EP1052881B1 - Prothèse acoustique avec détecteur d'oscillations et méthode de détection d'oscillations dans une prothèse acoustique - Google Patents

Prothèse acoustique avec détecteur d'oscillations et méthode de détection d'oscillations dans une prothèse acoustique Download PDF

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Publication number
EP1052881B1
EP1052881B1 EP00109229A EP00109229A EP1052881B1 EP 1052881 B1 EP1052881 B1 EP 1052881B1 EP 00109229 A EP00109229 A EP 00109229A EP 00109229 A EP00109229 A EP 00109229A EP 1052881 B1 EP1052881 B1 EP 1052881B1
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EP
European Patent Office
Prior art keywords
hearing aid
feedback
oscillation
microphone
detected
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
Application number
EP00109229A
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German (de)
English (en)
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EP1052881A2 (fr
EP1052881A3 (fr
Inventor
Volkmar Dipl.-Ing. Hamacher
Georg-Erwin Dipl.-Ing. Arndt
Tom Dipl.-Ing. Weidner (FH)
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Sivantos GmbH
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Siemens Audiologische Technik GmbH
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Filing date
Publication date
Priority claimed from DE1999122133 external-priority patent/DE19922133C2/de
Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1052881A2 publication Critical patent/EP1052881A2/fr
Publication of EP1052881A3 publication Critical patent/EP1052881A3/fr
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Publication of EP1052881B1 publication Critical patent/EP1052881B1/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

  • the invention relates to a hearing aid with an oscillation detector and a method for detecting oscillation in a hearing aid.
  • a feedback suppression is known in a hearing aid, in which the occurrence of feedback is determined. If feedback is detected, the gain is reduced in at least one frequency band and left unchanged in all other frequency bands. Finally, to set the hearing aid, a set of appropriate parameters is generated and stored.
  • a disadvantage of this feedback suppression is that while the occurrence of feedback only during the adaptation of the hearing aid is detected and feedback during normal operation of the hearing aid not recognized and eliminated.
  • Maxwell / Zurek "Reducing Acoustic Feedback in Hearing Aids” (IEEE TRANSACTION ON SPEECH AND AUDIO PROCESSING, VOL. 3, NO 4, July 1995 ) uses an adaptive filter whose frequency response always corresponds to the inverted signal frequency response. If the input signal has strong tonal components, a kind of blocking filter is formed whose blocking band lies on the largest frequency component of the microphone signal. When the energy of the microphone signal in the stopband exceeds a threshold, the output is the output of the notch filter. Otherwise, the microphone signal will remain unchanged. There is thus no reliable feedback detection. This signal processing not only reduces any feedback but generally all the dominant spectral components of the input signal. Therefore, voice signals having a pronounced frequency structure are also attacked. As reported in Maxwell / Zurek, this leads to a significant deterioration of the sound quality.
  • the invention has for its object to provide a hearing aid with an oscillation detector and a method for detecting oscillations, which can be realized with little circuit complexity in a hearing aid.
  • a separate hearing aid device e.g. BTE or ITE device, or an implantable hearing aid understood.
  • the hearing aid according to the invention is characterized by a particularly simple design of the oscillation detector, which requires only small space and can be realized with a low circuit complexity.
  • the oscillation detector of the hearing aid comprises a period measuring element for determining the respective number of digitized samples of successive periods of an input signal of the microphone of the hearing aid.
  • the input signal is digitized by an A / D converter, which can be connected upstream of the oscillation detector or integrated into it.
  • the output values of the period measuring element undergo downstream averaging elements to determine a long-term average and a short-term average, which are respectively related to a longer and a shorter time period.
  • the hearing aid according to the invention thus takes into account that oscillations to be detected usually occur in the form of sinusoidal input signals and that in such sinusoidal input signals of the long-term and short-term average of the number of digitized samples in successive signal periods is substantially identical. As a result, sinusoidal signals can be distinguished from non-sinusoidal input signals.
  • the averaging elements of the hearing aid device according to the invention can be designed as low-pass filters.
  • first-order low-pass filters are used, a low-pass filter having a longer time constant for determining the long-term average value and a further low-pass filter having a shorter time constant for determining the short-time average value.
  • the oscillation detector has an amount element to cause a sign correction of the difference between the long-term and the short-term average, so that all the evaluation values with positive signs are present. This allows a comparison with a likewise positive threshold, without having to monitor a threshold range with both negative and positive values.
  • the oscillation detector has another averaging element, e.g. another low-pass filter to even out and smooth out the difference between the long-term and the short-term mean value as determined in the predicate.
  • another averaging element e.g. another low-pass filter to even out and smooth out the difference between the long-term and the short-term mean value as determined in the predicate.
  • the comparison element of the oscillation detector used for this purpose advantageously has an adjustable threshold value in order to be able to regulate the sensitivity of the oscillation detector.
  • the threshold value can either be set manually or adjusted automatically depending on detected ambient or noise situations.
  • An object of the method according to the invention for detecting oscillation is to detect substantially sinusoidal input signals of the microphone, since in the presence of such signals usually oscillation and thus present feedback is assumed.
  • the number of digitized samples in successive periods of the input signal of the microphone is determined. Now it is a question of determining whether the number of sampled values obtained in successive periods changes or is substantially identical. For this purpose, a long-term average value N L and a short-term average value N K of the number of sampled values determined are formed.
  • the method according to the invention makes it possible to detect the presence of substantially sinusoidal signals and thus of oscillation with a small number of process steps which are simple to implement in terms of circuitry.
  • a filter element When oscillation is detected, a filter element is set to the appropriate notch frequency and activated to reduce frequency-specific (narrow-band) gain and to suppress the feedback effect. This ensures that a gain reduction is set only when in fact a feedback effect to be suppressed occurs. Furthermore, the interference suppression by the activated filter element concentrates only on that frequency or that frequency range in which the feedback actually occurs. The remaining frequency ranges of the signal to be processed are not reduced in their gain.
  • the hearing aid device With the oscillation detector, it is also possible for the hearing aid device according to the invention to detect fluctuating feedback effects over time and to determine the respective frequency suitable for suppression and via activation of the filter element. This also allows changing feedback situations to be detected and remedied.
  • the hearing aid device can have a plurality of filter elements (notch filters, for example notch filters). If it is determined upon activation of a first filter element that the feedback effects persist, thus further filter elements can be activated in order to achieve a gain reduction at the respective further frequencies.
  • filter elements notch filters, for example notch filters
  • a general adjustability of the filter characteristic of the filter elements makes it possible, after a determination of the respective feedback effect by the oscillation detector not only the frequency range of the gain reduction, but also other suitable countermeasures (eg "width” and " Depth "of the notch effect of the notch filter).
  • suitable countermeasures eg "width” and " Depth "of the notch effect of the notch filter.
  • the reliability of the oscillation detector is increased when the level of the output signal is detected by a level measuring unit and feedback is detected only when an adjustable level threshold is exceeded.
  • the oscillation detector, the filter elements and / or level measuring unit connected can be controlled and activated.
  • the control unit upon detection of feedback conditions activation of the filter element takes place by the oscillation detector only when a signal level detected by the level measuring unit and above an adjustable threshold value is present.
  • the control unit may also be programmable and take on further functions of the signal analysis of the signal to be processed, so that e.g. due to the signal analysis, a suitable threshold value is set in the level measuring unit and this is changed if necessary.
  • the desired frequency-specific gain reduction is realized in the signal processing path. Then, when the goal of feedback suppression is achieved, no feedback effect can be detected.
  • the filter elements are activated only for an adjustable period of time and then turned off again. Thereupon it can be determined by the oscillation detector whether the initially determined feedback is still present and, if necessary, a new filter activation takes place. By a time-limited filter activation is avoided that the filters remain turned on, although due to changing environmental conditions, the causes of the feedback effect are eliminated.
  • a time-controlled activation of the filter elements can take place via a time switching element, which can also be integrated in the control.
  • a method for operating a hearing aid it is first determined for feedback detection, whether an oscillating microphone signal is present and then - if this is the case - set a corresponding frequency-specific gain reduction of the processed microphone signal. Occurring feedback effects are suppressed frequency-specific and narrow-band, without other frequency ranges of the microphone signal to be processed are touched.
  • the method according to the invention enables a targeted feedback suppression, which is particularly convenient for the user, since the usual amplification potential is retained in all frequency ranges which are not affected.
  • the method it is continuously determined whether a feedback occurs and then respectively suitable measures for frequency-specific gain reduction are taken, which adapt continuously in time to changes in the determined feedback effects.
  • suitable dynamic gain reduction measures By constantly monitoring the sound situation, changes in feedback effects are also detected, and it is possible to react accordingly by means of suitable dynamic gain reduction measures, so that precisely the respective detected feedback is always suppressed and changes and an omission of the feedback effects are taken into account.
  • a further method step it can be determined whether the output signal exceeds a certain level threshold value. This takes into account the large increase in signal levels occurring in a feedback situation.
  • the method is additionally queried whether the signal level of the sinusoidal signal is above a certain threshold value. Only when an oscillating signal and an increased level are cumulative, a feedback is actually detected.
  • a sinusoidal largely monofrequent input signal can also be present without a feedback situation.
  • the respective measure for the suppression of the feedback can be adapted in an optimized manner and, by activating a suitable filter characteristic, an adaptation of e.g. the position and the size of the notch frequency range and the degree of gain reduction, a further improved feedback suppression can be achieved.
  • the gain reduction takes place only for a certain period of time and then is canceled on its own, in order to take back and switch off the originally set gain reductions with changes in the sound situation and an omission of the originally detected feedback effect.
  • a renewed activation of filter measures for gain reduction can again be set.
  • the operation of the oscillation detector 4 follows from the block diagram FIG. 1 out.
  • An input signal 11 from the microphone 1 Is first digitized in the A / D converter 10 at a sampling rate f S.
  • the A / D converter 10 may be integrated in or connected to the oscillation detector 4.
  • Such a period measurement in the period measuring element 5 may e.g. by detecting and analyzing the zero crossings of the digitized samples. Thus, a change of sign and also the direction of the sign change (from + to - or vice versa) can be detected. Overall, therefore, the beginning and the end of a period of the input signal 11 (period) can be determined and the number of digital samples between the beginning and the end of the period can be determined.
  • Averaging elements downstream of the period measuring element 5, namely the low-pass filters 6, 7, are used to determine the long-term average value N L and the short-term average value N K of the number of sampling values determined by the period measuring element in the respective signal periods of the input signal 11.
  • x represents the input value (ie the number of sampled values determined per period) and y the respective output value (ie N L or N K ) of the processing instruction, in each case provided with the indices t for the respective sampling time interval.
  • difference element 12 a difference between N L and N K is formed, which is advantageously sign-corrected in magnitude element 13, so that only positive values occur.
  • another smoothing by another averaging element, here also for example a first order low-pass filter 14, also takes place.
  • the comparison element 8 the magnitude of the difference between N L and N K is judged. If it is below a certain adjustable threshold value, it is assumed that a substantially sinusoidal input signal 11 is present and thus the presence of oscillation can be assumed.
  • the oscillation frequency 16 (f OSZ ) is now determined in the frequency determiner 15, specifically as the product of the sampling rate f S with the reciprocal of the long-term mean value N L.
  • oscillation frequency f OSZ 4 kHz is present.
  • This oscillation frequency f OSZ can be passed from the oscillation detector 4 to a control element 20, so that suitable filter elements 17, 18, 19 can be activated in order to suppress the detected oscillation, for example by filters with notch effect (cf. FIG. 2 ).
  • a hearing aid with at least one microphone 1, a signal processing device 2 with means for signal processing and a handset 3, wherein in the signal processing path between the microphone 1 and the handset 3 filter elements 17, 18, 19 are provided for frequency-specific gain reduction.
  • the filter elements 17, 18, 19 mentioned are set to a determined blocking frequency and activated if oscillating signals are detected by the oscillation detector 4 and thus a feedback is analyzed as present.
  • the control element 20 is informed of the level of the output signal. Feedback is detected by the control element 20 only if the presence of an oscillating signal is registered by the oscillation detector 4 and at the same time a level of the output signal, ie the processed microphone signal, exceeding the determined threshold value of the level measuring element 21 is detected by the level measuring element 21.
  • the filter elements 17, 18 and 19 are not only activated, but also adjusted according to their filter characteristics (e.g., position and magnitude of the notch frequency range, degree of gain reduction).
  • the control may be programmable and e.g. initially set the usual basic parameters of filter characteristics, then - if the feedback is not sufficiently suppressed - make a corresponding adjustment of the filter characteristics after a specified or self-learning program flow.
  • An analysis or typing of the feedback detected by the oscillation detector 4 can also take place via the control element 20 and can be used to determine or determine the filter characteristic of the filter elements 17, 18 and 19.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)
  • Control Of Amplification And Gain Control (AREA)

Claims (23)

  1. Prothèse auditive comprenant un microphone, un dispositif de traitement du signal et un écouteur,
    caractérisée en ce qu'un détecteur ( 4 ) d'oscillation est prévu pour constater des réactions acoustiques et le détecteur ( 4 ) d'oscillation comporte
    - un élément ( 5 ) de mesure de périodes, pour déterminer le nombre respectif de valeurs numériques d'échantillonnage dans des périodes successives d'un signal ( 11 ) d'entrée du microphone ( 1 ),
    - des éléments ( 6, 7 ) pour faire une moyenne afin de déterminer une valeur moyenne NL de temps longue et une valeur NK moyenne de temps court du nombre de valeurs d'échantillonnage déterminé par l'élément ( 5 ) de mesure de périodes,
    - un élément ( 12 ) de différence, pour former la différence entre NL et NK,
    - un élément ( 3 ) de valeur absolue pour la correction du signe de la différence de NL et de NK,
    - un autre élément ( 14 ) pour faire une moyenne afin de lisser la valeur de différence de NL et de NK et
    - un élément ( 8 ) de comparaison pour la comparaison de NL et de NK.
  2. Prothèse auditive suivant la revendication 1,
    caractérisée en ce que le détecteur ( 4 ) d'oscillation comporte un convertisseur ( 10 ) A/N, pour la détermination de valeurs numérisées d'échantillonnage, à partir du signal ( 11 ) analogique d'entrée du microphone ( 1 ).
  3. Prothèse auditive suivant la revendication 1 ou 2,
    caractérisée en ce que les éléments pour faire une moyenne sont constitués sous la forme de passe-bas ( 6, 7, 14 ).
  4. Prothèse auditive suivant la revendication 3,
    caractérisée en ce qu'il est prévu des passe-bas du premier ordre.
  5. Prothèse auditive suivant l'une des revendications 1 à 4,
    caractérisée en ce que l'élément ( 8 ) de comparaison a une valeur de seuil réglable pour la comparaison avec la différence de NL et de NK.
  6. Prothèse auditive suivant l'une des revendications 1 à 5,
    caractérisée en ce qu'il est prévu un élément ( 17 ) de filtrage, ayant des fréquences d'arrêt réglables différentes correspondantes pour supprimer la réaction constatée.
  7. Prothèse auditive suivant la revendication 6,
    caractérisée en ce qu'il est prévu plusieurs éléments ( 17, 18, 19 ) de filtrage, ayant des plages de fréquence d'arrêt différentes et/ou des caractéristiques de filtrage différentes.
  8. Prothèse auditive suivant l'une des revendications 6 ou 7,
    caractérisée en ce que, pour les éléments ( 17, 18, 19 ) de filtrage, des caractéristiques différentes de filtrage ( par exemple position et largeur sur la plage de fréquence d'arrêt, degré de réduction de l'amplification etc. ) sont réglables.
  9. Prothèse auditive suivant l'une des revendications 6 à 8,
    caractérisée en ce qu'il est prévu un élément ( 20 ) de commande relié au détecteur ( 4 ) d'oscillation et aux éléments ( 17, 18, 19 ) de filtrage.
  10. Prothèse auditive suivant l'une des revendications 6 à 9,
    caractérisée en ce qu'il est prévu un élément ( 22 ) de temporisation, pour réduire la durée de l'activation des éléments ( 17, 18, 19 ) de filtrage.
  11. Prothèse auditive suivant la revendication 10,
    caractérisée en ce que l'élément ( 22 ) de temporisation est intégré dans l'élément ( 20 ) de commande.
  12. Prothèse auditive suivant l'une des revendications 1 à 11,
    caractérisée en ce qu'il est prévu une unité ( 21 ) de mesure de niveau, pour constater le niveau du signal de sortie.
  13. Prothèse auditive suivant la revendication 12,
    caractérisée en ce que l'unité ( 21 ) de mesure du niveau a une valeur de seuil réglable pour l'activation de l'élément ( 20 ) de commande.
  14. Procédé de détection une oscillation dans une prothèse auditive comprenant un microphone, un dispositif de traitement du signal et un écouteur, notamment dans une prothèse auditive suivant l'une des revendications 1 à 13,
    caractérisé par les stades de procédé suivants :
    a ) on détermine le nombre respectif des valeurs numérisées d'échantillonnage dans des périodes successives d'un signal d'entrée du microphone,
    b ) on détermine une valeur NL moyenne de temps long et une valeur NK moyenne de temps court du nombre déterminé suivant a ) de valeurs d'échantillonnage,
    c ) on forme la différence entre NL et NK,
    d ) on forme la valeur absolue de la différence de NL et de NK,
    e ) on lisse la valeur de différence de NL et de NK,
    f ) on compare NL et NK ainsi que
    g ) on constate une oscillation, si NL et NK sont sensiblement identiques.
  15. Procédé suivant la revendication 14,
    caractérisé en ce que dans le stade a ) du procédé suivant la revendication 14, on effectue une constatation et une analyse du signe des valeurs numérisées d'échantillonnage.
  16. Procédé suivant la revendication 14 ou 15,
    caractérisé en ce que dans le stade g ) du procédé suivant la revendication 14, il est prévu une valeur de seuil réglable, par le dépassement duquel une oscillation est détectée.
  17. Procédé suivant l'une des revendications 14 à 16,
    caractérisé en ce que, si une oscillation est constatée, suivant le stade g ) du procédé suivant la revendication, on détermine la fréquence fosz d'oscillation comme produit de la fréquence fS, à laquelle le signal d'entrée du microphone a été numérisé et de l'inverse de NL.
  18. Procédé suivant l'une des revendications 14 à 17,
    caractérisé en ce que, si une oscillation est constatée, on effectue une réduction de l'amplification spécifique à la fréquence du signal du microphone à traiter en vue de supprimer une réaction.
  19. Procédé suivant la revendication 18,
    caractérisé en ce que l'on constate en continu s'il y a une réaction et on effectue une réduction correspondante modifiée d'amplification spécifique à la fréquence.
  20. Procédé suivant l'une des revendications 18 et 19,
    caractérisé en ce que, pour la réduction de l'amplification spécifique de fréquence, on effectue une activation d'éléments de filtrage ayant des fréquences d'arrêt réglées de manière adéquate.
  21. Procédé suivant la revendication 20,
    caractérisé en ce que l'on modifie les caractéristiques de filtrage des éléments de filtrage ( par exemple position et largeur de la plage de fréquence d'arrêt, degré de réduction d'amplification etc. ) pour optimiser la suppression de réaction.
  22. Procédé suivant l'une des revendications 18 à 21,
    caractérisé en ce que l'on règle la réduction d'amplification pendant une durée réglable, puis on y met fin à nouveau.
  23. Procédé suivant l'une des revendications 14 à 22,
    caractérisé en ce que l'on constate une réaction lorsqu'il y a un signal de microphone oscillant et lorsque le signal de sortie dépasse un niveau minimum réglable.
EP00109229A 1999-05-12 2000-04-28 Prothèse acoustique avec détecteur d'oscillations et méthode de détection d'oscillations dans une prothèse acoustique Expired - Lifetime EP1052881B1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
DE19922132 1999-05-12
DE1999122133 DE19922133C2 (de) 1999-05-12 1999-05-12 Hörhilfsgerät mit Oszillationsdetektor sowie Verfahren zur Feststellung von Oszillationen in einem Hörhilfsgerät
DE19922132 1999-05-12
DE19922133 1999-05-12

Publications (3)

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EP1052881A2 EP1052881A2 (fr) 2000-11-15
EP1052881A3 EP1052881A3 (fr) 2008-04-23
EP1052881B1 true EP1052881B1 (fr) 2010-10-20

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US (1) US7024011B1 (fr)
EP (1) EP1052881B1 (fr)
DE (1) DE50016012D1 (fr)
DK (1) DK1052881T3 (fr)

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DE102004050304B3 (de) * 2004-10-14 2006-06-14 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Rückkopplungen bei einem Akustiksystem und Signalverarbeitungsvorrichtung
US9008319B2 (en) * 2004-12-30 2015-04-14 Plantronics, Inc. Sound pressure level limiter with anti-startle feature
US8096937B2 (en) 2005-01-11 2012-01-17 Otologics, Llc Adaptive cancellation system for implantable hearing instruments
EP2624597B1 (fr) * 2005-01-11 2014-09-10 Cochlear Limited Système de prothèse auditive implantable
GB2445984B (en) * 2007-01-25 2011-12-07 Sonaptic Ltd Ambient noise reduction
US8045738B2 (en) * 2008-10-31 2011-10-25 Zounds Hearing, Inc. System for managing feedback
DE102009016845B3 (de) * 2009-04-08 2010-08-05 Siemens Medical Instruments Pte. Ltd. Anordnung und Verfahren zur Erkennung von Rückkopplungen bei Hörvorrichtungen
DK200970303A (en) * 2009-12-29 2011-06-30 Gn Resound As A method for the detection of whistling in an audio system and a hearing aid executing the method
US8630437B2 (en) * 2010-02-23 2014-01-14 University Of Utah Research Foundation Offending frequency suppression in hearing aids
DE102011001793A1 (de) * 2011-04-05 2012-10-11 Burmester Audiosysteme Gmbh Hörgerät und Verfahren zum Einstellen und Betreiben eines Hörgeräts
US10284968B2 (en) 2015-05-21 2019-05-07 Cochlear Limited Advanced management of an implantable sound management system

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US4596902A (en) * 1985-07-16 1986-06-24 Samuel Gilman Processor controlled ear responsive hearing aid and method
DE3733983A1 (de) * 1987-10-08 1989-04-20 Bosch Gmbh Robert Verfahren zum daempfen von stoerschall in von hoergeraeten uebertragenen schallsignalen
DE3802903A1 (de) * 1988-02-01 1989-08-10 Siemens Ag Einrichtung zur uebertragung von sprache
US5170434A (en) 1988-08-30 1992-12-08 Beltone Electronics Corporation Hearing aid with improved noise discrimination
FR2635680B1 (fr) * 1988-08-30 1997-12-26 Belone Electronics Corp Prothese auditive
US5396560A (en) * 1993-03-31 1995-03-07 Trw Inc. Hearing aid incorporating a novelty filter
JP2947093B2 (ja) * 1994-11-02 1999-09-13 日本電気株式会社 適応フィルタによるシステム同定の方法および装置
DK0824845T3 (da) * 1995-05-02 1999-06-21 Toepholm & Westermann Fremgangsmåde til styring af et programmerbart eller programstyret høreapparat til dettes in situ tilpasningsjustering
US6359992B1 (en) * 1997-02-06 2002-03-19 Micro Ear Technology Acoustics conditioner

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DK1052881T3 (da) 2011-02-14
US7024011B1 (en) 2006-04-04
EP1052881A2 (fr) 2000-11-15
DE50016012D1 (de) 2010-12-02
EP1052881A3 (fr) 2008-04-23

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