EP2229010A2 - Procédé de compensation d'un bruit parasite dans un appareil auditif, appareil auditif et procédé d'adaptation de celui-ci - Google Patents

Procédé de compensation d'un bruit parasite dans un appareil auditif, appareil auditif et procédé d'adaptation de celui-ci Download PDF

Info

Publication number
EP2229010A2
EP2229010A2 EP10151957A EP10151957A EP2229010A2 EP 2229010 A2 EP2229010 A2 EP 2229010A2 EP 10151957 A EP10151957 A EP 10151957A EP 10151957 A EP10151957 A EP 10151957A EP 2229010 A2 EP2229010 A2 EP 2229010A2
Authority
EP
European Patent Office
Prior art keywords
hearing
sound
filter
compensation
noise
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
EP10151957A
Other languages
German (de)
English (en)
Other versions
EP2229010A3 (fr
EP2229010B1 (fr
Inventor
Robert Kasanmascheff
Ulrich Kornagel
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 Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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 Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2229010A2 publication Critical patent/EP2229010A2/fr
Publication of EP2229010A3 publication Critical patent/EP2229010A3/fr
Application granted granted Critical
Publication of EP2229010B1 publication Critical patent/EP2229010B1/fr
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1781—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase characterised by the analysis of input or output signals, e.g. frequency range, modes, transfer functions
    • G10K11/17821—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase characterised by the analysis of input or output signals, e.g. frequency range, modes, transfer functions characterised by the analysis of the input signals only
    • G10K11/17823—Reference signals, e.g. ambient acoustic environment
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1783—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase handling or detecting of non-standard events or conditions, e.g. changing operating modes under specific operating conditions
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1785—Methods, e.g. algorithms; Devices
    • G10K11/17853—Methods, e.g. algorithms; Devices of the filter
    • G10K11/17854—Methods, e.g. algorithms; Devices of the filter the filter being an adaptive filter
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1785—Methods, e.g. algorithms; Devices
    • G10K11/17855—Methods, e.g. algorithms; Devices for improving speed or power requirements
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/16—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/175—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound
    • G10K11/178—Methods or devices for protecting against, or for damping, noise or other acoustic waves in general using interference effects; Masking sound by electro-acoustically regenerating the original acoustic waves in anti-phase
    • G10K11/1787—General system configurations
    • G10K11/17873—General system configurations using a reference signal without an error signal, e.g. pure feedforward
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • H04R1/1083—Reduction of ambient noise
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K2210/00—Details of active noise control [ANC] covered by G10K11/178 but not provided for in any of its subgroups
    • G10K2210/10—Applications
    • G10K2210/108—Communication systems, e.g. where useful sound is kept and noise is cancelled
    • G10K2210/1081—Earphones, e.g. for telephones, ear protectors or headsets
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K2210/00—Details of active noise control [ANC] covered by G10K11/178 but not provided for in any of its subgroups
    • G10K2210/30—Means
    • G10K2210/301—Computational
    • G10K2210/3025—Determination of spectrum characteristics, e.g. FFT
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K2210/00—Details of active noise control [ANC] covered by G10K11/178 but not provided for in any of its subgroups
    • G10K2210/50—Miscellaneous
    • G10K2210/509—Hybrid, i.e. combining different technologies, e.g. passive and active
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K2210/00—Details of active noise control [ANC] covered by G10K11/178 but not provided for in any of its subgroups
    • G10K2210/50—Miscellaneous
    • G10K2210/511—Narrow band, e.g. implementations for single frequency cancellation
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/01—Hearing devices using active noise cancellation

Definitions

  • the invention relates to a method for compensating for background noise in a hearing device.
  • the invention also relates to a hearing device which is designed to compensate for background noise.
  • the invention relates to a device and a method for adjusting a hearing device.
  • the term hearing device is understood in particular to mean a hearing device. In addition, however, the term includes other portable acoustic devices such as headsets, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE - In the ear, CIC - Completely in the canal).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE - In the ear, CIC - Completely in the canal e.g. Concha hearing aids or canal hearing aids
  • ITE - In the ear concha hearing aids or canal hearing aids
  • CIC canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is standard integrated into a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
  • a signal processing unit 3 which is also integrated into the hearing aid housing 1, processes signals from the microphones and amplifies the processed signals.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • a sound detected by a microphone of a hearing aid also partially contains disturbing noises from an environment of the equipment wearer. These ambient sounds can be attenuated in the microphone signal by the signal processing unit of a hearing aid by means of a filter for noise reduction.
  • the filtered microphone signal can then be converted by a receiver of the hearing device into a sound signal, which is delivered into the ear canal of the device carrier. It is important that not even a sound from the environment directly, d. H. on the acoustic path, from the environment into the ear canal to the eardrum.
  • noise Such a sound, which has undesirably passed from the environment directly, for example, through a ventilation opening of an otoplastic into the auditory canal of the device carrier, is referred to as noise in the context of this invention.
  • the ambient noise is again audible to the equipment wearer, which were elaborately filtered out in the microphone signal of the hearing aid.
  • a hearing aid for aviation in which an ambient sound by means of a compensation sound broadband is compensated.
  • an ambient sound is superimposed with the compensation sound in the ear canal of a wearer of the hearing aid.
  • the compensation sound is phase inverse. It compensates in the auditory canal for the pressure fluctuations that would be caused by the ambient sound without the compensatory sound. In other words, the ambient sound and the compensation sound cancel each other out by their superposition.
  • Compensating for noise by means of a compensation sound is called active noise cancellation (ANC) or more generally active sound compensation.
  • the invention is achieved by a method according to claim 1. Furthermore, the object is achieved by a method according to claim 11. The object concerning the hearing device is achieved by a hearing device according to claim 5 and a device according to claim 14.
  • the hearing includes a subjective loudness perception by a device wearer. Such a perception of loudness can be determined by methods of psychoacoustics known per se. However, the hearing can also be an auditory threshold, as it is e.g. can be determined by a hearing curve.
  • a compensation sound for a hearing device can be generated. Compensation does not take place for all frequencies, but only for frequencies in that spectral band in which a device carrier, for example hears particularly well according to his hearing and / or in which, for example, a sound has a lot of sound energy. Such a spectral band can often be relatively narrow in relation to the total range of audible frequencies.
  • the method may also be designed for compensating in multiple spectral bands.
  • the compensation sound can also be generated in particular without specially optimized device components.
  • an unfavorable group delay caused, for example, by the transducers of the hearing device may be corrected by a group delay of the filter which is negative in the particular spectral band. Such a correction is impossible with a broadband active sound compensation.
  • Störschallpfad the entirety of all acoustic transmission paths is meant over which, for example, an ambient sound, or a significant proportion of the same, from an environment of a device carrier can reach his eardrum, where he then perceptible as noise in the context of the invention.
  • the interference sound path does not include the transmission that is intended to be effected by the hearing device in a partially electronic way.
  • a transfer function of a Störschallpfads can be determined, for example, by a manufacturer by measurements using methods known per se from the prior art.
  • the filtered input signal for the spectral band has the same spectral characteristics as the noise.
  • a further filtering of the input signal can be provided by which, for example, a transmission behavior of a microphone or a loudspeaker of the hearing device is compensated.
  • a signal results, from which a sound inverse to the phase of the noise, that is to say a compensation sound, can be generated.
  • the compensation property is ensured by the inventive method, in particular in the particular spectral band.
  • the spectral band is determined as a function of the spectral distribution of the energy of the noise or the noise causing the noise, an advantageous development results if the determination of the spectral bands is repeated periodically or continuously.
  • the spectral band By constantly adapting the spectral band to the spectral distribution of the energy of the sound to be compensated, it is possible to compensate for it even when an ambient noise changes rapidly in its spectral composition.
  • a further advantage results if, for filtering as a function of the spectral band, one of a plurality of predetermined filters is selected or a filter is calculated.
  • a filter is meant here all those parameters which are necessary for the configuration of a filter algorithm. These parameters of a filter algorithm are also called coefficients of a filter.
  • the outlay for calculating a compensation sound signal is particularly low. Calculating a filter as a function of a spectral band allows to provide a filter for any spectral band.
  • the processing device comprises a filter bank.
  • the spectral distribution of the sound energy is always at intervals of a few milliseconds redeterminable again. Consequently, that spectral band can be determined correspondingly fast, for which a compensation sound signal is to be calculated by the filter device.
  • the hearing device is advantageously further developed in that the filter device comprises a recursive, linear filtering.
  • a linear filter By using a linear filter, there is the advantage that little computing time is needed to calculate a compensation sound signal.
  • a recursive filter has the advantage that particularly few coefficients are required for simulating a transfer function for the sound on an interference sound path, so that the calculation can be carried out with particularly few calculation steps. With a recursive filter also a very low group delay can be achieved.
  • the filter device of the hearing device comprises an adaptive filter. This makes it possible to use one and the same filter for different spectral bands.
  • the filter only has to be adapted to the transfer function of the noise path before filtering in the corresponding spectral band.
  • a plurality of filters are provided in the filter device, from which filter one of them can be selected depending on the particular spectral band.
  • the transfer function is advantageously formed from a spectral profile and a scaling factor.
  • the spectral curve describes the ratio of the influence of the Störschallpfads on the sound in one frequency to the influence of the Störschallpfads on the sound in another frequency. In other words is operated by the spectral curve only the principal form of the transfer function.
  • the spectral course and the transfer function can still differ by a multiplicative factor. This multiplicative factor is the scaling factor.
  • the division results in the advantage that the hearing device can be adapted particularly easily to a user. Namely, while the spectral course can be determined by measurements in the production of the hearing device, the spectral profile with an actual transfer function, as it results when wearing the hearing device, can easily be brought into coincidence by adapting the hearing device for a user only the scaling factor has to be determined.
  • the compensation filter is preferably chosen so that in the spectral band for which the user has a good hearing, a compensation sound can be provided by means of the compensation filter.
  • Good hearing as already mentioned, is to be understood in particular as a pronounced loudness sensation.
  • the compensation can also be done for several spectral bands.
  • a configuration can be done, for example, by storing parameters or coefficients of the compensation filter in the hearing device so that a filter unit of the hearing device can filter the input signal accordingly.
  • determining the compensation filter comprises calculating coefficients as a function of the hearing and of a transfer function for a sound on a noise path.
  • the configuring includes transmitting the selected and determined compensation filter to the hearing device.
  • the selection or determination thus takes place outside the actual hearing device. This does not rely on the storage capacity and computing capacity of the hearing device when it comes to selecting or determining a compensation filter.
  • a list of possible compensation filters for selection and a comprehensive algorithm for calculating a compensation filter can be provided by dedicated devices. It is only necessary to transfer the finished compensation filter to the hearing device.
  • the method for adjusting a hearing device can be easily implemented.
  • the device is developed in an advantageous manner by storing in the determination device a plurality of predetermined compensation filters, one of which can be selected as a function of the hearing. As a result, the device is also operable for persons who are not familiar with a calculation of compensation filters.
  • FIG. 2 an ear with an auricle 6 and an ear canal 7 is shown.
  • a hearing aid 8 is introduced in the ear canal 7.
  • a vent 9 is formed through which fresh air from an environment of the ear can flow into the ear canal 7. Such ventilation significantly increases the wearing comfort for the user of the hearing device 8.
  • a sound source 10 which emits an unwanted sound 11, so a sound to the auricle 6 down.
  • the sound 11 can penetrate through the vent 9 in the ear canal, where it can meet as a noise 12 on a tympanic membrane 13 of the user.
  • the sound 11 thus reaches the eardrum 13 in a purely acoustic way through the vent 9.
  • Störschall 12 represented in the example also further noise that penetrates another way from the environment of the device carrier to the eardrum.
  • the background noise 12 is so far attenuated in a region 14 in front of the eardrum 13 by compensation by means of a compensation sound 15 that it is barely audible to the user of the hearing aid 8.
  • the compensation sound 15 is superimposed on the background noise 12 in such a way that the sound formed by the superimposition of this sound has significantly less energy in the region 14 than the background noise 12 alone does.
  • the sound formed from the two superimposed sound has in the area 14 but not across all frequencies significantly less energy than the noise 12 alone.
  • the compensation is only effected for those frequencies which can be perceived relatively well by the user of the hearing device 8 and in which, on the other hand, the background noise 12 has a relatively large amount of energy. The totality of these frequencies forms a spectral band.
  • the compensation sound 15 is part of a sound that a listener 16 of the hearing device 8 radiates.
  • the listener 16 emits the compensation sound 15, because a useful signal which converts the listener 16 into sound, a compensation sound signal is additively superimposed.
  • the compensation sound signal is calculated from a microphone signal that a microphone 17 of the hearing device 8 generates.
  • the microphone signal is an input signal in the sense of the invention and represents the sound 11 from the environment of the user.
  • the microphone signal is filtered by means of a filter 18 of the hearing device 8 in such a way that it has the same spectral properties as the noise 12 in the mentioned spectral band.
  • the compensation sound signal is generated, in which the filtered signal is inverted.
  • the inverting is done in the example by an inverter 19.
  • the filter 18 and the inverter 19 act together as a compensation filter according to the invention.
  • the filter 18 and the inverter 19 can also be combined to form a compensation filter.
  • the filter function of the filter 18 is then such that filtering and inverting are performed together. A separate inverter is then not necessary.
  • the filter 18 is a recursive, linear filter. This makes it possible to provide a required group delay of the filter in a particular spectral band.
  • the filter 18 forms the spectral change of the sound 11 as it passes through the vent 9 and through the remaining locations en route to the ear canal 7 only for that mentioned spectral Band exactly after.
  • a microphone signal to be processed by the filter 18, since it is actually intended to represent the sound 11, has been falsified by a transmission characteristic of the microphone 17.
  • the receiver 16 also causes distortion when converting the compensation sound signal into the compensation sound 15.
  • the filter 18 compensates for this influence of the two transducers and other components of the hearing aid.
  • the hearing aid 8 is for the user not only a hearing aid, but it also acts like an active earplugs, ie it compensates for the noise 12, which reaches the eardrum 13 of the user, for example by the vent 9.
  • the ambient sound 11 is recorded with the aid of the microphone 17 of the hearing device 8 and the spectral characteristic of the microphone signal is modified by means of the filter 18 and the inverter 19.
  • the compensation sound is then generated by means of the receiver 16.
  • the hearing aid 8 With the hearing aid 8 it is not possible to dimension the filter 18 so that it functions ideally for the entire audio frequency range. This is because a hearing aid is not built exclusively for the purpose of active noise cancellation. Therefore, the components of the hearing aid 8 used, that is, for example, the microphone, the earpiece, the housing shape and damping materials, are not such that an active noise compensation can be ideally achieved. Therefore, the active noise compensation in the hearing aid 8 is limited to a specific spectral band.
  • the filter 18 By suitable dimensioning of the filter 18, it can be controlled in which frequency band an active noise compensation is particularly effective and in which frequency band or in which frequency bands the active noise compensation behaves suboptimally. The consequence is that the active noise compensation decreases in certain frequency ranges or even instead of a sound cancellation in certain frequency bands a sound amplification takes place.
  • the frequency band in which the active noise compensation works particularly well can be placed in that frequency band in which the wearer of the hearing device perceives a background noise relatively clearly or loudly.
  • the artifacts that arise in frequency ranges with poor noise compensation, masked by the hearing loss of the hearing aid wearer are annoying and annoying.
  • FIG. 3 is in connection with FIG. 2 illustrates once again how the signal of the sound 11 of the sound source 10 on an interference sound path 20a and on a signal path 20b to the area 14 in the ear canal of the user passes.
  • the Störschallpfad 20a represents the unwanted transmission of the sound 11 through the vent and along the remaining paths from the environment into the interior of the ear canal.
  • About the Störschallpfad 20a of the sound 11 passes as noise to the area 14.
  • FIG. 3 symbolized by a transfer function H of the Störschallpfads 20a.
  • the signal path 20b represents the path of the signal of the sound 11, as determined by the electronic processing of the sound 11 in the sound in FIG. 2 shown hearing aid is formed.
  • the signal path 20b comprises the conversion of the sound 11 into a microphone signal, the filtering of the microphone signal by means of the in FIG. 2 illustrated filter 18 and the inverter 19 and the generation of the also in FIG. 2
  • the filter modifies the microphone signal according to a transfer function H 'of the filter 18th
  • the inverter 19 It is achieved by the inverter 19 that the signal filtered by the filter 18 in accordance with the transfer function H 'in the spectral band acquires the properties of a compensation sound signal.
  • the output signal of the inverter 19 is then by means of the in FIG. 2 shown receiver 16 converted into a compensation sound 15 and also emitted in the direction of the area 14. In the region 14, the signals of the interference sound paths 20a and the signal path 20b cancel each other out in the described manner in the spectral band.
  • FIG. 4 shown circuit diagram of an active noise compensation in a hearing aid shows how from an input signal obtained by means of a microphone 21, a compensation sound signal can be generated, which is then convertible with a listener 22 in a compensation sound.
  • the microphone signal of the microphone 21 is to spectrally analyzed with a filter bank 23.
  • a filter bank 23 In FIG. 4 Individual bandpass filters 24a, 24b, 24c of the filter bank are shown.
  • the filter bank 23 has more than the three bandpass filters 24a, 24b, 24c shown. The sake of clarity not shown Bandpass filters are symbolized by ellipsis.
  • the signals at the outputs of the bandpass filters 24a, 24b, 24c of the filter bank 23 are compared by a power meter 25 with each other.
  • An output signal of a bandpass filter 24a, 24b, 24c shows how much energy is present in a spectral band for which the corresponding bandpass filter 24a, 24b, 24c is transparent.
  • the power meter 25 determines based on the output signals of the band-pass filter 24a, 24b, 24c that spectral band in which a device carrier would perceive a background noise most clearly. It is also possible to combine several spectral bands.
  • the power meter 25 does not directly use the distribution of the energy as can be read off at the outputs of the filter bank 23. Instead, a spectral distribution of the energy of the noise is calculated.
  • the spectral distribution of the energy of the microphone signal calculated by the filter bank 23 is first weighted with a magnitude spectrum of a transfer function for the interference sound path.
  • the power meter 25 may also be capable of weighting the information received from the bandpass filters 24a, 24b, 24c with a user's listening curve to account for the user's subjective loudness perception for the individual spectral bands detected by the bandpass filters 24a , 24b, 24c. This may result in a spectral band in which relatively high spectral energy of the noise is still not selected by the power meter 25 because the user of the hearing aid in this spectral band has poor hearing. It may also be provided to estimate the subjective loudness perception further by means of a psychoacoustic model.
  • the selection unit 26 configures a filter unit 27 such that the microphone signal of the microphone 21, after being filtered by the filter unit 27, forms a compensation sound signal for the spectral band selected by the power meter 25.
  • FIG. 4 the configuration is symbolized in such a way that the selection unit 26 acts on a selection switch 28.
  • the selection switch 28 can be used to switch symbolically between the outputs of different filters 29a to 29d.
  • not all filters 29a to 29d present in the filter unit 27 are also in FIG. 4 shown.
  • the filters, not shown are again indicated by ellipsis. In the in FIG. 4 shown switching state of the selection switch 28, the filter 29a is active.
  • FIG. 4 illustrated form of selection by means of the selector switch 28 only a symbolic representation of the process.
  • a change between the various filters 29a to 29d is actually made possible by a filter algorithm of the filter unit 27 being configured via coefficients.
  • a filter algorithm of the filter unit 27 In order for the filter unit 27 to filter the microphone signal according to one of the filters 29a to 29d, a corresponding set of coefficients must be passed to the filter algorithm.
  • the various sets of coefficients representing filters 29a-29d are stored in a table. From this, the selection unit 26 makes a selection. As already described, this selection is dependent on the determined spectral band or spectral bands and thus, in the context of the invention, on the spectral distribution of the energy of the microphone signal and optionally also on the auditory ability of the user.
  • the filter unit 27 by restricting it to a comparatively narrow spectral band for the compensation, it is possible for this band to have a correct transit time Processing the sound to reach through the hearing aid. It is accepted that in other frequency ranges, ie outside the spectral bands determined by the arithmetic unit 25, the compensation works suboptimal. However, this is not perceived by the user.
  • the microphone signal is analyzed spectrally by the filter bank 23 continuously. For the respective spectral distribution of the energy of the noise, an optimal filter 29a to 29d is selected. Switching between sets of coefficients can be done as a fade to avoid switching artifacts.
  • the filter unit 27 as a filter algorithm may also contain as a whole or in part an adaptive filter.
  • a hearing loss of a wearer of a hearing aid 32 is measured by means of an audiometer 31.
  • the hearing loss is determined frequency dependent.
  • the hearing of the device wearer determined by means of the audiometer 31 is detected by an operating device 33 by an acoustician on an in FIG. 5 not shown screen displayed as a hearing curve.
  • the operating device also stores filters 34a to 34c developed by the manufacturer of the hearing device 32.
  • the filters are compensation filters in the sense of the invention, with which in different spectral bands for the hearing aid 32, a noise can be compensated, the 32 when wearing the hearing aid by a in FIG. 5 not shown earmold of the hearing aid 32 can penetrate to the eardrum of the wearer.
  • the filters can also be calculated in such a way that they bring about active noise compensation for typical, previously determined hearing losses. For such typical hearing losses, it is possible to determine in advance spectral bands for which compensation is required. To select a filter, the hearing curve measured with the audiometer 31 can then be compared with the typical hearing curves become. The filter is chosen to be the typical hearing curve that has the greatest similarity to the measured hearing curve.
  • FIG. 5 symbolize omission symbols that there are other filters in addition to the filters shown 34a to 34c.
  • the filters are stored as sets of coefficients that can be fed to a corresponding filtering algorithm.
  • FIG. 4 symbolizing the selection of a set of coefficients from a list by acting on a selection switch 35. In FIG. 5 is selected by the selection switch 35 just the filter 34a.
  • the set of coefficients to the selected filter is transmitted to the hearing aid 32 by means of a dubbing device 36.
  • the set of coefficients is then stored.
  • FIG. 5 As shown, it is the filter 34a that is dubbed.
  • the transfer functions of the filters 34a to 34c describe only a principal spectral profile.
  • a scaling factor is then determined with the aid of test signals, which is stored in the hearing device. This scaling factor is multiplicatively applied to a filtered signal so that the filtered and scaled signal actually causes active noise cancellation.
  • a hearing curve determined by means of the audiometer 31 can also be provided to use a hearing curve determined by means of the audiometer 31 to design a compensation filter individually for a hearing curve of a device carrier. This can be done by the acoustician operating the appropriate programmer. But it can also be provided to transmit the determined hearing curve, for example, to a laboratory for hearing aids. A function of the transmitted hearing curve and a transfer function, which describes the transmission behavior of a Störschallpfads a particular model of hearing aid, then a set of coefficients can be calculated, which is transmitted to the acoustician again, so that it transmits the set of coefficients in the hearing aid ,
  • Diagrams D1 to D5 shown show graphs of different sizes as a function of a frequency f.
  • the frequency range shown is an audio frequency range. Here frequencies between 0 Hz and about 15000 Hz are shown.
  • horizontally extending frequency axes of the individual diagrams D1 to D5 are not divided linearly, so that the explained below properties of the individual graphs are easier to represent.
  • all diagrams D1 to D5 have the same non-linear distribution.
  • a hearing curve 37 of a wearer of a hearing aid is shown, wherein in the hearing aid the method is carried out, to which the in FIG. 6 Diagrams D1 to D5 are included.
  • a comparison with a hearing curve 38 of a normal hearing person shows that the wearer of the hearing device 37 has a poorer hearing ability than a healthy person for all frequencies shown.
  • spectral band 40 in which the wearer of the hearing aid can hear comparatively well.
  • a spectral distribution 41 of the energy of a sound over the frequency is shown.
  • the sound comes from an environment of the wearer of the hearing aid and is z.T. accidentally transmitted acoustically, for example by a Vent of the hearing aid as noise to the eardrum of the wearer of the hearing aid.
  • the distribution 41 there is a spectral band 42 in which the energy of the sound is particularly large.
  • the subjective perception 43 of individual frequencies of the sound has been calculated by the wearer of the hearing device.
  • the subjective perception 43 results from a weighting of the distribution 41 of the energy of the sound with the hearing curve 37 of the wearer of the hearing aid.
  • a spectral band 44 for which the wearer of the hearing device perceives the sound particularly clearly, lies between the region 42 in which the energy of the sound is concentrated and the region 40, in which the wearer of the hearing aid can hear relatively well.
  • a set of coefficients of a compensation filter is determined in the hearing aid, with which a compensation sound signal can be generated from a microphone signal which represents the sound with the energy distribution 41.
  • the compensation filter is chosen so that the compensation is effected in particular for the area 44. However, it can also be provided to determine the compensation filter only as a function of the hearing curve 37 or only as a function of the distribution 41 of the energy of the sound. Of course, if the compensation filter is only determined as a function of a hearing curve, then the compensation filter only has to be determined once, for example when adjusting the hearing aid.
  • a set of coefficients ie a compensation filter
  • the spectral band compensation filter 45b is selected.
  • the boundaries of the spectral band 45b in both the diagram D3 and the diagram D5 are indicated by dashed lines.
  • Diagram D5 shows a transfer function 46 of the filter associated with the set of coefficients for the spectral band 45b. Furthermore, in the diagram D5, a transfer function 47 of a Störschallpfads shown, via which the sound arrives acoustically from the environment of the wearer of the hearing aid as noise to his eardrum. As can be seen from a comparison of the two transfer functions 46 and 47, the two transfer functions in the region of the spectral band 45b almost coincide. This makes it possible to generate in the spectral band 45b, with a filter unit that uses the corresponding set of coefficients, a compensation sound signal from a microphone signal representing the sound.
  • a spectral band here the spectral band 45b
  • the limits are a transition region in which a deviation of the transfer function 46 of the compensation filter from the transfer function 47 of the Störschallpfads gradually becomes larger.
  • a threshold value for the deviation can be determined, which can be determined, for example, as a function of the perceptibility or measurability of artifacts in active sound compensation.
  • the examples show how the invention makes it possible to compensate for background noise, even if the hearing device is not designed for such compensation. For calculating a compensation sound signal very little computing capacity is required.

Landscapes

  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Multimedia (AREA)
  • Signal Processing (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
EP10151957.7A 2009-03-12 2010-01-28 Appareil auditif et procédé de compensation du bruit dans un appareil auditif Active EP2229010B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102009012745A DE102009012745A1 (de) 2009-03-12 2009-03-12 Verfahren zum Kompensieren eines Störschalls bei einer Hörvorrichtung, Hörvorrichtung und Verfahren zum Anpassen derselben

Publications (3)

Publication Number Publication Date
EP2229010A2 true EP2229010A2 (fr) 2010-09-15
EP2229010A3 EP2229010A3 (fr) 2013-12-04
EP2229010B1 EP2229010B1 (fr) 2020-08-26

Family

ID=42199311

Family Applications (1)

Application Number Title Priority Date Filing Date
EP10151957.7A Active EP2229010B1 (fr) 2009-03-12 2010-01-28 Appareil auditif et procédé de compensation du bruit dans un appareil auditif

Country Status (4)

Country Link
US (1) US8693717B2 (fr)
EP (1) EP2229010B1 (fr)
DE (1) DE102009012745A1 (fr)
DK (1) DK2229010T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023214020A1 (fr) * 2022-05-06 2023-11-09 Elevear GmbH Dispositif de réduction du bruit lors de la reproduction d'un signal audio à l'aide d'un casque d'écoute ou d'une prothèse auditive, et procédé correspondant

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102011087692B4 (de) * 2011-12-05 2014-07-10 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung und Verfahren zur Verbesserung der Wahrnehmbarkeit eines Anteils eines Eingangssignals für einen Benutzer der Hörvorrichtung
US10856781B2 (en) * 2013-07-09 2020-12-08 Senspd Ltd. Method and a device for monitoring a human brain's sub-cognitive activity using Oto-acoustic Emissions
FR3019961A1 (fr) * 2014-04-11 2015-10-16 Parrot Casque audio a controle actif de bruit anc avec reduction du souffle electrique
DE102015121333A1 (de) * 2015-12-08 2017-06-08 Sennheiser Electronic Gmbh & Co. Kg Elektroakustische Schallwandlereinheit und Hörer
WO2017196453A1 (fr) * 2016-05-09 2017-11-16 Snorehammer, Inc. Annulation, masquage et suppression de bruit de ronflement active
DE102016011719B3 (de) * 2016-09-30 2017-09-07 Rheinisch-Westfälische Technische Hochschule Aachen Aktive Unterdrückung des Okklusionseffektes in Hörhilfen
US10104459B2 (en) * 2016-10-14 2018-10-16 Htc Corporation Audio system with conceal detection or calibration
EP3681175B1 (fr) 2019-01-09 2022-06-01 Oticon A/s Dispositif auditif comprenant une compensation du son direct
DK180916B1 (en) 2020-07-09 2022-06-23 Gn Hearing As HEARING DEVICE WITH ACTIVE VENTILATION CLICK COMPENSATION

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2894001B2 (ja) * 1991-06-06 1999-05-24 松下電器産業株式会社 消音装置
US5740258A (en) * 1995-06-05 1998-04-14 Mcnc Active noise supressors and methods for use in the ear canal
US6480610B1 (en) * 1999-09-21 2002-11-12 Sonic Innovations, Inc. Subband acoustic feedback cancellation in hearing aids
NO314380B1 (no) * 2000-09-01 2003-03-10 Nacre As Öreterminal
WO2007011337A1 (fr) * 2005-07-14 2007-01-25 Thomson Licensing Ecouteurs a filtre choisi par l'utilisateur pour suppression active du bruit
DK1931172T3 (da) 2006-12-01 2009-10-12 Siemens Audiologische Technik Höreapparat med undertrykkelse af stöjlyde og en tilsvarende fremgangsmåde
JP5007561B2 (ja) * 2006-12-27 2012-08-22 ソニー株式会社 ノイズ低減装置、ノイズ低減方法、ノイズ低減処理用プログラム、ノイズ低減音声出力装置およびノイズ低減音声出力方法
GB2445984B (en) 2007-01-25 2011-12-07 Sonaptic Ltd Ambient noise reduction
EP2023664B1 (fr) 2007-08-10 2013-03-13 Oticon A/S Suppression sonore active dans des dispositifs d'écoute

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023214020A1 (fr) * 2022-05-06 2023-11-09 Elevear GmbH Dispositif de réduction du bruit lors de la reproduction d'un signal audio à l'aide d'un casque d'écoute ou d'une prothèse auditive, et procédé correspondant

Also Published As

Publication number Publication date
EP2229010A3 (fr) 2013-12-04
DE102009012745A1 (de) 2010-09-23
US8693717B2 (en) 2014-04-08
DK2229010T3 (da) 2020-11-30
EP2229010B1 (fr) 2020-08-26
US20100232622A1 (en) 2010-09-16

Similar Documents

Publication Publication Date Title
EP2229010B1 (fr) Appareil auditif et procédé de compensation du bruit dans un appareil auditif
DE102005020317B4 (de) Automatische Verstärkungseinstellung bei einem Hörhilfegerät
EP2437258B1 (fr) Procédé et dispositif de compression de fréquence à décalage de fréquence sélectif
EP2164283B1 (fr) Appareil auditif et fonctionnement d'un appareil auditif doté d'une transposition de fréquence
EP2091268A1 (fr) Procédé et dispositif destinés à la surveillance d'une aide auditive
DE102011006129B4 (de) Hörvorrichtung mit Rückkopplungsunterdrückungseinrichtung und Verfahren zum Betreiben der Hörvorrichtung
DE102007035171A1 (de) Verfahren zum Anpassen eines Hörgeräts mit Hilfe eines perzeptiven Modells
EP2114089A1 (fr) Procédé et dispositif de détermination d'un degré de fermeture dans des appareils auditifs
DE102009021855A1 (de) Verfahren zur Akklimatisierung einer programmierbaren Hörvorrichtung und zugehörige Hörvorrichtung
DE102006015497B4 (de) Audiosystem und Verfahren sowie Computerprogramm und Datenträger der das Computerprogramm enthält zur Anpassung der Übertragungsfunktion eines Audiosystems mittels Sprachsteuerung
EP2584795B1 (fr) Procédé de détermination d'une ligne caractéristique de compression
DE102012203349B4 (de) Verfahren zum Anpassen einer Hörvorrichtung anhand des Sensory Memory und Anpassvorrichtung
EP2437521B2 (fr) Procédé de compression fréquentielle à l'aide d'une correction harmonique et dispositif correspondant
EP2373063A1 (fr) Dispositif auditif et procédé de réglage de celui-ci pour un fonctionnement sans contre-réaction
DE102007035173A1 (de) Verfahren zum Einstellen eines Hörsystems mit einem perzeptiven Modell für binaurales Hören und entsprechendes Hörsystem
DE102010022632A1 (de) Verstärkungseinstellung bei Hörhilfegeräten
DE102011006472B4 (de) Verfahren zur Verbesserung der Sprachverständlichkeit mit einem Hörhilfegerät sowie Hörhilfegerät
DE102020201615B3 (de) Hörsystem mit mindestens einem im oder am Ohr des Nutzers getragenen Hörinstrument sowie Verfahren zum Betrieb eines solchen Hörsystems
DE102007030067B4 (de) Hörgerät mit passiver, eingangspegelabhängiger Geräuschreduktion und Verfahren
EP4134002A1 (fr) Procédé de génération d'un audiogramme d'une personne soumise à l'essai au moyen d'un instrument auditif
DE102011087692B4 (de) Hörvorrichtung und Verfahren zur Verbesserung der Wahrnehmbarkeit eines Anteils eines Eingangssignals für einen Benutzer der Hörvorrichtung
EP2506602B1 (fr) Appareil auditif et son procédé de fonctionnement associé
DE102008019374A1 (de) Verfahren zur Bestimmung einer Zeitkonstante des Gehörs und Verfahren zum Einstellen einer Hörvorrichtung
DE102007035175A1 (de) Verfahren zum Gewinnen individueller Hörsituationsdaten und entsprechendes Aufzeichnungsgerät

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 HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR

AX Request for extension of the european patent

Extension state: AL BA RS

RTI1 Title (correction)

Free format text: METHOD FOR COMPENSATING FOR INTERFERENCE IN A HEARING AID, HEARING AID AND METHOD FOR ADAPTING THE SAME

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

RIC1 Information provided on ipc code assigned before grant

Ipc: G10K 11/178 20060101ALI20131024BHEP

Ipc: H04R 25/00 20060101AFI20131024BHEP

Ipc: H04R 1/10 20060101ALI20131024BHEP

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 HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR

AX Request for extension of the european patent

Extension state: AL BA RS

17P Request for examination filed

Effective date: 20140602

RBV Designated contracting states (corrected)

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: SIVANTOS PTE. LTD.

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: SIVANTOS PTE. LTD.

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: EXAMINATION IS IN PROGRESS

17Q First examination report despatched

Effective date: 20180327

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: GRANT OF PATENT IS INTENDED

INTG Intention to grant announced

Effective date: 20200325

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE PATENT HAS BEEN GRANTED

RIN1 Information on inventor provided before grant (corrected)

Inventor name: KASANMASCHEFF, ROBERT

Inventor name: KORNAGEL, ULRICH

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

Free format text: NOT ENGLISH

REG Reference to a national code

Ref country code: CH

Ref legal event code: EP

REG Reference to a national code

Ref country code: AT

Ref legal event code: REF

Ref document number: 1307572

Country of ref document: AT

Kind code of ref document: T

Effective date: 20200915

REG Reference to a national code

Ref country code: IE

Ref legal event code: FG4D

Free format text: LANGUAGE OF EP DOCUMENT: GERMAN

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 502010016738

Country of ref document: DE

REG Reference to a national code

Ref country code: DK

Ref legal event code: T3

Effective date: 20201123

Ref country code: CH

Ref legal event code: NV

Representative=s name: E. BLUM AND CO. AG PATENT- UND MARKENANWAELTE , CH

REG Reference to a national code

Ref country code: LT

Ref legal event code: MG4D

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

Ref country code: HR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: PT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20201228

Ref country code: FI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: LT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20201127

Ref country code: BG

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20201126

Ref country code: NO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20201126

Ref country code: SE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

REG Reference to a national code

Ref country code: NL

Ref legal event code: MP

Effective date: 20200826

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

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20201226

Ref country code: NL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: LV

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: PL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

Ref country code: RO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: SM

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: EE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 502010016738

Country of ref document: DE

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

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

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

Ref country code: IT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

26N No opposition filed

Effective date: 20210527

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

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

Ref country code: SI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

Ref country code: LU

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

Effective date: 20210128

REG Reference to a national code

Ref country code: BE

Ref legal event code: MM

Effective date: 20210131

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

Ref country code: IE

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

Effective date: 20210128

REG Reference to a national code

Ref country code: AT

Ref legal event code: MM01

Ref document number: 1307572

Country of ref document: AT

Kind code of ref document: T

Effective date: 20210128

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

Ref country code: AT

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

Effective date: 20210128

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

Ref country code: BE

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

Effective date: 20210131

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

Ref country code: HU

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT; INVALID AB INITIO

Effective date: 20100128

Ref country code: CY

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

Ref country code: MK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826

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

Ref country code: DE

Payment date: 20240119

Year of fee payment: 15

Ref country code: GB

Payment date: 20240124

Year of fee payment: 15

Ref country code: CH

Payment date: 20240202

Year of fee payment: 15

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

Ref country code: FR

Payment date: 20240124

Year of fee payment: 15

Ref country code: DK

Payment date: 20240123

Year of fee payment: 15

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

Ref country code: TR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20200826