EP1041857A2 - Système auditif implantable avec audiomètre - Google Patents

Système auditif implantable avec audiomètre Download PDF

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Publication number
EP1041857A2
EP1041857A2 EP99122698A EP99122698A EP1041857A2 EP 1041857 A2 EP1041857 A2 EP 1041857A2 EP 99122698 A EP99122698 A EP 99122698A EP 99122698 A EP99122698 A EP 99122698A EP 1041857 A2 EP1041857 A2 EP 1041857A2
Authority
EP
European Patent Office
Prior art keywords
hearing system
hearing
signal
signal processing
unit
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.)
Granted
Application number
EP99122698A
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German (de)
English (en)
Other versions
EP1041857A3 (fr
EP1041857B1 (fr
Inventor
Hans Dr.-Ing. Leysieffer
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.)
Cochlear Ltd
Original Assignee
Cochlear Ltd
Implex AG Hearing Technology
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 Cochlear Ltd, Implex AG Hearing Technology filed Critical Cochlear Ltd
Publication of EP1041857A2 publication Critical patent/EP1041857A2/fr
Publication of EP1041857A3 publication Critical patent/EP1041857A3/fr
Application granted granted Critical
Publication of EP1041857B1 publication Critical patent/EP1041857B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing

Definitions

  • the coupling of the mechanical stimuli generated by an electromechanical transducer happens by direct mechanical connection of the vibrating transducer element the ossicular chain or an ossicle of the middle ear or to the inner ear (US-A-5 941 814) or by force coupling via an air gap in e.g. electromagnetic Walkers.
  • the coupling quality of the mechanical stimulus is influenced by many parameters and contributes to the rehabilitation of hearing damage and perceived hearing quality crucial with. Intraoperatively, this quality of coupling is difficult or even impossible Cannot be estimated as the movement amplitudes of the vibrating parts also at highest stimulation levels in a range around or far below 1 ⁇ m and therefore cannot be assessed by direct visual inspection. Even if this is done by others technical measurement methods succeed, e.g. through intraoperative laser measurements (e.g. laser Doppler vibrometry), the uncertainty of a long-term stable, safe remains Coupling, as this is caused by necrosis, new tissue formation, Changes in air pressure and other external and internal influences are negatively affected can be.
  • intraoperative laser measurements e.g. laser Doppler vibrometry
  • the present invention has as its object a partially or fully implantable To create a hearing system that allows by avoiding the disadvantages mentioned psychoacoustic measurements, i.e. by subjective patient responses that Coupling quality of the electromechanical transducer to the middle or To determine the inner ear without further biological-technical interfaces in the Assessment are included, which the meaningfulness of the determination of the Impair the converter coupling quality.
  • the audiometer module preferably consists of one or more, from the outside adjustable or programmable electronic signal generators that an electrical hearing test signal in the signal processing path of the implant feed.
  • the electro-mechanical output transducer of the implanted hearing system will technically reproducible and quantified electrically by the audiometer module directly controlled; this will falsify the stimulation level avoided, such as by headphone or in particular acoustic free-field performances of the audiometric test sound can occur because the Sensor or microphone function with all associated variabilities in the psychoacoustic measurement is included.
  • the system according to the invention has the advantage, for example, that Frequency-specific hearing threshold measurements with pure sine tones or narrow-band Signals (e.g. third-octave noise) even with larger, temporal examination intervals are very reproducible. Extraction is also more reproducible Psychoacoustic data in the over-threshold range, such as loudness scaling possible.
  • pure signals such as For example, sinusoidal signals are also subjectively queried, leading to Example can arise from a deterioration in the coupling quality and as "clinking" are audible.
  • Such investigations are due to the objective described above Measurement methods based on evoked potentials only to a limited extent or not at all possible.
  • the inventive system Solution of the advantage that the parameters of the signaling such as the electrical Control level of the electromechanical implant transducer by the internal ones Generators are quantified exactly and reproducible and not Fluctuations are subject to, such as those caused by a full implant acoustic headphone presentation of the test signals are given.
  • the transfer function of the implanted sound sensor (microphone) with in included the transfer the sensor function can also fluctuate over time subject and thus makes an exact interface definition for the converter transfer function impossible.
  • An implantable electromechanical output converter is particularly suitable Converter according to US-A-5 277 694, that is a converter in which a wall of the Converter housing is designed as a vibratable membrane, which together with a the piezoelectric ceramic disc applied to the inside of the membrane represents electromechanically active heteromorph composite element.
  • Another type of converter suitable for the present purposes is in the older EP patent application 98 121 495.0. It is a Transducer arrangement for partially or fully implantable hearing aids for direct mechanical Excitation of the middle or inner ear with reference to one at the implantation site the skull fixable housing and a movable with respect to the housing, mechanically rigid coupling element is provided, one in the housing electromechanical transducer is housed, with which the coupling element in Vibrations can, which after implantation of the transducer assembly a middle ear ossicle or directly to the inner ear.
  • the Electromechanical transducer is designed as an electromagnet arrangement, the one with Related to the converter housing fixed component, in particular a ring coil, and a vibratable component, preferably in the form of in a central opening of the toroid immersed permanent magnetic pin, which with the coupling element in such Connection is that vibrations of the vibratable component on the coupling element be transmitted.
  • a converter of the type disclosed in the older EP patent application 98 121 613.8 is also advantageous described type. It is a converter for partial or fully implantable hearing aids for direct mechanical excitation of the middle or Inner ear, which has a housing that can be fixed at the implantation site and a cover is provided on the housing movable, mechanically rigid coupling element, wherein in the housing is housed a piezoelectric element with which the Coupling element can be made to vibrate after implantation of the Transducer can be transferred to a middle ear ossicle or directly to the inner ear, and wherein an electromagnet arrangement is also provided in the housing, which has a With respect to the housing fixed component and a vibratable component, which is connected to the coupling element in such a way that vibrations of the vibratable component are transferred to the coupling element.
  • Such a converter has the advantage that the frequency response of the converter is both pure improved piezoelectric as well as compared to purely electromagnetic systems can be, so that an adequate auditory impression at a sufficient volume level is made possible.
  • a largely flat frequency response can be the deflection of the coupling element in a wide frequency band at sufficiently high Stimulation levels and low power consumption can be realized.
  • the electronic signal processing and amplification unit expediently has one amplifier connected downstream of the microphone, one with the output signal of the amplifier applied audiological signal processing level and one the electromechanical Output converter upstream driver amplifier.
  • This can be advantageous electronic module with a signal generator arrangement for generating the for Audiometry function necessary signals and one between the signal processing stage and the driver amplifier switched summing element, via which the Driver amplifier both the output signal of the audiological signal processing stage as well as the output signal of the signal generator arrangement.
  • a digital signal processor can be provided both for the preparation of the audio signal and for the generation of the for Audiometry function necessary signals and for the summary of the the latter signals is designed with the audio signal.
  • a digital signal processor Appropriately upstream of the signal processor, an analog-digital converter and a digital-analog converter downstream.
  • the digital-to-analog converter and the driver amplifier can be in one module be summarized.
  • the signal processor is preferably with a data memory for storing patient-specific, audiological adjustment parameters and / or parameters for the Generation of signals equipped for the audiometry function.
  • a microcontroller can advantageously be provided expediently a data memory for storing patient-specific, audiological Matching parameters and / or operating parameters of the signal generator arrangement having.
  • the signal processor can also itself for controlling at least part of the and preferably all signal processing and / or generating stages.
  • a telemetry unit which is equipped with a external programming system communicates wirelessly or wired.
  • the hearing aid is designed to be fully implantable, those in the are preferably electronic hearing system path signal processing and amplification unit, the electronic module for generating and feeding in for the audiometry function necessary signals and the telemetry unit as an electronic module, expedient together with the power supply unit, in a hermetically sealed and biocompatible implant housing.
  • the electronics module is advantageous here via an implant line with a subcutaneously in the posterior wall of the auditory canal implantable microphone and via an implantable line with the electromechanical Output converter connected. This connection can be fixed or detachable be trained.
  • a plug connection is particularly suitable for a detachable connection, as detailed in US-A-5,755,743.
  • Such a connection arrangement has at least a first contact, at least one on an elastic Body mounted second contact and a locking mechanism for engaging the end face of the first contact with the end face of the second contact, wherein the first contact is surrounded by at least one sealing web, which at a Engagement of the contacts in the elastic body is pressed and the contacts after seals on the outside.
  • the output converter is preferably connected to an ossicle via a coupling element Middle ear chain for transmission of the mechanical converter vibrations on the output side connectable.
  • Solutions in US-A-5 277 694 and in are particularly suitable for this US-A-5 941 814 described.
  • an actively vibratable part of the output converter with a coupling rod mechanically fixed, the over a coupling element is coupled to a part of the ossicular chain.
  • the coupling element at least in Fixing area sleeve-shaped and plastic using a crimping tool is cold-deformable, while the coupling rod is rod-shaped at least in the fixing area trained, provided with a rough surface and under the influence of by means of Crimping tool exerted crimping force is not plastically cold deformable, wherein in fixed state of the sleeve-shaped part of the coupling element by the crimping force cold-flowing, permanently deformed on the rod-shaped part of the coupling rod without play is attached.
  • the end of the coupling rod remote from the output transducer can, however also inserted into a hole in part of the ossicular chain and fixed there.
  • the output converter can also be designed such that it is connected via an air gap the ossicle chain or the inner ear can be coupled, as is described in detail in US Pat. No. 5 015 225.
  • the hearing aid belongs to a fully implantable hearing aid an external system for transcutaneous transmission of patient-specific hearing aids and audiometry programming data to the implant-side telemetry unit.
  • the telemetry unit is preferably additionally as Energy receiving circuit for the provision of recharge energy on the implant side the power supply unit is trained, while the external system at the same time as Charger is set up.
  • a charging system from US-A-5 is particularly suitable for this 279 292 known type or arrangements, such as those in the earlier EP patent applications 98 121 496.8 and 98 121 498.4 are described.
  • a portable remote control unit for setting or changing is also useful provided by hearing aid and audiometric functions.
  • an implant part preferably also assigns the output converter an energy and signal reception interface and an between electronic receiving system and the output converter switched with components required for energy supply and data regeneration, and an external system part includes the microphone, an electronic module with the im Hearing aid path lying signal processing unit and the electronic module Generation and feeding of the signals necessary for the audiometry function, one Driver unit and an energy and connected to the output of the driver unit Signal transmission interface.
  • the partially implantable hearing system preferably also includes an external system for transmitting patient-specific hearing aid and audiometry programming data to the electronic module of the external system part.
  • the implant system according to FIG. 1 has a microphone 10, by means of which the sound signal recorded and converted into an electrical signal, which in an amplifier 40 is preamplified.
  • This pre-amplified signal is used in an audiological Signal processing level 50 (AP: "Audio Processor") processed further.
  • This stage can all known components common to modern hearing aids such as filter stages, automatic Gain controls, noise suppression devices and so on contain.
  • This processed signal is fed to a summation element 70.
  • Further inputs of the signal-summarizing element 70 are the one or more outputs one or more signal generators 90 (SG1 to SGn), the one or more audiometer signals to generate. These can be single sine signals, narrowband signals, broadband signals Signals and the like, their spectral position, level and phase relationships to one another are adjustable.
  • the audio signal processed by stage 50 is combined with the or the Audiometer signals of the generator (s) 90 fed to a driver amplifier 80, which controls an electromechanical converter 20.
  • the converter 20 stimulates this damaged inner ear by direct mechanical coupling via a coupling element 21 a middle ear crosspiece or via an air gap coupling in, for example, electromagnetic, implantable transducers.
  • the signal processing components 40, 50, 80 and the Generators 90 are operated by a microcontroller 100 (.mu.C) with associated data storage (S) controlled.
  • a microcontroller 100 (.mu.C) with associated data storage (S) controlled.
  • patient-specific, audiological adjustment parameters as well as the audiometric parameters of the signal generators 90 be filed.
  • This individual, programmable data becomes the controller 100 fed via a telemetry unit 110 (T).
  • This telemetry unit 110 communicates wireless or wired bidirectional with an external programming system 120 (hp).
  • All electronic components of the system are except for the programming system 120 by a primary or a rechargeable secondary battery 60 with electrical Operating energy supplied.
  • a module 30 In particular with a fully implantable system, it is advisable to describe all of them electronic signal processing and processing circuit parts as well as the control components and summarize the energy supply in a module 30; this is shown in Fig. 1 indicated by the dash-dotted line.
  • This signal module 30 is on the implant side only the microphone 10 and the electromechanical transducer 20 via appropriate Lines 61 or 59 fixed or possibly via implantable Plug connections connected.
  • a further embodiment of the electronic signal module 30 is shown in FIG. 2.
  • the signal of the microphone 10 is pre-amplified in the amplifier 40 and by means of of an analog-to-digital converter 130 (A / D) is converted into a digital signal that one digital signal processor 140 (DSP) with a data storage area S is supplied.
  • the signal processor 140 basically takes on two tasks: on the one hand, as in fully digital hearing aids, the audio signal using the signal processing methods described prepared for the rehabilitation of an inner ear damage.
  • the signal generators in the signal processor 140 become digital or software realized that generate the audiometer signals described.
  • the abstract of these digital audiometer signals and the processed and amplified audio signal also takes place in the signal processor 140.
  • the digital output signal of the Signal processor 140 is converted into an analog in a digital-to-analog converter 150 (D / A) Signal converted back and the driver amplifier 80 the electromechanical Transducer 20 supplied.
  • the D / A converter 150 and the driver amplifier 80 can, as in FIG Block 81 is indicated to be combined in one module. This is particularly true in to be preferable to the case where an electromagnetic system is used as the transducer 20 and in the output signal of the signal processor 140 through the signal information Pulse width modulation is included, so that for the conversion back into an analog signal required time integration is taken over directly by the converter 20.
  • All signal processing components are controlled by a microcontroller 100 ( ⁇ C) associated data storage (S) controlled.
  • ⁇ C microcontroller 100
  • S data storage
  • This individual, programmable data will be to controller 100 via a telemetry unit 110 (T).
  • This telemetry unit 110 communicates wirelessly or wired bidirectionally with an external programming system 120 (hp). All electronic components of the system are up on the programming system 120 through the primary or secondary battery 60 electrical operating energy supplied.
  • FIG. 3 differs from that of FIG. 2 in essentially only in that a signal processor 141 is provided, which also functions of the microcontroller 100 according to FIG. 2 takes over.
  • the patient-specific data for audio signal processing and audiometer functions then also stored in the data storage area S of the signal processor 141.
  • FIG. 4 shows a possible fully implantable embodiment according to FIG. 1, 2 or Fig. 3 is shown schematically.
  • a hermetically sealed and biocompatible implant housing 56 is an electronics module 31 (shown without a battery) that Except for the absence of the battery corresponds to module 30 of Figures 1, 2 and 3.
  • Farther Housing 56 contains battery 60 for electrical supply to the implant and the telemetry device 110.
  • the microphone 10 is preferably in that of US-A-5 814 095 known manner, optionally using the in EP-A-0 920 239 described fixation element, subcutaneously in the posterior wall of the auditory canal implanted. The microphone 10 picks up the sound and converts it into an electrical one Signal which is sent to the electronics module 31 in the housing 56 via the implant line 61 is fed.
  • This transducer 20 is shown in the present example as a directly coupled system, that is, the output-side mechanical vibrations of the converter 20 are over a suitable coupling element 21 directly coupled to an ossicle of the middle ear chain, in shown case on the anvil 62. This is preferably done in the per se from US-A-5 277,694 and US-A-5,788,711.
  • the external programming system 120 is shown in FIG described the patient-specific hearing aid data and the audiometer parameters transcutaneously through the closed skin 57 to the implant-side telemetry unit 110 be transmitted.
  • a transmit head 121 is used for this purpose, for (bidirectional) data transmission is brought over the implant and, for example, by induction Data transferred.
  • the battery 60 in the implant housing 56 is a secondary, rechargeable Element, unit 110 may also include an energy receiving circuit for the implant side Provision of recharging energy.
  • the external system 120 is included the transmitter head 121, for example, a portable, wireless charger.
  • a portable remote control unit 65 is also shown, with which the patient can adjust or change essential hearing aid functions.
  • a partially implantable system is illustrated schematically in FIG.
  • the implantable part shown as subsystem 220 and the external one on the outside of the body load-bearing part as block 210.
  • the external unit 210 contains the microphone 10, one Signal processing unit 30 and a driver unit 160, the generated signals and Operating energy for the implant part, for example, via a transmission coil 170 inductively and transmitted transcutaneously through the closed skin 180 to the implanted system part 220.
  • This type of transfer corresponds to the transfer with known, partially implantable Cochlear implants or partially implantable hearing aids (see under others US-A-4 741 339, EP-B-0 572 382, US-A-5 795 287).
  • the electronic unit 30 of the external system part 210 contains all necessary electronic components for hearing aid signal processing and generation of the audiometer signals, such as, for example are explained with reference to Figures 1 to 3.
  • the individual programming of the external system with patient-specific hearing aid data and with audiometer parameters takes place via the programming system 120, which is the same as in conventional hearing aids is usually in this case wired to the electronic unit 30
  • the system 220 includes an energy and signal reception interface, in the illustrated case an inductive receiving coil 190.
  • the electronic system 200 contains all components required for energy supply and data regeneration such as demodulators and driver circuits for the electromechanical converter 20.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Prostheses (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP99122698A 1999-04-01 1999-11-15 Système auditif implantable avec audiomètre Expired - Lifetime EP1041857B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19914992 1999-04-01
DE19914992A DE19914992A1 (de) 1999-04-01 1999-04-01 Implantierbares Hörsystem mit Audiometer

Publications (3)

Publication Number Publication Date
EP1041857A2 true EP1041857A2 (fr) 2000-10-04
EP1041857A3 EP1041857A3 (fr) 2006-05-31
EP1041857B1 EP1041857B1 (fr) 2012-03-07

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EP99122698A Expired - Lifetime EP1041857B1 (fr) 1999-04-01 1999-11-15 Système auditif implantable avec audiomètre

Country Status (6)

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US (1) US6788790B1 (fr)
EP (1) EP1041857B1 (fr)
AT (1) ATE548861T1 (fr)
AU (1) AU766943B2 (fr)
CA (1) CA2300636A1 (fr)
DE (1) DE19914992A1 (fr)

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US7651460B2 (en) * 2004-03-22 2010-01-26 The Board Of Regents Of The University Of Oklahoma Totally implantable hearing system
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EP2278827A1 (fr) 2006-03-23 2011-01-26 Phonak Ag Procedé pour l'adaptation individuelle d'un appareil auditif
US7715571B2 (en) * 2006-03-23 2010-05-11 Phonak Ag Method for individually fitting a hearing instrument
CA2601662A1 (fr) 2006-09-18 2008-03-18 Matthias Mullenborn Interface sans fil pour programmer des dispositifs d'aide auditive
EP2066140B1 (fr) * 2007-11-28 2016-01-27 Oticon Medical A/S Procédé pour adapter une prothèse auditive ancrée dans l'os sur un utilisateur et système de prothèse auditive à conduction osseuse ancrée dans l'os
KR100977525B1 (ko) * 2008-04-11 2010-08-23 주식회사 뉴로바이오시스 적외선 통신 방식의 귓속형 인공 와우 장치
EP2303204A4 (fr) * 2008-06-25 2014-06-25 Cochlear Ltd Système de microphone implantable à performances améliorées
US8144909B2 (en) * 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
AU2010225449A1 (en) 2009-03-16 2011-10-13 Cochlear Limited Transcutaneous modulated power link for a medical implant
US8675900B2 (en) * 2010-06-04 2014-03-18 Exsilent Research B.V. Hearing system and method as well as ear-level device and control device applied therein
CN103328041B (zh) 2010-10-19 2016-03-16 耳蜗有限公司 用于将植入式医疗设备连接至外部电子设备的中继接口
CN103503484B (zh) 2011-03-23 2017-07-21 耳蜗有限公司 听力设备的调配
US9313589B2 (en) * 2011-07-01 2016-04-12 Cochlear Limited Method and system for configuration of a medical device that stimulates a human physiological system
US10455336B2 (en) 2013-10-11 2019-10-22 Cochlear Limited Devices for enhancing transmissions of stimuli in auditory prostheses
WO2016209682A1 (fr) * 2015-06-23 2016-12-29 Duke University Systèmes et procédés utilisant une optimisation basée sur un modèle de paramètres de stimulation de la moelle épinière
US10348891B2 (en) 2015-09-06 2019-07-09 Deborah M. Manchester System for real time, remote access to and adjustment of patient hearing aid with patient in normal life environment
CN109893139A (zh) * 2019-04-02 2019-06-18 佛山博智医疗科技有限公司 听力测试状态反馈***
CN114305402B (zh) * 2021-12-29 2024-03-01 中山大学附属第三医院（中山大学肝脏病医院） 基于云平台的纯音测听质量评价***

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US5277694A (en) * 1991-02-13 1994-01-11 Implex Gmbh Electromechanical transducer for implantable hearing aids
WO1997014267A1 (fr) * 1995-10-12 1997-04-17 Audiologic, Inc. Prothese auditive a capacite d'essai in situ
EP0806884A1 (fr) * 1996-05-10 1997-11-12 IMPLEX GmbH Spezialhörgeräte Dispositif destiné à la stimulation électro-mécanique et à l'examen de l'ouie
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
WO1998036711A1 (fr) * 1997-02-21 1998-08-27 St. Croix Medical, Inc. Prothese auditive implantable comportant des fonctions d'etalonnage et de controle de reaction auditive
EP1014755A2 (fr) * 1998-12-21 2000-06-28 IMPLEX Aktiengesellschaft Hearing Technology Prothèse auditive implantable avec masquage de acuphène

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AU766943B2 (en) 2003-10-23
ATE548861T1 (de) 2012-03-15
US6788790B1 (en) 2004-09-07
EP1041857A3 (fr) 2006-05-31
CA2300636A1 (fr) 2000-10-01
EP1041857B1 (fr) 2012-03-07
AU2226700A (en) 2000-10-05
DE19914992A1 (de) 2000-12-07

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