkömmlichen Hörhilfegerät mit einer Quellentrennungseinrichtung bei.Furthermore, in accordance with the invention, the source-specific received signals Q1, Q2,..., Qm can also be advantageously determined in chronological succession and subsequently presented to the user. Thus, only one source-specific received signal must be determined at any time. This also contributes to the reduction of the required computing power compared to a conventional hearing aid device with a source separation device.
In Abweichung von dem dargestellten Ausführungsbeispiel sieht eine alternative Ausführungsform (nicht dargestellt) die Anordnung der Analyseeinrichtung 4 gemäß
Eine weitere Ausführungsform der Erfindung zeigt das Ausführungsbeispiel gemäß
Neben dem Hörhilfegerät 10 umfasst das Hörhilfegerätesystem in dem Ausführungsbeispiel gemäß
Ähnlich wie bei dem Ausführungsbeispiel gemäß
Nach erfolgter Einteilung in Stör- oder Nutzsignale werden die quellenspezifischen Empfangssignale hinsichtlich des Vorhandenseins bestimmter Charakteristika analysiert. Hierzu zählen insbesondere die Einfallsrichtung der von den jeweiligen Schallquellen erzeugten akustischen Signale in die externe Prozessoreinheit 20, das Frequenzspektrum der Signale, evtl. darin vorhandene Modulationsfrequenzen usw. Anhand der so ermittelten charakteristischen Eigenschaften der quellenspezifischen Empfangssignale erfolgt dann in der Parameter-Bestimmungseinrichtung 15 die Bestimmung geeigneter Parameter für den Betrieb der Signalverarbeitungseinheit 11 des Hörhilfegerätes 10. Diese Parameter-Einstellungen betreffen insbesondere die Wirkungsweise (Richtwirkung) des Mikrofonsystems des Hörhilfegerätes 10 oder die Wirkungsweise bestimmter Filter und Algorithmen. Damit die ermittelten Parameter-Einstellungen wirksam werden können, müssen diese von der externen Prozessoreinheit 20 auf das Hörhilfegerät 10 übertragen werden. Hierfür umfasst sowohl das Hörhilfegerät 10 als auch die externe Prozessoreinheit 20 jeweils eine Sende- und Empfangseinheit 18 bzw. 19. Ferner umfasst die externe Prozessoreinheit 20 einen Controller 21, der Abläufe und Zustände innerhalb der externen Prozessoreinheit 20 steuert bzw. überwacht.After classification into interfering or useful signals, the source-specific received signals are analyzed for the presence of certain characteristics. These include in particular the direction of incidence of the acoustic signals generated by the respective sound sources in the
Wie bei dem Hörhilfegerät nach dem Ausführungsbeispiel gemäß
Zur weiteren Verdeutlichung der Erfindung werden die wesentlichen Verfahrensschritte bei einem erfindungsgemäßen Verfahren zum Betrieb eines Hörhilfegerätesystems in Verbindung mit
Claims (13)
- Method for operating a hearing aid system comprising at least one hearing aid, having the following steps:- receiving a plurality of acoustic mixed signals from a plurality of sound sources and converting said signals into electrical mixed signals,- processing at least one of the electrical mixed signals as a function of at least one parameter setting and generating an electrical output signal,- converting the electrical output signal into an output signal which can be perceived by a user as an acoustic output signal,- generating a plurality of source-specific reception signals from the electrical mixed signals,- analyzing the source-specific reception signals,- determining the parameter setting as a function of a result of the analysis,- wherein the source-specific reception signals are not directly included in the electrical output signal.
- Method according to Claim 1, wherein the source-specific reception signals are respectively characterized as an interference signal or as a useful signal.
- Method according to Claim 2, wherein the characterization is effected in consideration of user inputs.
- Method according to one of Claims 1 to 3, wherein the parameter setting effects the reduction of an interference signal.
- Method according to one of Claims 1 to 4, wherein the parameter setting effects the accentuation of a useful signal.
- Method according to one of Claims 1 to 5, wherein the generation of the source-specific reception signals from the electrical mixed signals is not effected in real time.
- Method according to one of Claims 1 to 6, wherein, after determining the parameter setting for at least one period, the signal processing is effected as a function of the determined parameter setting and the generation and analysis of the source-specific reception signals ceases.
- Hearing aid system comprising at least- a hearing aid,- two microphones (M1, M2, ..., Mn; M1' , M2', ..., Mn') for receiving a plurality of acoustic mixed signals from a plurality of sound sources (S1, S2; S1', S2') and for converting the acoustic mixed signals into electrical mixed signals (E1, E2, ..., En; E1', E2', ..., En'),- a signal processing unit (1; 11) for processing at least one of the electrical mixed signals (E1, E2, ..., En; E1', E2', ..., En') as a function of at least one parameter setting and for generating an electrical output signal,- an earpiece (2; 12) for converting the electrical output signal into an output signal which can be perceived by a user as an acoustic output signal,- a source separation device (3; 13) for generating a plurality of source-specific reception signals (Q1, Q2, ..., Qm; Q1', Q2', ..., Qm'),- an analysis device (4; 14) for analyzing the source-specific reception signals (Q1, Q2, ..., Qm; Q1', Q2', ..., Qm'),- a parameter determination device (5; 15) for determining the parameter setting for the signal processing unit (1; 11) as a function of a result of the analysis,- wherein the signal processing unit (1; 11) is designed in such a way that the source-specific reception signals are not directly included in the electrical output signal.
- Hearing aid system according to Claim 8, wherein the source-specific reception signals (Q1, Q2, ..., Qm; Q1', Q2', ..., Qm') or signals resulting therefrom can be supplied to the user in succession and the hearing aid system comprises a characterization device (6, 16) for characterizing the respective source-specific reception signal (Q1, Q2, ..., Qm; Q1', Q2', ..., Qm') as an interference signal or as a useful signal by the user.
- Hearing aid system according to Claim 9, wherein the characterization device (6; 16) is designed for the automatic characterization of the source-specific reception signals (Q1, Q2, ..., Qm; Q1', Q2', ..., Qm') as an interference signal or as a useful signal.
- Hearing aid system according to one of Claims 8 to 10, wherein the source separation device (3; 13) and the parameter determination device (5; 15) can be operated periodically during the operation of the hearing aid system and the signal processing is effected as a function of the parameter setting, at least also in a period during which the generation of source-specific reception signals ceases.
- Hearing aid system according to one of Claims 8 to 11, wherein the hearing aid comprises the microphones (M1, M2, ..., Mn), the signal processing unit (1), the earpiece (2), the source separation device (3), the analysis device (4) and the parameter determination device (5), wherein there are at least two signal pick-up points in a signal path between the microphones (M1, M2, ..., Mn) and the earpiece (2) for generating two pick-up signals and wherein the pick-up signals are fed to the source separation device (3) for generating the source-specific reception signals (Q1, Q2, ..., Qm) from the pick-up signals.
- Hearing aid system according to one of Claims 8 to 11, comprising at least one external processor unit (20) in which the source separation device (13) and the analysis device (14) are arranged.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102008062587 | 2008-12-16 |
Publications (2)
Publication Number | Publication Date |
---|---|
EP2200341A1 EP2200341A1 (en) | 2010-06-23 |
EP2200341B1 true EP2200341B1 (en) | 2015-02-25 |
Family
ID=42025776
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP09175951.4A Active EP2200341B1 (en) | 2008-12-16 | 2009-11-13 | Method for operating a hearing aid and hearing aid with a source separation device |
Country Status (3)
Country | Link |
---|---|
US (1) | US20100158289A1 (en) |
EP (1) | EP2200341B1 (en) |
DK (1) | DK2200341T3 (en) |
Families Citing this family (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE102010026381A1 (en) * | 2010-07-07 | 2012-01-12 | Siemens Medical Instruments Pte. Ltd. | Method for locating an audio source and multichannel hearing system |
DE102012214081A1 (en) | 2012-06-06 | 2013-12-12 | Siemens Medical Instruments Pte. Ltd. | Method of focusing a hearing instrument beamformer |
US9414170B2 (en) * | 2012-12-28 | 2016-08-09 | Gn Resound A/S | Hearing aid having an adaptive antenna matching mechanism and a method for adaptively matching a hearing aid antenna |
CN107113486A (en) * | 2014-10-30 | 2017-08-29 | 索尼公司 | Audio output device |
DE102016225205A1 (en) * | 2016-12-15 | 2018-06-21 | Sivantos Pte. Ltd. | Method for determining a direction of a useful signal source |
WO2019084214A1 (en) * | 2017-10-24 | 2019-05-02 | Whisper.Ai, Inc. | Separating and recombining audio for intelligibility and comfort |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1912472A1 (en) * | 2006-10-10 | 2008-04-16 | Siemens Audiologische Technik GmbH | Method for operating a hearing aid and hearing aid |
Family Cites Families (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE10114015C2 (en) | 2001-03-22 | 2003-02-27 | Siemens Audiologische Technik | Method for operating a hearing aid and / or hearing protection device and hearing aid and / or hearing protection device |
DE10313331B4 (en) * | 2003-03-25 | 2005-06-16 | Siemens Audiologische Technik Gmbh | Method for determining an incident direction of a signal of an acoustic signal source and apparatus for carrying out the method |
ATE324763T1 (en) * | 2003-08-21 | 2006-05-15 | Bernafon Ag | METHOD FOR PROCESSING AUDIO SIGNALS |
DE10356093B3 (en) * | 2003-12-01 | 2005-06-02 | Siemens Audiologische Technik Gmbh | Hearing aid with adaptive signal processing of received sound waves dependent on identified signal source direction and signal classification |
US7464029B2 (en) * | 2005-07-22 | 2008-12-09 | Qualcomm Incorporated | Robust separation of speech signals in a noisy environment |
DE102006018634B4 (en) * | 2006-04-21 | 2017-12-07 | Sivantos Gmbh | Hearing aid with source separation and corresponding method |
DE102006020832B4 (en) | 2006-05-04 | 2016-10-27 | Sivantos Gmbh | Method for suppressing feedback in hearing devices |
WO2008043758A1 (en) * | 2006-10-10 | 2008-04-17 | Siemens Audiologische Technik Gmbh | Method for operating a hearing aid, and hearing aid |
DE102006047983A1 (en) * | 2006-10-10 | 2008-04-24 | Siemens Audiologische Technik Gmbh | Processing an input signal in a hearing aid |
-
2009
- 2009-11-13 DK DK09175951.4T patent/DK2200341T3/en active
- 2009-11-13 EP EP09175951.4A patent/EP2200341B1/en active Active
- 2009-12-16 US US12/639,352 patent/US20100158289A1/en not_active Abandoned
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1912472A1 (en) * | 2006-10-10 | 2008-04-16 | Siemens Audiologische Technik GmbH | Method for operating a hearing aid and hearing aid |
Also Published As
Publication number | Publication date |
---|---|
EP2200341A1 (en) | 2010-06-23 |
DK2200341T3 (en) | 2015-06-01 |
US20100158289A1 (en) | 2010-06-24 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1379102B1 (en) | Sound localization in binaural hearing aids | |
EP1360870B1 (en) | Method for operating a hearing aid system and hearing aid system | |
EP3451705B1 (en) | Method and apparatus for the rapid detection of own voice | |
EP1307072B1 (en) | Method for operating a hearing aid and hearing aid | |
EP2200341B1 (en) | Method for operating a hearing aid and hearing aid with a source separation device | |
DE102011087984A1 (en) | Hearing apparatus with speaker activity recognition and method for operating a hearing apparatus | |
WO2001020965A2 (en) | Method for determining a current acoustic environment, use of said method and a hearing-aid | |
DE102006047965A1 (en) | Method for the reduction of occlusion effects with acoustic device locking an auditory passage, involves using signal from transmission path of audio signal, and transmission function is observed by output of output converter | |
DE102009012166B4 (en) | Hearing apparatus and method for reducing a noise for a hearing device | |
EP1456839A2 (en) | Method and device for the suppression of periodic interference signals | |
EP3454572A1 (en) | Method for detection of a defect in a listening instrument | |
DE102008046040B4 (en) | Method for operating a hearing device with directivity and associated hearing device | |
WO2001047335A2 (en) | Method for the elimination of noise signal components in an input signal for an auditory system, use of said method and a hearing aid | |
EP1503612A2 (en) | Hearing aid and method for operating a hearing aid with a microphone system in which different directional characteristics are selectable | |
DE10114101A1 (en) | Processing input signal in signal processing unit for hearing aid, involves analyzing input signal and adapting signal processing unit setting parameters depending on signal analysis results | |
DE102018207346B4 (en) | Method for operating a hearing device and hearing aid | |
EP1926087A1 (en) | Adjustment of a hearing device to a speech signal | |
EP2658289B1 (en) | Method for controlling an alignment characteristic and hearing aid | |
DE10114015C2 (en) | Method for operating a hearing aid and / or hearing protection device and hearing aid and / or hearing protection device | |
DE102006029268B4 (en) | Hearing device with structure-borne noise detection device and corresponding method | |
DE102019201879B3 (en) | Method for operating a hearing system and hearing system | |
EP3534624B1 (en) | Method for operating a hearing aid | |
EP1909535A2 (en) | Hearing device with controlled input channels and corresponding method | |
EP1359437A1 (en) | Method for determining a position of a user of a communication terminal | |
WO2024104945A1 (en) | Method for operating a hearing aid, and hearing aid |
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 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR |
|
AX | Request for extension of the european patent |
Extension state: AL BA RS |
|
17P | Request for examination filed |
Effective date: 20101223 |
|
17Q | First examination report despatched |
Effective date: 20110120 |
|
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 20060101AFI20140826BHEP |
|
INTG | Intention to grant announced |
Effective date: 20140918 |
|
GRAS | Grant fee paid |
Free format text: ORIGINAL CODE: EPIDOSNIGR3 |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR |
|
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: NV Representative=s name: SIEMENS SCHWEIZ AG, CH Ref country code: CH Ref legal event code: EP |
|
REG | Reference to a national code |
Ref country code: IE Ref legal event code: FG4D Free format text: LANGUAGE OF EP DOCUMENT: GERMAN |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R096 Ref document number: 502009010651 Country of ref document: DE Effective date: 20150409 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R082 Ref document number: 502009010651 Country of ref document: DE Representative=s name: FDST PATENTANWAELTE FREIER DOERR STAMMLER TSCH, DE |
|
REG | Reference to a national code |
Ref country code: AT Ref legal event code: REF Ref document number: 712874 Country of ref document: AT Kind code of ref document: T Effective date: 20150415 |
|
REG | Reference to a national code |
Ref country code: DK Ref legal event code: T3 Effective date: 20150527 |
|
REG | Reference to a national code |
Ref country code: NL Ref legal event code: VDEP Effective date: 20150225 |
|
REG | Reference to a national code |
Ref country code: LT Ref legal event code: MG4D |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: LT Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: HR Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: FI Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: NO Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150525 Ref country code: ES Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: SE Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: IS Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150625 Ref country code: GR Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150526 Ref country code: LV Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: NL Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R082 Ref document number: 502009010651 Country of ref document: DE Representative=s name: FDST PATENTANWAELTE FREIER DOERR STAMMLER TSCH, DE Ref country code: DE Ref legal event code: R081 Ref document number: 502009010651 Country of ref document: DE Owner name: SIVANTOS GMBH, DE Free format text: FORMER OWNER: SIEMENS AUDIOLOGISCHE TECHNIK GMBH, 91058 ERLANGEN, DE |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: RO Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: SK Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: CZ Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: EE Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
RAP2 | Party data changed (patent owner data changed or rights of a patent transferred) |
Owner name: SIVANTOS GMBH |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 7 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R097 Ref document number: 502009010651 Country of ref document: DE |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: PL Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: IT Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PLBE | No opposition filed within time limit |
Free format text: ORIGINAL CODE: 0009261 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT |
|
26N | No opposition filed |
Effective date: 20151126 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: SI Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: LU Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20151113 Ref country code: MC Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
REG | Reference to a national code |
Ref country code: IE Ref legal event code: MM4A |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: IE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20151113 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 8 |
|
REG | Reference to a national code |
Ref country code: AT Ref legal event code: MM01 Ref document number: 712874 Country of ref document: AT Kind code of ref document: T Effective date: 20151113 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: AT Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20151113 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: HU Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT; INVALID AB INITIO Effective date: 20091113 Ref country code: BG Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: SM Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: CY Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: BE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20151130 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: TR Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: MT Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: PLFP Year of fee payment: 9 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: PT Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 Ref country code: MK Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 20150225 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GB Payment date: 20231123 Year of fee payment: 15 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: FR Payment date: 20231123 Year of fee payment: 15 Ref country code: DK Payment date: 20231122 Year of fee payment: 15 Ref country code: DE Payment date: 20231120 Year of fee payment: 15 Ref country code: CH Payment date: 20231202 Year of fee payment: 15 |