EP1416764B1 - Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens - Google Patents

Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens Download PDF

Info

Publication number
EP1416764B1
EP1416764B1 EP20030028311 EP03028311A EP1416764B1 EP 1416764 B1 EP1416764 B1 EP 1416764B1 EP 20030028311 EP20030028311 EP 20030028311 EP 03028311 A EP03028311 A EP 03028311A EP 1416764 B1 EP1416764 B1 EP 1416764B1
Authority
EP
European Patent Office
Prior art keywords
hearing
hearing device
hearing aid
signal
microphone
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
EP20030028311
Other languages
German (de)
English (en)
French (fr)
Other versions
EP1416764A3 (de
EP1416764A2 (de
Inventor
Volker KÜHNEL
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.)
Sonova Holding AG
Original Assignee
Phonak AG
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 Phonak AG filed Critical Phonak AG
Priority to EP20030028311 priority Critical patent/EP1416764B1/de
Priority to DK03028311T priority patent/DK1416764T3/da
Priority to DE50309302T priority patent/DE50309302D1/de
Publication of EP1416764A2 publication Critical patent/EP1416764A2/de
Publication of EP1416764A3 publication Critical patent/EP1416764A3/de
Priority to CN 200410100769 priority patent/CN1627865A/zh
Application granted granted Critical
Publication of EP1416764B1 publication Critical patent/EP1416764B1/de
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • 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
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • H04R29/001—Monitoring arrangements; Testing arrangements for loudspeakers

Definitions

  • the present invention relates to a method for adjusting a hearing aid and to an apparatus for carrying out the method.
  • a tone audiogram is used as the basis for the new hearing aid setting.
  • the actual desired setting of the hearing aid parameters - such as gain, compression, limitation, knee point or time constant - often deviates very much from the audiogram-based preset.
  • the need for amplification may deviate up to 20 dB from the target gain precalculated according to the audiogram.
  • a different basis of presetting than the audiogram alone is desirable.
  • the present invention is therefore based on the object of specifying a simple and efficient method for setting a first hearing device based on settings of a second hearing device.
  • the invention has the following advantages: in that a predefined measuring signal is applied to a microphone of a hearing device which is adapted to a specific hearing aid wearer and in that an acoustic signal generated by a listener of this hearing aid is recorded and recorded in a hearing aid to be adjusted, wherein settings in a new hearing aid due to results of the Evaluation are made in the evaluation, a particularly suitable method for Movanpassung the new hearing aid is created.
  • the method according to the invention very quickly leads to a spontaneous acceptance of the newly set hearing device in the case of the hearing aid wearer and considerably reduces the fitting outlay compared with the methods used today. In addition, the acoustician needs less time for initial adaptation.
  • Fig. 1 is a control unit 1, an existing hearing aid 2, which is set to a specific hearing aid wearer and is referred to below as a second hearing aid, and another hearing aid 3 shown, which is operatively connected to the second hearing aid 2 and is referred to below as the first hearing aid.
  • the control unit 1 which for example a commercially available PC (personal computer), consisting essentially of input / output unit and arithmetic unit, a fitting program (fitting software program) is processed, which allows the acoustician as simple and quick hearing aid adaptation to a specific hearing aid wearer.
  • PC personal computer
  • control unit 1 on the one hand with a loudspeaker 6, by means of which acoustic test signals 20 can be generated, on the other hand connected via the connecting line 7 with the first hearing aid 3, which is equipped as usual with a microphone 3a and a receiver 3b.
  • the first hearing device 3 has an audio input 10, via which an audio signal can be supplied.
  • the second hearing device 2 likewise has a microphone 2a and a receiver 2b, the latter being completely covered by a coupling element 5, so that a closed cavity is created. In this cavity also a measuring microphone 4 is arranged, whose signal is applied to the audio input 10 of the first hearing aid 3.
  • a known coupling element for use in the present invention is described, for example, in Phonak Focus No. 20 entitled “ The Desired Sensation Level (DSL) Method for Hearing Aid Fitting Infants and Children "(Richard C. Seewald, 1995 ).
  • DSL Desired Sensation Level
  • the object of the present invention is to provide a hearing aid setting for to find the first hearing aid 3, which is as similar as possible to that of the second hearing aid 2.
  • This first hearing aid setting is then ideally suited as a starting point for further fine adjustments and optimizations of the hearing aid settings.
  • the first hearing device 3 can be brought into a so-called measurement mode at the beginning of the adaptation, in which the transmission properties of the second hearing device 2 are analyzed and transmitted to the control unit 1.
  • the adaptation software executed in the control unit 1 transforms the information obtained into a parameter set which can be understood by the first hearing device 3. Incidentally, the entire sequence of the setting of the first hearing device 3 is controlled or monitored by the fitting software. Likewise, any instructions or error messages on the control unit 1 are displayed to the acoustician.
  • control unit 1 for example, a so-called sound card is used to drive the loudspeaker 6, as used in conventional personal computers.
  • the second hearing device 2 is coupled to the coupling element 5 having a known transmission characteristic, which contains the measuring microphone 4, preferably in the form of a probe microphone (corresponding to IEC Standard 126 2cc coupler HA-1 for ITE (In -The-Ear) hearing aids or HA-2 for BTE (Behind-the-Ear) hearing aids).
  • the signal of the measuring microphone 4 is fed via the audio input 10 into the first hearing device 3 and analyzed therein.
  • a filter bank which is present in the first hearing device 3 and which is used for signal processing during normal operation of the hearing aid can be used.
  • the microphone 3a of the first hearing device 3 picks up the sound of the loudspeaker 6 and serves as a reference microphone for determining the volume or sound level and for controlling the sound presentation via the control unit 1.
  • This also creates the possibility that a calibration of the first hearing aid 3 can be made.
  • the two hearing aids 2 and 3 should be close together so that the same sound field is present.
  • the adaptation of the first hearing device 3 can be made optimally if no acoustic interference signals can be picked up by the microphones 2a and 3a.
  • the whole arrangement is located in a sound-deadened room.
  • noise is detected by a corresponding algorithm in the control unit 1, whereby erroneous measured values can be eliminated (artefact rejection).
  • acoustic test signals 20 such as white noise at different levels.
  • test signals but also sinusoidal or sinusoidal signals, wobble tones, natural language or music are conceivable.
  • transient test signals 20 e.g., level jumps
  • the temporal behavior such as the time constant of the compression.
  • the first hearing device 3 can now be set so that the transfer functions of the first and second hearing devices 3 and 2 become as similar as possible.
  • the second hearing device 2 to be measured can be any hearing device.
  • the "new" first hearing device 3 has a frequency resolution and an audio input 10, to which a simple coupling of the measuring microphone 4 is possible.
  • the measurement is carried out in as quiet a room as possible - which incidentally is also necessary for the measurement of the feedback threshold of a hearing device or the hearing threshold of the hearing impaired person.
  • the conditions at the space required for the measurements in an acoustician are therefore already readily met.
  • the second hearing aid 2 is connected to the coupling element 5, which is for example a so-called 2cc coupler.
  • the 2cc coupler is defined according to standard IEC 126 (see above literature by Richard C. Seewald), although other couplers can be used as long as a defined volume with appropriate coupling is present. A conversion to standardized 2cc values is then possible at any time.
  • an adapter with a channel for a probe tube is inserted into the coupling element 5.
  • the actual measuring microphone 5 forms, for example, a RECD (Real-Ear-to-Coupler Difference) - direct audio shoe (see again IEC 126 and the literature cited by Richard C. Seewald), whose probe tube protrudes into the 2cc volume via the adapter.
  • RECD Real-Ear-to-Coupler Difference
  • the first and the second hearing device 2 and 3 are placed on a smooth surface so that the microphones 2a and 3a of the two hearing aids 2 and 3 are close to each other.
  • the loudspeaker 6 used for sonication with test signals 20 is, for example, approximately 50 cm away from the microphones 2a and 3a.
  • ICRA noises Artificial noise signals with speech-like spectral and temporal properties for hearing aid assessment "(Audiology, Vol. 40, No. 3, May-June, 2001, pp. 148-157 ) contain.
  • the test signals 20 are given to the loudspeaker 6 via the sound card of the personal computer operating as the control unit 1.
  • a stationary white noise is reproduced as a test signal 20 via the loudspeaker 6.
  • Input level averaging means present in the first hearing device 3 are read out and, if appropriate, the reproduction is corrected spectrally and in terms of level, provided that no excessive changes are necessary. Otherwise, the acoustician is informed that the speaker quality is insufficient. If a spectral correction via the control unit 1 is not possible, the method can nevertheless be carried out. However, the informative value of the results is somewhat limited.
  • the spectral background level in the test room is determined using the same method. If it is so high that a meaningful measurement is not possible, the acoustician, for example via the control unit 1, informed accordingly.
  • a first measurement consists for example in that a modulated test noise (see above) is reproduced via the loudspeaker 6 in succession as the acoustic test signal 20 with the levels 50, 65 and 80 dB.
  • the reproduction of the second hearing device 2 to be measured is detected by means of the measuring microphone 4. This reproduction is representative of the reproduction of modulated signals, e.g. Language.
  • a second measurement consists, for example, in that over the loudspeaker 6 an unmodulated test noise (see above) is reproduced as an acoustic test signal 20 at 65 dB.
  • the reproduction of the second hearing device 2 to be measured is detected. This reproduction is representative of stationary sound reproduction.
  • the amount of noise reduction (noise canceling) is determined from the reproduction difference between the first and the second measurement.
  • a third measurement may be that an unmodulated noise is reproduced via the loudspeaker 6 with a level jump of 25 dB in the middle of the signal (first 55 dB, then 80 dB and then 55 dB). From the response detected in the coupling element 5, the order of magnitude of the entry and release times can be determined.
  • loudspeaker 6 becomes real speech or equivalent modulated test noise (see above) at 65 dB level output as acoustic test signal 20.
  • the amplitude distribution of the recorded signal is evaluated and from this the effective dynamic compression and the time constants of the compression can be determined, which will be explained further below.
  • the effective dynamic compression of a signal is determined as follows: First, one determines the dynamics of the input signal of a typical modulated signal, such as speech at 65 dB SPL. It results e.g. from the difference between the 10th and 95th percentile of the amplitude distribution. Now, the signal picked up by the microphone 2a and processed in the second hearing aid 2 is analyzed in the same way. The ratio of the dynamic range determined above to the dynamic range now obtained indicates the effective compression ratio of the signal processing from the second hearing aid 2.
  • a typical modulated signal such as speech at 65 dB SPL. It results e.g. from the difference between the 10th and 95th percentile of the amplitude distribution.
  • the signal picked up by the microphone 2a and processed in the second hearing aid 2 is analyzed in the same way.
  • the ratio of the dynamic range determined above to the dynamic range now obtained indicates the effective compression ratio of the signal processing from the second hearing aid 2.
  • the time constants of the compression control can be determined on the other side as follows:
  • the results of the first measurement are used to set the input / output functions of the different channels.
  • the difference between the second and the first measurement is used to adjust the amount of noise cancellation (noise canceling). If the time constants of the gain control belong to the fitting parameters, the third measurement can be used to set the settling times.
  • the individual programs are activated one after the other in the second hearing device 2 to be measured and measured with the described method.
  • the volume adjuster is preferably placed in the position to be measured, second hearing aid 2 in that position, which is suitable for listening ffenlauter sound.
  • For digital hearing aids is this is usually the setting directly after switching on the hearing aid.
  • the second hearing device 2 must additionally be sonicated with 90 dB.
  • the method described is used.
  • a 90 dB performance is usually uncomfortable for the acoustician and the hearing aid user.
  • Fig. 2 shows a further embodiment of the invention, wherein these from the in Fig. 1 shown embodiment differs only in that the acoustic test signal 20 is generated by means of the first hearing aid 3.
  • a further coupling element 50 between the second and the first hearing device 2 or 3 is necessary.
  • the speaker 6 is required in this embodiment only for the mentioned calibration.
  • the main processing of the signals is carried out - under the guidance of the control unit 1 - mainly in the first hearing aid 3.
  • the various measurement methods that are associated with the in Fig. 1 illustrated embodiment, according to the embodiment according to Fig. 2 usable and therefore need no further explanation.

Landscapes

  • 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)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
EP20030028311 2003-12-09 2003-12-09 Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens Expired - Lifetime EP1416764B1 (de)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP20030028311 EP1416764B1 (de) 2003-12-09 2003-12-09 Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens
DK03028311T DK1416764T3 (da) 2003-12-09 2003-12-09 Fremgangsmåde til indstilling af parametre af et höreapparat og en anordning til udövelse af fremgangsmåden
DE50309302T DE50309302D1 (de) 2003-12-09 2003-12-09 Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens
CN 200410100769 CN1627865A (zh) 2003-12-09 2004-12-06 调整听力装置的方法以及实现该方法的设备

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
EP20030028311 EP1416764B1 (de) 2003-12-09 2003-12-09 Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens

Publications (3)

Publication Number Publication Date
EP1416764A2 EP1416764A2 (de) 2004-05-06
EP1416764A3 EP1416764A3 (de) 2004-07-07
EP1416764B1 true EP1416764B1 (de) 2008-03-05

Family

ID=32088141

Family Applications (1)

Application Number Title Priority Date Filing Date
EP20030028311 Expired - Lifetime EP1416764B1 (de) 2003-12-09 2003-12-09 Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens

Country Status (4)

Country Link
EP (1) EP1416764B1 (da)
CN (1) CN1627865A (da)
DE (1) DE50309302D1 (da)
DK (1) DK1416764T3 (da)

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102006042083B4 (de) * 2006-09-07 2010-11-11 Siemens Audiologische Technik Gmbh Verfahren und Vorrichtung zur Bestimmung eines effektiven Vents
DE102007039185A1 (de) 2007-08-20 2009-02-26 Siemens Medical Instruments Pte. Ltd. Verfahren und Vorrichtung zur Einstellung eines Hörgerätes
EP2247119A1 (de) 2009-04-27 2010-11-03 Siemens Medical Instruments Pte. Ltd. Vorrichtung zum akustischen Analysieren einer Hörvorrichtung und Analyseverfahren
CN103650534A (zh) * 2011-07-13 2014-03-19 峰力公司 用于从远程地点测试听力设备的方法和系统
DE102014200677A1 (de) * 2014-01-16 2015-07-16 Siemens Medical Instruments Pte. Ltd. Verfahren und Vorrichtung zur Analyse von Hörhilfeeinstellungen
DE102020202915B4 (de) 2020-03-06 2022-05-05 Sivantos Pte. Ltd. Verfahren zur Übertragung eines Hörgeräteeinstelldatensatzes von einem ersten Hörgerät auf ein zweites Hörgerät, Hörgerätesystem und Hörgerät
CN113518298B (zh) * 2020-04-09 2022-06-07 圣布拉斯特有限公司 音频校正系统
EP4622300A1 (en) 2024-03-19 2025-09-24 Sonova AG Programming a new hearing device based on an old hearing device

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5703797A (en) * 1991-03-22 1997-12-30 Frye Electronics, Inc. Method and apparatus for testing acoustical devices, including hearing aids and the like
US7058182B2 (en) * 1999-10-06 2006-06-06 Gn Resound A/S Apparatus and methods for hearing aid performance measurement, fitting, and initialization

Also Published As

Publication number Publication date
CN1627865A (zh) 2005-06-15
DE50309302D1 (de) 2008-04-17
DK1416764T3 (da) 2008-06-30
EP1416764A3 (de) 2004-07-07
EP1416764A2 (de) 2004-05-06

Similar Documents

Publication Publication Date Title
DE69826331T2 (de) Verfahren zum in-situ korrigieren oder anpassen eines signalverarbeitungsverfahrens in einem hörgerät mit hilfe eines referenzsignalprozessors
DE69933141T2 (de) Tonprozessor zur adaptiven dynamikbereichsverbesserung
DE102007033484A1 (de) Hörgerät
EP3427498B1 (de) Verfahren zum betrieb eines hörgeräts sowie hörgerät zur detektion der eigenstimme anhand eines individuellen schwellwerts
DE102005020317A1 (de) Automatische Verstärkungseinstellung bei einem Hörhilfegerät
DE102006047965A1 (de) Hörhilfsgerät mit einer Okklusionsreduktionseinrichtung und Verfahren zur Okklusionsreduktion
EP1737270A1 (de) Hörhilfegerät mit Mitteln zur Rückkopplungskompensation
EP1416764B1 (de) Verfahren zur Einstellung eines Hörgerätes sowie Vorrichtung zur Durchführung des Verfahrens
DE102012203349B4 (de) Verfahren zum Anpassen einer Hörvorrichtung anhand des Sensory Memory und Anpassvorrichtung
EP1850634A2 (de) Verfahren zum Einstellen eines Hörgeräts mit Hochfrequenzverstärkung
EP2584795B1 (de) Verfahren zum Ermitteln einer Kompressionskennlinie
EP1351550B1 (de) Verfahren zur Anpassung einer Signalverstärkung in einem Hörgerät sowie ein Hörgerät
DE102009004185B3 (de) Verfahren zur Signalverarbeitung einer Hörvorrichtung und entsprechende Hörvorrichtung
DE102012203253B3 (de) Verstärken eines Sprachsignals in Abhängigkeit vom Eingangspegel
DE102016103297B4 (de) Vorrichtung und Verfahren zur Konfiguration eines nutzerspezifischen Hörsystems
EP2648424B1 (de) Verfahren zur Ausgangspegelbegrenzung bei Hörvorrichtungen
EP3796676B1 (de) Verfahren zum betrieb eines hörgeräts und hörgerät
DE102004025122A1 (de) Hörgerät mit abgespeichertem, individuellem Frequenzgang und entsprechendes Anpassverfahren
EP4505760B1 (de) Hörgerät und verfahren zum betrieb eines hörgeräts
DE102011089865B4 (de) Verfahren zum Anpassen einer Frequenzkompressionseinrichtung einer Hörvorrichtung und entsprechende Anpassungsvorrichtung
EP4135345A2 (de) Verfahren zur anpassung eines digitalen hörgerätes, hörgerät und computerprogrammprodukt
CH719643A2 (de) Verfahren und System zum Verifizieren von Hörgeräten mit frequenzverändernder Funktion
DE102024117610A1 (de) Verfahren zum Erzeugen von Testsignalen zum Ermitteln einer Hörbeeinträchtigung einer Person
WO2024104945A1 (de) Verfahren zum betrieb eines hörgeräts sowie hörgerät
EP4664931A1 (de) Verfahren zur rauschunterdrückung in einem hörgerät

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: A2

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IT LI LU MC NL PT RO SE SI SK TR

AX Request for extension of the european patent

Extension state: AL LT LV MK

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

AK Designated contracting states

Kind code of ref document: A3

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IT LI LU MC NL PT RO SE SI SK TR

AX Request for extension of the european patent

Extension state: AL LT LV MK

RIC1 Information provided on ipc code assigned before grant

Ipc: 7H 04R 25/00 A

Ipc: 7H 04R 29/00 B

17P Request for examination filed

Effective date: 20041002

17Q First examination report despatched

Effective date: 20041116

AKX Designation fees paid

Designated state(s): CH DE DK LI

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

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): CH DE DK LI

REG Reference to a national code

Ref country code: CH

Ref legal event code: NV

Representative=s name: TROESCH SCHEIDEGGER WERNER AG

Ref country code: CH

Ref legal event code: EP

REF Corresponds to:

Ref document number: 50309302

Country of ref document: DE

Date of ref document: 20080417

Kind code of ref document: P

REG Reference to a national code

Ref country code: DK

Ref legal event code: T3

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: 20081208

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DK

Payment date: 20101210

Year of fee payment: 8

REG Reference to a national code

Ref country code: DK

Ref legal event code: EBP

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DK

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20120102

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: CH

Payment date: 20171227

Year of fee payment: 15

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20171229

Year of fee payment: 15

REG Reference to a national code

Ref country code: DE

Ref legal event code: R119

Ref document number: 50309302

Country of ref document: DE

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20190702

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20181231

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20181231