EP2080410A1 - Procédé d'utilisation d'une aide auditive et aide auditive - Google Patents

Procédé d'utilisation d'une aide auditive et aide auditive

Info

Publication number
EP2080410A1
EP2080410A1 EP07821079A EP07821079A EP2080410A1 EP 2080410 A1 EP2080410 A1 EP 2080410A1 EP 07821079 A EP07821079 A EP 07821079A EP 07821079 A EP07821079 A EP 07821079A EP 2080410 A1 EP2080410 A1 EP 2080410A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
signal
acoustic signal
preferred
module
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.)
Withdrawn
Application number
EP07821079A
Other languages
German (de)
English (en)
Inventor
Eghart Fischer
Matthias Fröhlich
Jens Hain
Henning Puder
André Steinbuß
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Original Assignee
Siemens Audioligische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP2080410A1 publication Critical patent/EP2080410A1/fr
Withdrawn legal-status Critical Current

Links

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
    • H04R2201/00—Details of transducers, loudspeakers or microphones covered by H04R1/00 but not provided for in any of its subgroups
    • H04R2201/40—Details of arrangements for obtaining desired directional characteristic by combining a number of identical transducers covered by H04R1/40 but not provided for in any of its subgroups
    • H04R2201/403—Linear arrays 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
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility

Definitions

  • the invention relates to a method for actively operating a hearing aid consisting of a single or two hearing aids. Furthermore, the invention relates to a corresponding hearing aid or a corresponding hearing aid.
  • Hearing aids with digital signal processing have been introduced in the recent past. They include one or more microphones, A / D converters, digital signal processors and speakers. Usually, the digital signal processors divide the incoming signals into a plurality of frequency bands. Within each band, signal amplification and processing may be individually adjusted in accordance with requirements for a particular hearing aid wearer to improve the intelligibility of a particular component. Furthermore, algorithms for feedback and noise minimization are available in digital signal processing, but have significant disadvantages. A disadvantage of the currently existing algorithms for noise minimization z. For example, their maximum attainable Improvement in hearing aid acoustics when speech and background sounds are in the same frequency region and therefore unable to distinguish between spoken speech and background noise. (See also EP 1 017 253 A2)
  • EP 1432282 A2 discloses a digital method for adapting a hearing program of a hearing device to a current acoustic environment situation and a hearing aid system therefor.
  • characteristic, auditory-based features are extracted from a digital acoustic signal and analyzed by pattern recognition in a signal identification unit to thereby determine an acoustic environment situation and to generate a corresponding acoustic output signal.
  • This acoustic output signal is a through an input unit, such.
  • a remote control, manipulatable transmission unit supplied with preset parameter sets of the transmission unit can be influenced by the input unit by a hearing aid wearer.
  • acoustic signal processing there are spatial (eg directional microphone, beamforming), statistical (eg blind source separation) or mixed methods, which include algorithms of several types simultaneously active sound sources can separate a single or a plurality thereof.
  • the blind source separation allows by means of statistical signal processing of at least two microphone signals to perform a separation of source signals without prior knowledge of their geometric arrangement.
  • This method has advantages over conventional directional microphone approaches when used in hearing aids. Due to the principle, with such a BSS method (BSS: Blind Source Separation) with n microphones, it is possible to separate up to n sources, ie generate n output signals.
  • BSS Blind Source Separation
  • the control of directional microphones in the sense of blind source separation is subject to ambiguity, as soon as several competing sources of use, eg. B. speaker, present simultaneously.
  • the blind source separation allows in principle the separation of the various sources, if this spatially are separated; the ambiguity, however, reduces the potential benefit of a directional microphone, although it is precisely in such scenarios that a directional microphone can be very useful for improving speech intelligibility.
  • the hearing aid or the mathematical algorithms for blind source separation are in principle faced with the problem of having to decide which of the signals generated by the blind source separation should be passed on most advantageously to the user of the algorithm, ie the hearing aid wearer.
  • the choice made by this algorithm must therefore be based on assumptions about the probable will of the listener.
  • the object of the invention is achieved by a method for operating a hearing aid according to claim 1 and by means of a hearing aid according to claim 18.
  • the object of the invention is thus solved to leave this decision to the hearing aid wearer himself.
  • a method for active operation of a hearing aid by a hearing aid wearer, wherein a command "hold” is transmitted to a signal processing of the hearing aid for tracking and selective amplification from a hearing aid wearer preferring an acoustic signal, which instructs the signal processing, to follow this selected by the hearing aid acoustic signal and to take into account in an acoustic output of the hearing aid particularly.
  • a hearing aid with an input device wherein the input device can be called by a hearing aid wearer to actively give the hearing aid an instruction in such a way that an operating instruction is given to the hearing aid by the input device to an acoustic module (signal processing) "Hold" is given, which identifies a preferred by the hearing aid wearer acoustic signal, which is particularly considered in an output sound of the hearing aid.
  • acoustic module signal processing
  • the choice of which acoustic signal or which speaker is to be followed is made in a simple and intuitive manner by the user of the hearing aid in order to avoid the principal ambiguity of source separation methods.
  • the hearing aid wearer knows best who he wants to talk to at the moment, so that no misclassification of the preferred acoustic signal is caused by automatisms within the hearing aid. He is not limited in his freedom of movement, except when executing the command "Hold", and he benefits in an acoustically difficult situation in which a directional microphone can give him a great benefit in speech intelligibility, of the automatic directional microphone.
  • the invention it is possible, depending on the number of existing microphones in the hearing aid, a single or a plurality of preferred by the hearing aid wearer to select acoustic signals of the ambient sound and emphasize the output sound of the hearing aid. In this case, it is possible to arbitrarily set a volume of the preferred or acoustic signals in the output sound.
  • the signal processing has a demixing module, which preferably operates as a means for blind source separation for separating the acoustic signals of the ambient sound. Furthermore, the signal processing has a post-processor module which sets up the corresponding operating mode in the hearing aid on the "hold" command of the hearing aid wearer. nal kau a preprocessor module - whose e- lekthari output signals are the electrical input signals of the demixing module - normalized and processed electrical signals that come from microphones of the hearing aid. With regard to the preprocessor module (preprocessor) and the demixing module (unmixer), reference is made to EP 1 017 253 A2 paragraphs [0008] to [0023].
  • the hearing aid wearer if he wants to have tracked a particular acoustic signal from the microphones of the hearing aid, via the input device, the command "hold" to the signal processing that selects the corresponding signals in the post-processor module and a speaker of a listener of the hearing aid at least louder than other unwanted acoustic signals.
  • the input device may be any input or device on the hearing aid or a remote control for the hearing aid. In its simplest embodiment, this is an operating element on the hearing aid and / or the remote control. However, it is also possible to form the input device as a voice control in the hearing aid or in the remote control.
  • the acoustic signal which is predominant when executing the command "hold” on the loudest or in the ambient sound and / or which preferably comes from a 0 ° viewing direction of the hearing aid wearer is then followed by the source separation algorithm, preferably the BSS algorithm, and provided accentuated by the listener of the hearing aid to the wearer.
  • a "simple tracking" of the preferred acoustic signal is possible, in which a speaker is tracked as long as he speaks, ie without a memory function, however, a so-called “intelligent tracking” is preferred or a plurality of preferred, acoustic signals, analyzed and temporarily stored in the hearing aid in the form of characteristic parameters (speaker recognition).
  • a real Dialogue ie in which also the hearing aid wearer speaks from time to time and whose dialog partner is silent, can be followed by the hearing aid or the signal processing.
  • a no further follow-up of the preferred or the acoustic signals can be carried out according to the invention by a release command to the input device. If a plurality of preferred acoustic signals are selected by the hearing aid wearer, then it is possible to release the preferred acoustic signal that is loudest or predominant in the execution of the release command, or preferably to release the preferred, audible signal from the current one 0 ° view of the hearing aid wearer comes. Furthermore, it is possible independently to release any, previously preferred, acoustic signal, since this is already identified. If only one single preferred, acoustic signal is selected, this can of course be dispensed with.
  • ceasing to track one or more preferred acoustic signals over a time criterion may occur
  • Timeout occur when one of the speakers or the speaker for a certain period of time was no longer recognized by the speaker recognition of the hearing aid.
  • An unintentional stay of the hearing aid in the "hold” mode can be reduced by an automatically generated release command, ie an automatic timeout.
  • FIG. 1 shows a block diagram of a hearing aid according to the prior art, with a module for blind source separation
  • 2 shows a block diagram of a hearing aid according to the invention with a signal processing according to the invention which can be influenced by a hearing aid wearer, during the processing of ambient sound with two acoustically independent signal sources
  • Fig. 3 is a block diagram of a second embodiment of the hearing aid according to the invention in the simultaneous processing of three mutually acoustically independent sources of ambient sound.
  • the invention is not limited to such blind source separation, but rather is intended to broadly include source separation methods for acoustic signals. Therefore, this BSS module is also referred to as demixing module.
  • the term below refers to a "tracking" of a preferred acoustic signal by a hearing aid of a hearing aid wearer, which is to be understood as a selection of one or a plurality of acoustic signals of the ambient sound made by the hearing aid wearer, which is transmitted electrically or electronically by the hearing aid Acoustic signals of the ambient sound are selected and which are reproduced in a manner amplified in relation to the other acoustic signals of the ambient sound, ie in a manner perceived by the hearing aid wearer as relatively louder than when the preferred acoustic signal is being monitored by the hearing aid Room, in particular a position of the hearing aid in the room, ie a Viewing direction of the hearing aid wearer, preferably not taken into account.
  • FIG. 1 shows the state of the art as taught by EP 1 017253 A2 (see paragraph [0008] ff there).
  • a hearing aid 1 has two microphones 200, 210, which together can form a directional microphone system, for generating two electrical output signals 202, 212.
  • Such a microphone arrangement gives the two electrical output signals 202, 212 of the microphones 200, 210 an inherent directional characteristic.
  • Each of the microphones 200, 210 receives an ambient sound 100 that is a composite of unknown, acoustic signals from an unknown number of acoustic sources.
  • the microphone signals 202, 212 are processed mainly in three stages.
  • the microphone signals 202, 212 are preprocessed in a preprocessing module 310 for improving the directional characteristic, which is accompanied by a normalization of the original
  • a blind source separation takes place in a BSS module 320, wherein the output signals of the preprocessor module 310 are subject to a demixing process.
  • the output signals of the BSS module 320 are post-processed in a post-processor module 330 to produce a desired electrical output signal 332 which serves as input to a handset 400 and loudspeaker 400 of the hearing aid 1, respectively, and a sound generated thereby to the hearing aid wearer leave.
  • steps 1 and 3 ie the preprocessor module 310 and the post-processor module 330, are optional.
  • FIG. 2 now shows a first embodiment of the invention, wherein in a signal processing 300 of the hearing aid 1 a demixing module 320, hereinafter referred to as BSS module 320, is located, to which a post-processor module 330 is connected downstream.
  • a preprocessor module 310 may be provided, which prepares or prepares the input signals for the BSS module 320 accordingly.
  • the signal processing 300 is preferably carried out in a DSP (Digital Signal Processor) or in an ASIC (Application Specific Integrated Circuit).
  • DSP Digital Signal Processor
  • ASIC Application Specific Integrated Circuit
  • acoustically independent signals 102, 104 or signal sources 102, 104 exist in ambient sound 100, one of these acoustic signals 102 being the acoustical signal 102 preferred by the hearing aid wearer.
  • This preferred acoustic signal 102 is intended to be tracked by the hearing aid 1 or the signal processor 300 and to be a main acoustic component of the handset 400 so that an output sound 402 of the loudspeaker 400 mainly contains this signal (102).
  • the two microphones 200, 210 of the hearing aid 1 each receive a mixture of the two acoustic signals 102, 104 - illustrated by the dotted arrow (representing the preferred, acoustic signal 102) and the solid arrow (representing the non-preferred, acoustic signal 104). - and deliver them either to the preprocessor module 310 or equal to the BSS module 320 as electrical input signals.
  • the two microphones 200, 210 can be distributed as desired. They may be located in a single hearing aid 1 of the hearing aid 1 or distributed to both hearing aids 1. In addition, it is possible, for. B. one or both microphones 200, 210 outside the hearing aid 1, z. B.
  • the electrical input signals of the BSS module 320 need not necessarily originate from a single hearing device 1 of the hearing aid 1.
  • a hearing aid 1 consisting of two hearing aids 1 has a total of four or six microphones.
  • the preprocessor module 310 prepares the data for the BSS module 320, which in turn is made up of its two mixed ones Depending on ability, input signals form two separate output signals, each of these output signals representing one of the two acoustic signals 102, 104.
  • the two separate output signals of the BSS module 320 are input signals for the post-processor module 330, in which it is now decided which of the two acoustic signals 102, 104 is output to the loudspeaker 400 as an electrical output signal 332.
  • the hearing aid wearer issues a corresponding command to the signal processor 300 or the postprocessor module 330, wherein an operating mode is provided for the hearing aid 1 by an input device 10 on or in the hearing aid 1 or by a remote control (shown schematically at the bottom right in FIG "Hold" is established for a certain period of time T.
  • This "hold" operating mode represents one of the two output signals of the BSS module 320. In the present example of FIG. 2, this is illustrated by the dotted arrow, which indicates the acoustic signal preferred by the hearing aid wearer Signal 102 represents.
  • the post-processor module 330 is now set up such that it outputs a representative of the preferred acoustic signal 102 to the listener 400 of the hearing aid 1 in an amplified manner.
  • the input device 10 may, for. As a button 10 or a
  • Switch 10 on the hearing aid 1 or the remote control for the hearing aid is possible to form the input device 10 as a speaker recognition module in the hearing device 1 or the remote control or as voice control.
  • the post-processor module 330 establishes the "hold" operating mode, which mainly outputs the preferred acoustic signal 102 as the electrical output signal 332 of the hearing aid 1 over a certain period of time T.
  • the source signal in the ambient sound 100 which is mainly incident upon actuation of the input device 10 from a 0 ° viewing direction of the hearing aid wearer other angles possible.
  • the corresponding acoustic signal preferred by the hearing aid wearer 102 at its frequency range or its respective frequency extremums, its tonal or Oktavrance, by a certain human voice, by music, by a certain interference freedom or by similar temporal distances similar to each other acoustic
  • Identify events or by an opposite of this list In the selection of the preferred acoustic signal 102, that acoustic signal 102 which is incident from the 0 ° viewing direction of the hearing aid wearer and is subsequently tracked by the algorithm of the BSS module 320 or the postprocessor module 330 is preferred.
  • a speech signal 102 can be temporarily stored by means of a speech analysis in the form of characteristic parameters in the signal processing 300 or the hearing aid 1 and is tracked independently of a head movement or viewing direction of the hearing aid wearer. In the latter situation, the speaker is released either by the release command of the hearing aid wearer or via a timeout.
  • FIG. 3 shows the method according to the invention and the hearing aid 1 according to the invention when processing three acoustic signal sources Si (t), S2 (t), S3 (t), which together form the ambient sound 100.
  • This ambient sound 100 is recorded in each case by three microphones, each of which outputs an electrical mic signal Xi (t), X2 (t), X3 (t) to the signal processor 300.
  • the signal processor 300 does not have a preprocessor module 310, but may preferably contain it (this also applies analogously to the first embodiment) Embodiment of the invention).
  • the electrical microphone signals Xi (t), X2 (t), X3 (t) are input signals to the BSS module 320, which contain the respectively in the microphone signals X 1 (t), X 2 (t), X 3 (t) acoustic signals Si (t), S2 (t), S3 (t) separated by acoustic sources and as electrical output signals s'i (t), s'2 (t), s'3 (t) [analogue: s' 4 ( t), ..., s' o (t)] to the post-processor module 330.
  • the hearing aid wearer prefers two acoustic signals, namely Si (t) and S3 (t) (this largely corresponds to the acoustic sources Si (t) and S3 (t)).
  • the hearing aid wearer of the input device 10 consecutively issues the corresponding command "hold” for establishing the operating mode "hold” (see above), wherein the post-processor module 330 outputs the corresponding output signals s' 1 (t), s'3 (t) of the BSS.
  • the output signals S 'i (t), s' 2 (t), s '3 (t) of the BSS module 320' to scan "and then to make an appropriate selection.
  • the present document relates inter alia to a post-processor module 20 of EP 1017253 A2 that can be controlled by a hearing aid wearer via an input device (reference numeral according to EP 1017253 A2). See also paragraph [0025] of EP 1 017 253 A2. Further, in the invention, the preprocessor module and the BSS module such as the preprocessor 16 and the unmixer 18 of EP 1 017 253 A2 can be constructed be. See in particular paragraphs [0008] to [0024] of EP 1 017 253 A2.
  • the invention ties in with EP 1 655 998 A2 in order to provide stereo signals for a hearing aid wearer for an acoustic source selected by him or to enable a binaural acoustic supply.
  • the invention (notation according to EP 1 655 998 A2) is the output signals z1, z2 for the right (k) and left (k) of a second filter device of EP 1 655 998 A2 (see FIGS. 2 and 3) for accentuation / Amplification of the corresponding acoustic source downstream.

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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)
  • Obtaining Desirable Characteristics In Audible-Bandwidth Transducers (AREA)

Abstract

L'invention concerne un procédé d'utilisation active d'une aide (1) auditive par un porteur d'aide auditive. Selon l'invention,un dispositif (300) de traitement de signal de l'aide (1) auditive présente un module (320) de dissociation de signaux (102, 104; s<SUB>1</SUB>(t), s<SUB>2</SUB>(t), s<SUB>3</SUB>(t), s<SUB>4</SUB>(t),..., s<SUB>m</SUB>(t)) sonores et un module (330) post-processeur par le biais duquel est établi un mode de fonctionnement = Maintien = de l'aide (1) auditive (ex. A15), pour poursuivre et sélectionner au moins un signal (102; s<SUB>1</SUB>(t), s<SUB>3</SUB>(t)) sonore préféré d'un porteur d'aide auditive parmi un bruit (100 ; 102, 104 ; s<SUB>1</SUB>(t), s<SUB>2</SUB>(t),S<SUB>3</SUB>(t), S<SUB>4</SUB>(t),..., s<SUB>n</SUB>(t)) ambiant, le porteur d'aide auditive transmet à l'aide (1) auditive une instruction qui établit dans le dispositif (300) de traitement de signal de l'aide auditive (1) le mode de fonctionnement = Maintien = pendant une durée (T) donnée, le signal(102; s<SUB>1</SUB>(t), s<SUB>3</SUB>(t)) sonore préféré est poursuivi dans le dispositif (300) de traitement de signal puis pris en compte de manière sélective dans un bruit (402; s''(t); s''<SUB>1</SUB>(t)+s''<SUB>3</SUB>(t)) initial de l'aide (1) auditive de telle sorte qu'il est moins prédominant acoustiquement pour le porteur d'aide auditive en comparaison d'un autre signal (104; s<SUB>2</SUB>(t), s<SUB>4</SUB>(t),..., s<SUB>m</SUB>(t)) sonore et peut ainsi être mieux pris en compte.
EP07821079A 2006-10-10 2007-10-09 Procédé d'utilisation d'une aide auditive et aide auditive Withdrawn EP2080410A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006047985 2006-10-10
PCT/EP2007/060710 WO2008043758A1 (fr) 2006-10-10 2007-10-09 Procédé d'utilisation d'une aide auditive et aide auditive

Publications (1)

Publication Number Publication Date
EP2080410A1 true EP2080410A1 (fr) 2009-07-22

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Application Number Title Priority Date Filing Date
EP07821079A Withdrawn EP2080410A1 (fr) 2006-10-10 2007-10-09 Procédé d'utilisation d'une aide auditive et aide auditive

Country Status (5)

Country Link
US (1) US8325957B2 (fr)
EP (1) EP2080410A1 (fr)
JP (1) JP5130298B2 (fr)
AU (1) AU2007306366B2 (fr)
WO (1) WO2008043758A1 (fr)

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Publication number Priority date Publication date Assignee Title
EP2200341B1 (fr) * 2008-12-16 2015-02-25 Siemens Audiologische Technik GmbH Procédé de fonctionnement d'un appareil d'aide auditive et appareil d'aide auditive doté d'un dispositif de séparation de sources
WO2010146857A1 (fr) * 2009-06-17 2010-12-23 パナソニック株式会社 Appareil auditif
US9037458B2 (en) * 2011-02-23 2015-05-19 Qualcomm Incorporated Systems, methods, apparatus, and computer-readable media for spatially selective audio augmentation
US10149068B2 (en) * 2015-08-25 2018-12-04 Cochlear Limited Hearing prosthesis sound processing
EP3291226B1 (fr) * 2016-09-05 2020-11-04 Unify Patente GmbH & Co. KG Procédé de traitement de données de parole, dispositif de gestion d'appels téléphoniques et appareil auditif
DE102016225207A1 (de) * 2016-12-15 2018-06-21 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes

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JPH0933329A (ja) 1995-07-17 1997-02-07 Nippon Telegr & Teleph Corp <Ntt> 音響分離方法およびこの方法を実施する装置
JP3530035B2 (ja) 1998-08-19 2004-05-24 日本電信電話株式会社 音認識装置
EP1017253B1 (fr) 1998-12-30 2012-10-31 Siemens Corporation Séparation aveugle de sources pour prothèses auditives
WO2001087011A2 (fr) * 2000-05-10 2001-11-15 The Board Of Trustees Of The University Of Illinois Techniques de suppression d'interferences
CA2390844A1 (fr) 2001-04-18 2001-07-19 Joseph Maisano Procede permettant d'analyser un environnement acoustique et systeme destine a sa mise en oeuvre
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EP1432282B1 (fr) 2003-03-27 2013-04-24 Phonak Ag Procédé d'adaptation d'une prothèse auditive à une situation environnante momentanée et système de prothèse auditive
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JP4533126B2 (ja) 2004-12-24 2010-09-01 日本電信電話株式会社 近接音分離収音方法、近接音分離収音装置、近接音分離収音プログラム、記録媒体

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Also Published As

Publication number Publication date
JP2010506526A (ja) 2010-02-25
JP5130298B2 (ja) 2013-01-30
AU2007306366B2 (en) 2011-03-10
AU2007306366A1 (en) 2008-04-17
US20100027821A1 (en) 2010-02-04
US8325957B2 (en) 2012-12-04
WO2008043758A1 (fr) 2008-04-17

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