EP2229010B1 - Hearing aid and method for noise compensation in a hearing aid - Google Patents
Hearing aid and method for noise compensation in a hearing aid Download PDFInfo
- Publication number
- EP2229010B1 EP2229010B1 EP10151957.7A EP10151957A EP2229010B1 EP 2229010 B1 EP2229010 B1 EP 2229010B1 EP 10151957 A EP10151957 A EP 10151957A EP 2229010 B1 EP2229010 B1 EP 2229010B1
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- European Patent Office
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- sound
- hearing aid
- filter
- hearing
- compensation
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Images
Classifications
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- 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
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- 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
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- 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
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- 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
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- 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
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- 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
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- H04R1/00—Details of transducers, loudspeakers or microphones
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- 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
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- G10K2210/00—Details of active noise control [ANC] covered by G10K11/178 but not provided for in any of its subgroups
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- G10K2210/301—Computational
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- 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
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- 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
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- H—ELECTRICITY
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- 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 an interfering sound in a hearing device.
- the invention also relates to a hearing device which is designed to compensate for an interfering sound.
- the term hearing device is understood here to mean a hearing aid.
- Hearing aids are portable hearing devices that are used to care for the hearing impaired.
- different designs 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 (ITE), e.g. Concha hearing aids or canal hearing aids (ITE - In the ear, CIC - Completely in the canal) are also provided.
- BTE behind-the-ear hearing aids
- RIC hearing aid with external receiver
- ITE in-the-ear hearing aids
- ITE concha hearing aids or canal hearing aids
- ITE - In the ear, CIC - Completely in the canal are also provided.
- the hearing aids listed as examples are worn on the outer ear or in the auditory canal.
- bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
- hearing aids have an input converter, an amplifier and an output converter as essential components.
- the input transducer is usually a sound receiver, e.g. B. a microphone, and / or an electromagnetic receiver, e.g. B. an induction coil.
- the output transducer is usually an electroacoustic transducer, e.g. B. miniature speakers, or as an electromechanical converter, e.g. B. bone conduction receiver realized.
- the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG 1 using the example of a behind-the-ear hearing aid shown.
- One or more microphones 2 for picking up the sound from the environment are built into a hearing aid housing 1 to be worn behind the ear.
- a signal processing unit 3 which is also integrated in 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. If necessary, the sound is transmitted to the eardrum of the device wearer via a sound tube that is fixed in the ear canal with an otoplastic.
- the hearing aid, and in particular that of the signal processing unit 3, is supplied with energy by a battery 5 which is also integrated in the hearing aid housing 1.
- a sound detected by a microphone of a hearing aid also partially contains disturbing noises from the surroundings of the device wearer. These ambient noises 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 listener of the hearing aid into a sound signal that is emitted into the ear canal of the device wearer. It is important that no sound from the environment is also direct, i.e. H. by acoustic means, from the environment into the ear canal to the eardrum.
- interfering sound Such a sound, which undesirably got from the environment directly into the ear canal of the device wearer, for example through a ventilation opening of an otoplastic, is referred to as interfering sound in the context of this invention.
- the device wearer can again hear the ambient noises that were elaborately filtered out in the microphone signal of the hearing device.
- a hearing set for aviation is known from the prior art, in which an ambient sound is compensated broadband by means of a compensation sound.
- an ambient sound is combined with the compensation sound in the ear canal Superimposed on the carrier of the hearing aid.
- the compensation sound is phase inverse. It thus compensates for the pressure fluctuations in the ear canal that would be caused by the ambient sound without the compensation sound. In other words, the ambient sound and the compensation sound cancel each other out through their superposition.
- the compensation of a noise by means of a compensation sound is called active noise compensation (ANC - Active Noise Cancellation) or more generally active noise compensation.
- components specially designed to generate a compensation sound can usually not be used.
- the components have to be optimized according to other aspects.
- EP 1 313 417 A1 describes an earplug for noise damping based on a microphone signal from a microphone directed into the auditory canal.
- Active noise compensation can be implemented by means of the device.
- an ambient signal can be reproduced by means of a loudspeaker in the inner ear, several filters being provided for reconstructing the natural voice, between which depending on the speech sounds that the user makes just pronounces, switching between the filters.
- a cross-fading can be provided when switching between the filters.
- a hearing protection is described, which can also be designed as an earplug.
- the hearing protection can be based on active noise compensation, which generates a compensation sound for a given noise and a given frequency band in the ear canal of the user.
- the noise compensation takes place as a feed-forward method.
- a transfer function required for this is determined in a calibration process using an artificial head or using a microphone placed in a test person's auditory canal.
- a third possibility is a user survey in which a user manually sets the transmission functions according to his needs.
- EP 1 931 172 A1 describes a hearing aid with noise suppression.
- a transfer function is stored in the hearing aid, by means of which a compensation sound is calculated for a current interference signal.
- the interference noise suppression is broadband, for which a filter is designed in advance by means of a filter design during a hearing aid fitting.
- the hearing ability includes a subjective loudness perception by a device wearer. Such a loudness perception can be determined using psychoacoustic methods known per se. However, the hearing ability can also be a hearing threshold, as it is e.g. can be determined using an auditory curve.
- a compensation sound for a hearing device can be generated with the method. There is compensation not for all frequencies, but only for frequencies in that spectral band in which a device wearer can hear particularly well according to his hearing ability and in which, for example, a noise has a particularly high level of sound energy. Such a spectral band can often be relatively narrow in relation to the total range of audible frequencies.
- the method can also be designed for compensation in several spectral bands.
- the compensation sound can in particular also be generated without device components specially optimized for it.
- an unfavorable group delay which is caused, for example, by the transducers of the hearing device, can possibly be corrected by a group delay of the filter which is negative in the specific spectral band. Such a correction is impossible with a broadband active sound compensation.
- interfering sound path refers to the entirety of all acoustic transmission paths via which, for example, ambient sound, or a significant proportion of it, can reach his eardrum from the surroundings of a device wearer, where it can then be perceived as interfering sound within the meaning of the invention.
- the interfering sound path does not include that transmission that is intended to be effected by the hearing device, in part electronically.
- a transfer function of an interfering sound path can be determined, for example, by a manufacturer through measurements using methods known per se from the prior art.
- the filtered input signal for the spectral band has the same spectral properties as the background noise.
- further filtering of the input signal can be provided, by means of which, for example, a transmission behavior of a microphone or a loudspeaker of the hearing device is compensated.
- the filtered input signal is inverted during or after the filtering results in a signal from which a sound that is phase-inverse to the interfering sound, i.e. a compensation sound, can be generated.
- the compensation property is ensured by the method according to the invention in particular in the specific spectral band.
- the spectral band is determined as a function of the spectral distribution of the energy of the interfering sound or the sound causing the interfering sound, an advantageous development results when the determination of the spectral band 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 this even if the spectral composition of an ambient noise changes rapidly.
- a filter means all those parameters that are necessary to configure a filter algorithm. These parameters of a filter algorithm are also called coefficients of a filter here.
- the outlay for calculating a compensation sound signal is particularly low.
- Computing a filter depending on a spectral band makes it possible to provide a filter for any desired spectral band.
- the processing device comprises a filter bank.
- the spectral distribution of the sound energy can be determined again and again at intervals of a few milliseconds. That spectral band can thus be determined correspondingly quickly for which a compensation sound signal is to be calculated by the filter device.
- the hearing device is advantageously developed in that the filter device comprises recursive, linear filtering.
- a linear filter has the advantage that little computing time is required to calculate a compensation sound signal.
- a recursive filter has the advantage that particularly few coefficients are required to simulate a transfer function for the sound on an interfering sound path, so that the calculation can be carried out with particularly few computing steps.
- a particularly short group delay can also be achieved with a recursive filter.
- 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 needs to be adapted to the transfer function of the noise path in the corresponding spectral band before filtering.
- a plurality of filters is provided in the filter device, from which one of them can be selected for filtering as a function of the specific 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 background noise path on the sound in a frequency to the influence of the background noise path to the sound in a different frequency.
- the spectral curve 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. While the spectral curve can namely be determined by measurements during the production of the hearing device, the spectral curve can easily be brought into congruence with an actual transfer function as it results when the hearing device is worn by the fact that when the hearing device is adapted for a user only the scaling factor has to be determined.
- FIG 2 an ear with an auricle 6 and an auditory canal 7 is shown.
- a hearing aid 8 is inserted into the ear canal 7.
- a vent 9 is formed in the hearing aid 8, through which fresh air can flow into the auditory canal 7 from the surroundings of the ear. Such ventilation increases the wearing comfort for the user of the hearing aid 8 considerably.
- a sound source 10 which emits an undesired sound 11, that is to say a noise, towards the auricle 6.
- the sound 11 can penetrate through the vent 9 into the auditory canal, where it can strike an eardrum 13 of the user as an interfering sound 12.
- the sound 11 thus reaches the eardrum 13 in a purely acoustic way through the vent 9.
- the interfering sound 12 shown also represents further interfering sound which penetrates in a different way from the surroundings of the device wearer to his eardrum.
- the interfering sound 12 is attenuated in an area 14 in front of the eardrum 13 by compensation by means of a compensation sound 15 to such an extent that it can hardly be heard by the user of the hearing aid 8.
- the compensation sound 15 is superimposed on the interfering sound 12 in such a way that the sound formed by the superimposition of this sound has significantly less energy in the area 14 than the interfering sound 12 alone does.
- the sound formed from the two superimposed sounds does not have all frequencies in the area 14 away significantly less energy than the background noise 12 alone.
- the compensation is only effected for those frequencies which, on the one hand, can be perceived relatively well by the user of the hearing aid 8 and in which, on the other hand, the interfering sound 12 has a relatively high amount of energy. All of these frequencies form a spectral band.
- the compensation sound 15 is part of a sound that a listener 16 of the hearing aid 8 emits.
- the receiver 16 emits the compensation sound 15 because a compensation sound signal is additively superimposed on a useful signal that the receiver 16 converts into sound.
- the compensation sound signal is calculated from a microphone signal that a microphone 17 of the hearing aid 8 generates.
- the microphone signal is an input signal and represents the sound 11 from the user's surroundings.
- the microphone signal is filtered by means of a filter 18 of the hearing aid 8 in such a way that it has the same spectral properties as the interfering sound 12 in the mentioned spectral band.
- the compensation sound signal is then generated from the filtered microphone signal, in which the filtered signal is inverted.
- the inverting takes place by an inverter 19.
- the filter 18 and the inverter 19 work together as a compensation filter in the sense of 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 through it the Filtering and inverting are done 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 time for the filter in a specific spectral band.
- the filter 18 reproduces the spectral change of the sound 11 when it passes through the vent 9 and through the other points on the way into the auditory canal 7 only for the aforementioned spectral band. It is also taken into account that 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 property of the microphone 17. It is also taken into account that the listener 16 also causes a 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 not only a hearing aid for the user, but also acts like an active earplug, ie it compensates for the interfering sound 12 that reaches the user's eardrum 13, for example through the vent 9.
- the ambient sound 11 is recorded with the aid of the microphone 17 of the hearing aid 8 and the spectral characteristics of the microphone signal are modified by the filter 18 and the inverter 19.
- the compensation sound is then generated by means of the receiver 16 from the filtered and inverted microphone signal (compensation sound signal).
- the filter 18 In the case of the hearing aid 8, it is not possible to dimension the filter 18 in such a way that it covers the entire audio frequency range works ideally. This is because a hearing aid is not built solely for the purpose of active noise cancellation. Therefore, the components used in the hearing aid 8, that is to say for example the microphone, the earpiece, the shape of the housing and the damping materials, are not such that active noise compensation can ideally be achieved. The active noise compensation in the hearing aid 8 is therefore limited to a specific spectral band.
- the filter 18 By suitably dimensioning the filter 18, it is possible to control in which frequency band 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 sound cancellation in certain frequency bands, sound amplification takes place.
- the frequency band in which the active noise compensation works particularly well is placed in the frequency band in which the wearer of the hearing aid perceives an interfering sound relatively clearly or loudly. Conversely, the artifacts that arise in frequency ranges with poor noise compensation are masked by the hearing loss of the hearing aid wearer.
- FIG 3 is associated with FIG 2 once again illustrates how the signal of the sound 11 from the sound source 10 reaches the area 14 in the user's auditory canal on an interfering sound path 20a and on a signal path 20b.
- the interfering sound path 20a represents the unwanted transmission of the sound 11 through the vent and along the other paths from the environment into the interior of the auditory canal.
- the sound 11 reaches the area 14 as interfering sound.
- the sound 11 is in its spectral properties changed. This is done in FIG 3 symbolized by a transfer function H of the interfering sound path 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 in FIG 2 hearing aid shown 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 as well as the generation of the also in FIG 2 compensation sound 15 illustrated via the earpiece 16.
- the filter modifies the microphone signal in accordance with a transfer function H ′ of the filter 18.
- the transfer function H 'it is possible for the specific spectral band to generate a sound in the region 14 which has approximately the same spectral properties as the sound transmitted via the interfering sound path 20a.
- the correspondence is so great that only barely audible artifacts arise in the spectral band when compensated. At best, the match is perfect, so that the artifacts do not arise.
- the effect of the inverter 19 is that the signal filtered by the filter 18 in accordance with the transfer function H ′ in the spectral band has the properties of a compensation sound signal.
- the output signal of the inverter 19 is then converted using the in FIG 2
- the receiver 16 shown is converted into a compensation sound 15 and is also emitted in the direction of the area 14. In the area 14, the signals of the interfering sound paths 20a and the signal path 20b cancel each other out in the spectral band in the manner described.
- FIG 4 The circuit diagram shown of an active noise compensation in a hearing aid shows how a compensation sound signal is obtained from an input signal obtained by means of a microphone 21 can be generated, which can then be converted into a compensation sound with a receiver 22.
- the microphone signal of the microphone 21 is spectrally analyzed with a filter bank 23.
- individual bandpass filters 24a, 24b, 24c of the filter bank are shown.
- the filter bank 23 has more than the three illustrated bandpass filters 24a, 24b, 24c.
- the bandpass filters, not shown for the sake of clarity, are symbolized by ellipses.
- the signals at the outputs of the bandpass filters 24a, 24b, 24c of the filter bank 23 are compared with one another by a power meter 25.
- An output signal of a bandpass filter 24a, 24b, 24c reflects how much energy is present in a spectral band for which the corresponding bandpass filter 24a, 24b, 24c is permeable.
- the power meter 25 uses the output signals of the bandpass filters 24a, 24b, 24c to determine the spectral band in which an equipment wearer would most clearly perceive an interfering sound. Several spectral bands can also be combined.
- 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 initially weighted with a magnitude spectrum of a transfer function for the interfering sound path.
- the power meter 25 is also able to weight the information received from the bandpass filters 24a, 24b, 24c with an auditory curve of a user in such a way that the subjective volume perception of the user is also taken into account for the individual spectral bands that are passed through the bandpass filters 24a, 24b, 24c are represented. This can lead to the fact that a spectral band in which there is a relatively large amount of spectral energy of the interfering sound is nevertheless not selected by the power meter 25 because the user of the hearing aid has poor hearing in this spectral band. It can also be provided that the subjective loudness perception is further estimated by means of a psychoacoustic model.
- the selection unit 26 configures a filter unit 27 in such a way 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 various filters 29a to 29d. As in the case of the filter bank 23, not all of the filters 29a to 29d present are in the filter unit 27 FIG 4 shown.
- the filters (not shown) are again indicated by ellipses. In the in FIG 4
- the switching state of the selection switch 28 shown, the filter 29a is active.
- the form shown of the selection by means of the selection switch 28 is only a symbolic representation of the process.
- a change between the various filters 29a to 29d is actually made possible in that a filter algorithm of the filter unit 27 is configured using coefficients.
- a corresponding set of coefficients must be transferred to the filter algorithm.
- the various sets of coefficients which the filters 29a to 29d represent are stored in a table.
- the selection unit 26 makes a selection from this. As already described, this selection depends on the one determined spectral band or the spectral bands and thus in the sense of the invention dependent on the spectral distribution of the energy of the microphone signal and also on the hearing ability of the user.
- the filter unit 27 by restricting the compensation to a relatively narrow spectral band, it is possible to achieve a correct transit time for this band when processing the sound through the hearing aid. It is accepted that in other frequency ranges, that is to say outside the spectral bands determined by the computing unit 25, the compensation works suboptimally. However, this is not perceived by the user.
- the microphone signal is continuously spectrally analyzed by the filter bank 23.
- An optimal filter 29a to 29d is selected for the respective spectral distribution of the energy of the interfering sound. Switching between the coefficient sets can be done as a fading process to avoid switching artifacts.
- the filter unit 27 as a filter algorithm can also contain an adaptive filter as a whole or in part.
- the in FIG 5 The programming device 30 shown schematically is used to measure a hearing loss of a wearer of a hearing device 32 by means of an audiometer 31.
- the hearing loss is determined depending on the frequency.
- the hearing ability of the device wearer determined by means of the audiometer 31 is transmitted to an acoustician on an in FIG 5 screen, not shown, displayed as an audio curve.
- Filters 34a to 34c developed by the manufacturer of hearing aid 32 are also stored in the control device.
- the filters are compensation filters within the meaning of the invention, with which an interfering sound can be compensated for in different spectral bands for the hearing aid 32 when the hearing aid is worn 32 through an in FIG 5 otoplastic, not shown, of the hearing aid 32 can penetrate the eardrum of the wearer.
- the filters can also be calculated in such a way that they effect active noise compensation for typical hearing losses determined in advance. For such typical hearing losses, spectral bands for which compensation is necessary can also be determined in advance.
- the hearing curve measured with the audiometer 31 can then be compared with the typical hearing curves. The filter is selected for that typical hearing curve which has the greatest similarity to the measured hearing curve.
- FIG 5 Ellipsis symbols symbolize that there are other filters in addition to the filters 34a to 34c shown.
- the filters are stored as sets of coefficients that can be fed to an appropriate filter algorithm. Also in FIG 5 is accordingly to FIG 4 symbolizes the selection of a set of coefficients from a list by acting on a selection switch 35. In FIG 5 the filter 34a is currently selected by the selection switch 35.
- the set of coefficients for the selected filter is transmitted to the hearing aid 32 by means of a transfer device 36.
- the set of coefficients is then stored in hearing aid 32. In the in FIG 5 In the example shown, it is the filter 34a that is dubbed.
- the transfer functions of the filters 34a to 34c only describe a basic spectral curve.
- a scaling factor is then determined with the aid of sample signals and is stored in the hearing aid. This scaling factor is applied multiplicatively to a filtered signal so that active noise compensation is actually brought about by the filtered and scaled signal.
- Diagrams D1 to D5 shown show graphs of various sizes as a function of a frequency f.
- the frequency range shown is an audio frequency range. Frequencies between 0 Hz and approximately 15000 Hz are shown here.
- Horizontal frequency axes of the individual diagrams D1 to D5 are not divided linearly so that the properties of the individual graphs explained below can be more easily represented. However, all diagrams D1 to D5 have the same non-linear division.
- a hearing curve 37 for a wearer of a hearing aid is shown in diagram D1, the method for which the in FIG 6 Diagrams D1 to D5 shown belong.
- a comparison with a hearing curve 38 of a person with normal hearing shows that the wearer of the hearing aid 37 has poorer hearing ability than a healthy person for all frequencies shown.
- the diagram D2 shows a spectral distribution 41 of the energy of a sound over the frequency.
- the sound comes from the environment of the wearer of the hearing aid and is partly Unintentionally transmitted acoustically, for example through a vent of the hearing aid, as interference sound 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 by the wearer of the hearing aid has been calculated.
- 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.
- the curve for the subjective perception 43 shows that a spectral band 44, for which the wearer of the hearing aid perceives the sound particularly clearly, lies between the area 42 in which the energy of the sound is concentrated and the area 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 device, 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 in particular for the area 44 is effected.
- the compensation filter is only determined as a function of the auditory curve 37. If the compensation filter is only determined as a function of a hearing curve, the compensation filter naturally only has to be determined once, for example when the hearing aid is being adjusted.
- a set of coefficients ie a compensation filter, is now selected as a function of the area 44 in which the sound can be perceived particularly well by the wearer of the hearing aid.
- the compensation filter for the spectral band 45b is selected.
- the limits of the spectral band 45b are plotted in both diagram D3 and diagram D5 by dashed lines.
- the diagram D5 shows a transfer function 46 of that filter which belongs to the set of coefficients for the spectral band 45b. Furthermore, a transfer function 47 of an interfering sound path is shown in diagram D5, via which the sound arrives acoustically from the surroundings of the wearer of the hearing aid as interfering sound to his eardrum. As can be seen from a comparison of the two transfer functions 46 and 47, the two transfer functions almost coincide in the region of the spectral band 45b. This makes it possible in the spectral band 45b with a filter unit that has the appropriate set of coefficients is used to generate a compensation sound signal from a microphone signal representing the sound.
- the limits of a spectral band do not have to be sharp limits.
- the limits are a transition area in which a deviation of the transfer function 46 of the compensation filter from the transfer function 47 of the interfering sound path gradually increases.
- a threshold value can be set for the deviation, for example, which can be determined, for example, as a function of the perceptibility or measurability of artifacts during active sound compensation.
- the examples show how a compensation of an interfering sound is made possible by means of the invention, even if the hearing device is not designed for such compensation. Very little computing capacity is required to calculate a compensation sound signal.
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Description
Die Erfindung betrifft ein Verfahren zum Kompensieren eines Störschalls bei einer Hörvorrichtung. Die Erfindung betrifft auch eine Hörvorrichtung, die zum Kompensieren eines Störschalls ausgelegt ist. Unter dem Begriff Hörvorrichtung wird hier ein Hörgerät verstanden.The invention relates to a method for compensating for an interfering sound in a hearing device. The invention also relates to a hearing device which is designed to compensate for an interfering sound. The term hearing device is understood here to mean a hearing aid.
Hörgeräte sind tragbare Hörvorrichtungen, die zur Versorgung von Hörgeschädigten dienen. Um den zahlreichen individuellen Bedürfnissen entgegenzukommen, werden unterschiedliche Bauformen von Hörgeräten wie Hinter-dem-Ohr-Hörgeräte (HdO), Hörgerät mit externem Hörer (RIC: receiver in the canal) und In-dem-Ohr-Hörgeräte (IdO), z.B. auch Concha-Hörgeräte oder Kanal-Hörgeräte (ITE - In the ear, CIC - Completely in the canal), bereitgestellt. Die beispielhaft aufgeführten Hörgeräte werden am Außenohr oder im Gehörgang getragen. Darüber hinaus stehen auf dem Markt aber auch Knochenleitungshörhilfen, implantierbare oder vibrotaktile Hörhilfen zur Verfügung. Dabei erfolgt die Stimulation des geschädigten Gehörs entweder mechanisch oder elektrisch.Hearing aids are portable hearing devices that are used to care for the hearing impaired. In order to meet the numerous individual needs, different designs 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 (ITE), e.g. Concha hearing aids or canal hearing aids (ITE - In the ear, CIC - Completely in the canal) are also provided. The hearing aids listed as examples are worn on the outer ear or in the auditory canal. In addition, bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
Hörgeräte besitzen prinzipiell als wesentliche Komponenten einen Eingangswandler, einen Verstärker und einen Ausgangswandler. Der Eingangswandler ist in der Regel ein Schallempfänger, z. B. ein Mikrofon, und/oder ein elektromagnetischer Empfänger, z. B. eine Induktionsspule. Der Ausgangswandler ist meist als elektroakustischer Wandler, z. B. Miniaturlautsprecher, oder als elektromechanischer Wandler, z. B. Knochenleitungshörer, realisiert. Der Verstärker ist üblicherweise in eine Signalverarbeitungseinheit integriert. Dieser prinzipielle Aufbau ist in
Ein von einem Mikrofon eines Hörgeräts erfasster Schall enthält auch teilweise störende Geräusche aus einer Umgebung des Geräteträgers. Diese Umgebungsgeräusche können in dem Mikrofonsignal durch die Signalverarbeitungseinheit eines Hörgeräts mittels eines Filters zur Geräuschreduktion gedämpft werden. Das gefilterte Mikrofonsignal kann anschließend von einem Hörer des Hörgeräts in ein Schallsignal gewandelt werden, der in den Gehörgang des Geräteträgers abgegeben wird. Dabei ist es wichtig, dass nicht auch ein Schall aus der Umgebung direkt, d. h. auf akustischem Weg, von der Umgebung in den Gehörgang zum Trommelfell gelangt. Ein solcher Schall, der unerwünscht aus der Umgebung direkt beispielsweise durch eine Belüftungsöffnung einer Otoplastik hindurch in den Gehörgang des Geräteträgers gelangt ist, wird im Rahmen dieser Erfindung als Störschall bezeichnet. In Form des Störschalls werden für den Geräteträger die Umgebungsgeräusche wieder hörbar, die in dem Mikrofonsignal des Hörgeräts aufwändig herausgefiltert wurden.A sound detected by a microphone of a hearing aid also partially contains disturbing noises from the surroundings of the device wearer. These ambient noises 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 listener of the hearing aid into a sound signal that is emitted into the ear canal of the device wearer. It is important that no sound from the environment is also direct, i.e. H. by acoustic means, from the environment into the ear canal to the eardrum. Such a sound, which undesirably got from the environment directly into the ear canal of the device wearer, for example through a ventilation opening of an otoplastic, is referred to as interfering sound in the context of this invention. In the form of the interfering sound, the device wearer can again hear the ambient noises that were elaborately filtered out in the microphone signal of the hearing device.
Aus dem Stand der Technik ist eine Hörgarnitur für die Luftfahrt bekannt, bei der ein Umgebungsschall mittels eines Kompensationsschalls breitbandig kompensiert wird. Dazu wird ein Umgebungsschall mit dem Kompensationsschall im Gehörgang eines Trägers der Hörgarnitur überlagert. Der Kompensationsschall ist dabei phaseninvers. Er gleicht damit in dem Gehörgang die Druckschwankungen aus, die ohne den Kompensationsschall durch den Umgebungsschall hervorgerufen würden. Mit anderen Worten löschen sich der Umgebungsschall und der Kompensationsschall durch ihre Überlagerung gegenseitig aus. Das Kompensieren eines Geräuschs mittels eines Kompensationsschalls wird aktive Geräuschkompensation (ANC - Active Noise Cancellation) oder allgemeiner aktive Schallkompensation genannt.A hearing set for aviation is known from the prior art, in which an ambient sound is compensated broadband by means of a compensation sound. For this purpose, an ambient sound is combined with the compensation sound in the ear canal Superimposed on the carrier of the hearing aid. The compensation sound is phase inverse. It thus compensates for the pressure fluctuations in the ear canal that would be caused by the ambient sound without the compensation sound. In other words, the ambient sound and the compensation sound cancel each other out through their superposition. The compensation of a noise by means of a compensation sound is called active noise compensation (ANC - Active Noise Cancellation) or more generally active noise compensation.
Um mit einer Hörgarnitur einen Kompensationsschall erzeugen zu können, müssen spezielle Komponenten, insbesondere spezielle Wandler, verwendet werden. Andernfalls weist ein aus den Wandlern und einem Kompensationsfilter gebildetes System eine zu große Gruppenlaufzeit auf. Mit anderen Worten ist es ohne die speziellen Komponenten nicht möglich, einen Kompensationsschall mit einer korrekten Phase bereitzustellen.In order to be able to generate a compensation sound with a hearing set, special components, in particular special converters, have to be used. Otherwise, a system formed from the converters and a compensation filter has too long a group delay. In other words, without the special components, it is not possible to provide a compensation sound with a correct phase.
In Hörvorrichtungen, wie z. B. Hörgeräten, können meist keine speziell zum Bilden eines Kompensationsschalls ausgelegten Komponenten verwendet werden. Für Hörvorrichtungen müssen die Komponenten nämlich bereits nach anderen Gesichtspunkten optimiert sein. Als eine Folge daraus lässt sich für eine aktive Geräuschkompensation kein System mit der benötigten Gruppenlaufzeit bilden. Auch ist es meistens nicht möglich, beispielsweise bei einer Otoplastik des Hörgeräts einen Umgebungsschall stark zu dämpfen, wenn dieser z.B. durch eine Belüftungsöffnung der Otoplastik, einen sogenannten Vent, als Störschall zu einem Trommelfell eines Geräteträgers gelangt. Eine Dämpfung in einem Vent würde bedeuten, dass auch der durch den Vent ermöglichte Austausch von Luft zwischen der Umgebung des Geräteträgers und dem Gehörgang verschlechtert würde.In hearing aids such. B. hearing aids, components specially designed to generate a compensation sound can usually not be used. For hearing devices the components have to be optimized according to other aspects. As a result, it is not possible to form a system with the required group delay for active noise compensation. Also, it is mostly not possible, for example in the case of an otoplastic of the hearing aid, to strongly attenuate ambient sound when this e.g. through a ventilation opening of the otoplastic, a so-called vent, reaches an eardrum of a device wearer as interfering sound. Attenuation in a vent would mean that the exchange of air made possible by the vent between the surroundings of the device wearer and the auditory canal would also be impaired.
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Es ist Aufgabe der vorliegenden Erfindung für einen Geräteträger die Wahrnehmbarkeit eines Störschalls zu vermindern, der auf direktem, also akustischem Weg an sein Ohr dringt. Weiter ist es Aufgabe der Erfindung, eine entsprechende Hörvorrichtung bereitzustellen.It is the object of the present invention to reduce the perceptibility of an interfering sound for a device wearer, which reaches his ear in a direct, ie acoustic way. Another object of the invention is to provide a corresponding hearing device.
Die Erfindung wird mit den Gegenständen der unabhängigen Patentansprüche gelöst.The invention is achieved with the subject matter of the independent patent claims.
Erfindungsgemäß wird ein Verfahren zum Kompensieren eines Störschalls bei einem Hörgerät bereitgestellt. Dieses Verfahren umfasst die Schritte:
- Bestimmen eines spektralen Bands in Abhängigkeit von einem Hörvermögen,
- Filtern eines Eingangssignals des Hörgerätes, welches einen den Störschall (12) hervorrufenden Schall (11) repräsentiert, in dem spektralen Band gemäß einer Übertragungsfunktion, die in dem spektralen Band einer Übertragungsfunktion für den Schall auf einem Störschallpfad entspricht, und
- Erzeugen eines Kompensationsschalls mit Hilfe des invertierten gefilterten Eingangssignals.
- Determining a spectral band depending on a hearing ability,
- Filtering an input signal of the hearing aid, which represents a sound (11) causing the interfering sound (12), in the spectral band according to a transfer function which corresponds in the spectral band to a transfer function for the sound on an interfering sound path, and
- Generating a compensation sound using the inverted filtered input signal.
Das Hörvermögen umfasst eine subjektive Lautheitswahrnehmung durch einen Geräteträger. Eine solche Lautheitswahrnehmung kann mit an sich bekannten Verfahren der Psychoakustik ermittelt werden. Es kann sich bei dem Hörvermögen aber auch um eine Hörschwelle handeln, wie sie z.B. anhand einer Hörkurve bestimmt werden kann.The hearing ability includes a subjective loudness perception by a device wearer. Such a loudness perception can be determined using psychoacoustic methods known per se. However, the hearing ability can also be a hearing threshold, as it is e.g. can be determined using an auditory curve.
Mit dem Verfahren kann ein Kompensationsschall für eine Hörvorrichtung erzeugt werden. Eine Kompensation findet dabei nicht für alle Frequenzen statt, sondern nur für Frequenzen in demjenigen spektralen Band, in dem ein Geräteträger gemäß seinem Hörvermögen besonders gut hört und in dem beispielsweise ein Geräusch besonders viel Schallenergie aufweist. Ein solches spektrales Band kann oftmals verhältnismäßig schmal in Bezug auf den Gesamtbereich hörbarer Frequenzen sein. Das Verfahren kann auch für ein Kompensieren in mehreren spektralen Bändern ausgelegt sein.A compensation sound for a hearing device can be generated with the method. There is compensation not for all frequencies, but only for frequencies in that spectral band in which a device wearer can hear particularly well according to his hearing ability and in which, for example, a noise has a particularly high level of sound energy. Such a spectral band can often be relatively narrow in relation to the total range of audible frequencies. The method can also be designed for compensation in several spectral bands.
Der Kompensationsschall kann insbesondere auch ohne speziell dafür optimierte Gerätekomponenten erzeugt werden. Beim Filtern kann nämlich eine ungünstige Gruppenlaufzeit, die beispielsweise durch die Wandler der Hörvorrichtung verursacht wird, gegebenenfalls durch eine Gruppenlaufzeit des Filters korrigiert werden, die in dem bestimmten spektralen Band negativ ist. Eine solche Korrektur ist bei einer breitbandigen aktiven Schallkompensation unmöglich.The compensation sound can in particular also be generated without device components specially optimized for it. In the case of filtering, an unfavorable group delay, which is caused, for example, by the transducers of the hearing device, can possibly be corrected by a group delay of the filter which is negative in the specific spectral band. Such a correction is impossible with a broadband active sound compensation.
Mit dem Begriff Störschallpfad ist die Gesamtheit aller akustischen Übertragungswege gemeint, über die beispielsweise ein Umgebungsschall, oder ein signifikanter Anteil desselben, von einer Umgebung eines Geräteträgers an sein Trommelfell gelangen kann, wo er dann als Störschall im Sinne der Erfindung wahrnehmbar ist. Der Störschallpfad umfasst nicht diejenige Übertragung, die bestimmungsgemäß durch die Hörvorrichtung auf teilweise elektronischem Wege bewirkt wird.The term interfering sound path refers to the entirety of all acoustic transmission paths via which, for example, ambient sound, or a significant proportion of it, can reach his eardrum from the surroundings of a device wearer, where it can then be perceived as interfering sound within the meaning of the invention. The interfering sound path does not include that transmission that is intended to be effected by the hearing device, in part electronically.
Beim unerwünschten Vordringen des Umgebungsschalls zum Trommelfell wird der Umgebungsschall spektral verändert. Diese spektrale Veränderung wird durch eine Übertragungsfunktion des Störschallpfads beschrieben. Eine Übertragungsfunktion eines Störschallpfads kann beispielsweise von einem Hersteller durch Messungen mit an sich aus dem Stand der Technik bekannten Verfahren ermittelt werden.If the ambient sound penetrates undesirably to the eardrum, the ambient sound is changed spectrally. This spectral change is described by a transfer function of the background noise path. A transfer function of an interfering sound path can be determined, for example, by a manufacturer through measurements using methods known per se from the prior art.
Indem das Eingangssignal mit einer Übertragungsfunktion gefiltert wird, die in einem bestimmten spektralen Band der Übertragungsfunktion des Störschallpfads entspricht, weist das gefilterte Eingangssignal für das spektrale Band die gleichen spektralen Eigenschaften wie der Störschall auf. Selbstverständlich kann im Rahmen der Erfindung eine weitere Filterung des Eingangssignals vorgesehen sein, durch die beispielsweise ein Übertragungsverhalten eines Mikrofons oder eines Lautsprechers der Hörvorrichtung ausgeglichen wird.By filtering the input signal with a transfer function that corresponds to the transfer function of the noise path in a specific spectral band the filtered input signal for the spectral band has the same spectral properties as the background noise. Of course, within the scope of the invention, further filtering of the input signal can be provided, by means of which, for example, a transmission behavior of a microphone or a loudspeaker of the hearing device is compensated.
Indem das gefilterte Eingangssignal während der Filterung oder anschließend invertiert wird, ergibt sich ein Signal, aus dem ein zum Störschall phaseninverser Schall, also ein Kompensationsschall, erzeugbar ist. Die Kompensationseigenschaft ist durch das erfindungsgemäße Verfahren dabei insbesondere in dem bestimmten spektralen Band gewährleistet.The fact that the filtered input signal is inverted during or after the filtering results in a signal from which a sound that is phase-inverse to the interfering sound, i.e. a compensation sound, can be generated. The compensation property is ensured by the method according to the invention in particular in the specific spectral band.
Wenn bei dem Verfahren das spektrale Band in Abhängigkeit von der spektralen Verteilung der Energie des Störschalls oder des den Störschall hervorrufenden Schalls bestimmt wird, ergibt sich eine vorteilhafte Weiterbildung, wenn das Bestimmen des spektralen Bands periodisch wiederholt wird oder kontinuierlich erfolgt. Durch ein ständiges Anpassen des spektralen Bands an die spektrale Verteilung der Energie des zu kompensierenden Schalls ist es möglich, diesen auch dann zu kompensieren, wenn sich ein Umgebungsgeräusch in seiner spektralen Zusammensetzung schnell ändert.If, in the method, the spectral band is determined as a function of the spectral distribution of the energy of the interfering sound or the sound causing the interfering sound, an advantageous development results when the determination of the spectral band is repeated periodically or continuously. 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 this even if the spectral composition of an ambient noise changes rapidly.
Ein weiterer Vorteil ergibt sich, wenn zum Filtern in Abhängigkeit von dem spektralen Band ein Filter aus einer Mehrzahl von vorbestimmten Filtern ausgewählt wird oder ein Filter berechnet wird. Mit einem Filter sind hier all diejenigen Parameter gemeint, die zum Konfigurieren eines Filteralgorithmus nötig sind. Diese Parameter eines Filteralgorithmus werden hier auch Koeffizienten eines Filters genannt.Another advantage is obtained if a filter is selected from a plurality of predetermined filters or a filter is calculated for filtering as a function of the spectral band. A filter here means all those parameters that are necessary to configure a filter algorithm. These parameters of a filter algorithm are also called coefficients of a filter here.
Durch Bereitstellen von mehreren bereits berechneten Filtern für unterschiedliche spektrale Bänder, in denen eine Kompensation mittels des Kompensationsschalls ermöglicht werden soll, ist der Aufwand zum Berechnen eines Kompensationsschallsignals besonders gering. Ein Berechnen eines Filters in Abhängigkeit von einem spektralen Band erlaubt es, ein Filter für ein beliebiges spektrales Band bereitzustellen.By providing a plurality of already calculated filters for different spectral bands in which compensation is to be made possible by means of the compensation sound, the outlay for calculating a compensation sound signal is particularly low. Computing a filter depending on a spectral band makes it possible to provide a filter for any desired spectral band.
Eine vorteilhafte Weiterbildung des Verfahrens ergibt sich, wenn bei dem Filter die Übertragungsfunktion mit einem vorbestimmten Faktor multipliziert wird, der einen Einfluss auf die Übertragungsfunktion in dem bestimmten spektralen Band beschreibt, den ein Zusammenwirken der Hörvorrichtung mit einem Ohr eines Benutzers hat. Mittels des multiplikativen Faktors ist es möglich, das erfindungsgemäße Verfahren mit einem sehr geringen Aufwand für einen bestimmten Benutzer der Hörvorrichtung anzupassen.An advantageous further development of the method results when the transfer function is multiplied by a predetermined factor in the filter, which describes an influence on the transfer function in the specific spectral band that an interaction of the hearing device with an ear of a user has. By means of the multiplicative factor it is possible to adapt the method according to the invention with very little effort for a specific user of the hearing device.
Zu der Erfindung gehört auch ein Hörgerät mit
- einer Verarbeitungseinrichtung zum Bereitstellen eines spektralen Bands in Abhängigkeit von einem Hörvermögen,
- einer Filtereinrichtung zum Filtern eines Eingangssignals des Hörgerätes, welches einen den Störschall (12) hervorrufenden Schall (11) repräsentiert, in dem spektralen Band gemäß einer Übertragungsfunktion, die in dem spektralen Band einer Übertragungsfunktion für den Schall auf einem Störschallpfad entspricht, und
- einer Schallausgabeeinrichtung zum Erzeugen eines Kompensationsschalls mit Hilfe des invertierten gefilterten Eingangssignals.
- a processing device for providing a spectral band depending on a hearing ability,
- a filter device for filtering an input signal of the hearing aid, which represents a sound (11) causing the interfering sound (12), in the spectral band according to a transfer function which corresponds in the spectral band to a transfer function for the sound on an interfering sound path, and
- a sound output device for generating a compensation sound with the aid of the inverted filtered input signal.
Mit einer solchen Hörvorrichtung ist es möglich, einen Schall in einem bestimmten spektralen Band zu kompensieren, ohne dass dabei andere Funktionalitäten der Hörvorrichtung, wie z.B. eine Geräuschreduktion oder eine Belüftung durch einen Vent, beeinträchtigt werden.With such a hearing device it is possible to compensate for a sound in a specific spectral band without affecting other functionalities of the hearing device, e.g. noise reduction or ventilation through a vent.
Für den Fall, dass mit der Verarbeitungseinrichtung der Hörvorrichtung eine spektrale Verteilung der Energie des Schalls bestimmbar ist, ergibt sich eine vorteilhafte Weiterbildung, wenn die Verarbeitungseinrichtung eine Filterbank umfasst. Mit einer Filterbank ist die spektrale Verteilung der Schallenergie in zeitlichen Abständen von wenigen Millisekunden immer wieder neu bestimmbar. Entsprechend schnell kann somit dasjenige spektrale Band bestimmt werden, für welches durch die Filtereinrichtung ein Kompensationsschallsignal zu berechnen ist.In the event that a spectral distribution of the energy of the sound can be determined with the processing device of the hearing device, an advantageous further development results when the processing device comprises a filter bank. With a filter bank is the spectral distribution of the sound energy can be determined again and again at intervals of a few milliseconds. That spectral band can thus be determined correspondingly quickly for which a compensation sound signal is to be calculated by the filter device.
Die Hörvorrichtung wird in vorteilhafter Weise dadurch weitergebildet, dass die Filtereinrichtung ein rekursives, lineares Filtern umfasst. Durch Verwenden eines linearen Filters ergibt sich der Vorteil, dass zum Berechnen eines Kompensationsschallsignals wenig Rechenzeit benötigt wird. Ein rekursives Filter hat den Vorteil, dass besonders wenig Koeffizienten zum Nachbilden einer Übertragungsfunktion für den Schall auf einem Störschallpfad benötigt werden, so dass sich die Berechnung mit besonders wenig Rechenschritten durchführen lässt. Mit einem rekursiven Filter kann auch eine besonders geringe Gruppenlaufzeit erzielt werden.The hearing device is advantageously developed in that the filter device comprises recursive, linear filtering. Using a linear filter has the advantage that little computing time is required to calculate a compensation sound signal. A recursive filter has the advantage that particularly few coefficients are required to simulate a transfer function for the sound on an interfering sound path, so that the calculation can be carried out with particularly few computing steps. A particularly short group delay can also be achieved with a recursive filter.
Vorteilhaft ist es des Weiteren, wenn die Filtereinrichtung der Hörvorrichtung ein adaptives Filter umfasst. Damit wird es möglich, ein und dasselbe Filter für verschiedene spektrale Bänder zu nutzen. Das Filter muss lediglich vor dem Filtern in dem entsprechenden spektralen Band an die Übertragungsfunktion des Störschallpfads adaptiert werden.It is also advantageous if 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 needs to be adapted to the transfer function of the noise path in the corresponding spectral band before filtering.
Alternativ zu einem adaptiven Filter ist es auch vorteilhaft, wenn in der Filtereinrichtung eine Mehrzahl von Filtern bereitgestellt ist, aus denen zum Filtern eines davon in Abhängigkeit von dem bestimmten spektralen Band auswählbar ist. Durch Berechnen der Filter, d.h. also der Parameter oder Koeffizienten, im Voraus wird ermöglicht, das Kompensationsschallsignals sehr schnell zu berechnen.As an alternative to an adaptive filter, it is also advantageous if a plurality of filters is provided in the filter device, from which one of them can be selected for filtering as a function of the specific spectral band. By calculating the filters, i. that is, the parameter or coefficient, in advance, it is possible to calculate the compensation sound signal very quickly.
In vorteilhafter Weise wird bei der Hörvorrichtung die Übertragungsfunktion aus einem spektralen Verlauf und einem Skalierungsfaktor gebildet. Der spektrale Verlauf beschreibt dabei das Verhältnis des Einflusses des Störschallpfads auf den Schall in einer Frequenz zu dem Einfluss des Störschallpfads auf den Schall in einer anderen Frequenz. Mit anderen Worten wird durch den spektralen Verlauf lediglich die prinzipielle Form der Übertragungsfunktion betrieben. Der spektrale Verlauf und die Übertragungsfunktion können sich dabei noch um einen multiplikativen Faktor unterscheiden. Dieser multiplikative Faktor ist der Skalierungsfaktor.In the hearing apparatus, 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 background noise path on the sound in a frequency to the influence of the background noise path to the sound in a different frequency. In other words, only the basic form of the transfer function is operated by the spectral profile. The spectral curve and the transfer function can still differ by a multiplicative factor. This multiplicative factor is the scaling factor.
Durch die Aufteilung ergibt sich der Vorteil, dass die Hörvorrichtung besonders leicht an einen Benutzer angepasst werden kann. Während der spektrale Verlauf nämlich durch Messungen bei der Herstellung der Hörvorrichtung ermittelt werden kann, lässt sich der spektrale Verlauf mit einer tatsächlichen Übertragungsfunktion, wie sie sich beim Tragen der Hörvorrichtung ergibt, leicht dadurch in Deckung bringen, dass bei einem Anpassen der Hörvorrichtung für einen Benutzer lediglich der Skalierungsfaktor ermittelt werden muss.The division results in the advantage that the hearing device can be adapted particularly easily to a user. While the spectral curve can namely be determined by measurements during the production of the hearing device, the spectral curve can easily be brought into congruence with an actual transfer function as it results when the hearing device is worn by the fact that when the hearing device is adapted for a user only the scaling factor has to be determined.
Die Erfindung wird im Folgenden anhand von Beispielen näher erläutert. Dazu zeigen:
- FIG 1
- eine schematische Darstellung einer Hörvorrichtung aus dem Stand der Technik mit darin enthaltenen Komponenten,
- FIG 2
- eine Darstellung eines Gehörgangs mit einem darin befindlichen In-dem-Ohr-Hörgerät gemäß einer Ausführungsform einer erfindungsgemäßen Hörvorrichtung,
- FIG 3
- einen Signalflussgraphen für ein Schallsignal, wie er sich bei einer Ausführungsform eines erfindungsgemäßen Verfahrens zum Kompensieren eines Störschalls ergibt,
- FIG 4
- einen Schaltplan eines Hörgeräts gemäß einer Ausführungsform einer erfindungsgemäßen Hörvorrichtung,
- FIG 5
- einen Schaltplan eines Programmiergeräts für ein Hörgerät gemäß einer Ausführungsform einer erfindungsgemäßen Vorrichtung zum Anpassen einer Hörvorrichtung und
- FIG 6
- eine Zusammenstellung von Diagrammen mit Graphen von mehreren spektralen Größen, wie sie sich bei einer Ausführungsform eines erfindungsgemäßen Verfahrens zum Kompensieren eines Störschalls ergeben.
- FIG 1
- a schematic representation of a hearing device from the prior art with components contained therein,
- FIG 2
- a representation of an auditory canal with an in-the-ear hearing aid located therein according to an embodiment of a hearing device according to the invention,
- FIG 3
- a signal flow graph for a sound signal, as it results in an embodiment of a method according to the invention for compensating for an interfering sound,
- FIG 4
- a circuit diagram of a hearing aid according to an embodiment of a hearing device according to the invention,
- FIG 5
- a circuit diagram of a programming device for a hearing device according to an embodiment of an inventive device for adapting a hearing device and
- FIG 6
- a compilation of diagrams with graphs of several spectral variables, as they result in an embodiment of a method according to the invention for compensating for an interfering sound.
Die erläuterten Beispiele stellen bevorzugte Ausführungsformen der Erfindung dar.The examples explained represent preferred embodiments of the invention.
In
In der Umgebung befindet sich auch eine Schallquelle 10, die einen unerwünschten Schall 11, also ein Geräusch, zur Ohrmuschel 6 hin abstrahlt. Der Schall 11 kann durch den Vent 9 in den Gehörgang vordringen, wo er als Störschall 12 auf ein Trommelfell 13 des Benutzers treffen kann. Der Schall 11 gelangt also auf rein akustischem Weg durch den Vent 9 zum Trommelfell 13.In the vicinity there is also a
Der in
Der Störschall 12 wird in einem Bereich 14 vor dem Trommelfell 13 durch Kompensation mittels eines Kompensationsschalls 15 soweit abgeschwächt, dass er für den Benutzer des Hörgeräts 8 kaum mehr hörbar ist. Der Kompensationsschall 15 überlagert sich derart mit dem Störschall 12, dass der durch die Überlagerung dieser Schalle gebildete Schall im Bereich 14 deutlich weniger Energie aufweist, als es der Störschall 12 allein tut. Der aus den beiden überlagerten Schallen gebildete Schall weist im Bereich 14 dabei aber nicht über alle Frequenzen hinweg signifikant weniger Energie als der Störschall 12 alleine auf. Die Kompensation wird lediglich für solche Frequenzen bewirkt, die zum einen von dem Benutzer des Hörgeräts 8 verhältnismäßig gut wahrgenommen werden können und in denen zum anderen der Störschall 12 verhältnismäßig viel Energie aufweist. Die Gesamtheit dieser Frequenzen bildet ein spektrales Band.The interfering
Der Kompensationsschall 15 ist Bestandteil eines Schalls, den ein Hörer 16 des Hörgeräts 8 abstrahlt. Der Hörer 16 strahlt den Kompensationsschall 15 ab, weil einem Nutzsignal, das der Hörer 16 in Schall wandelt, ein Kompensationsschallsignal additiv überlagert ist. Das Kompensationsschallsignal wird aus einem Mikrofonsignal berechnet, dass ein Mikrofon 17 des Hörgeräts 8 erzeugt. Das Mikrofonsignal ist im Sinne der Erfindung ein Eingangssignal und repräsentiert den Schall 11 aus der Umgebung des Benutzers.The
Um aus dem Mikrofonsignal das Kompensationsschallsignal zu berechnen, wird mittels eines Filters 18 des Hörgeräts 8 das Mikrofonsignal derart gefiltert, dass es in dem erwähnten spektralen Band dieselben spektralen Eigenschaften wie der Störschall 12 aufweist. Aus dem gefilterten Mikrofonsignal wird dann das Kompensationsschallsignal erzeugt, in dem das gefilterte Signal invertiert wird. Für einen Verlauf eines Graphs des gefilterten Mikrofonsignals bedeutet dies, dass für jede Stelle des Graphen sein Vorzeichen umgekehrt wird. Für ein Spektrum des gefilterten Mikrofonsignals bedeutet dies, dass für jede Frequenz des Spektrums die Phase um 180° verändert wird. Das Invertieren erfolgt in dem Beispiel durch einen Invertierer 19. Das Filter 18 und der Invertierer 19 wirken zusammen als ein Kompensationsfilter im Sinne der Erfindung.In order to calculate the compensation sound signal from the microphone signal, the microphone signal is filtered by means of a
Das Filter 18 und der Invertierer 19 können auch zu einem Kompensationsfilter zusammengefasst werden. Die Filterfunktion des Filters 18 ist dann so beschaffen, dass durch sie das Filtern und das Invertieren zusammen erfolgt. Ein gesonderter Invertierer ist dann nicht nötig.The
Das Filter 18 ist ein rekursives, lineares Filter. Dadurch ist es möglich, eine benötigte Gruppenlaufzeit des Filters in einem bestimmten spektralen Band bereitzustellen. Das Filter 18 bildet die spektrale Veränderung des Schalls 11 beim Durchtritt durch den Vent 9 und durch die übrigen Stellen auf dem Weg in den Gehörgang 7 nur für das erwähnte spektrale Band genau nach. Dabei ist auch berücksichtigt, dass ein von dem Filter 18 zu verarbeitendes Mikrofonsignal, da ja eigentlich den Schall 11 repräsentieren soll, durch eine Übertragungseigenschaft des Mikrofons 17 verfälscht worden ist. Außerdem ist berücksichtigt, dass auch der Hörer 16 beim Wandeln des Kompensationsschallsignals in den Kompensationsschall 15 ebenfalls eine Verzerrung bewirkt. Das Filter 18 gleicht diesen Einfluss der beiden Wandler und weiterer Komponenten des Hörgeräts aus.The
Die Funktion des in
Bei dem Hörgerät 8 ist es nicht möglich, das Filter 18 derart zu dimensionieren, dass es für den gesamten Audio-Frequenzbereich ideal funktioniert. Dies liegt daran, dass ein Hörgerät nicht ausschließlich für den Zweck der aktiven Geräuschkompensation gebaut ist. Daher sind die verwendeten Komponenten des Hörgeräts 8, also beispielsweise das Mikrofon, der Hörer, die Gehäuseform und dämpfende Materialien, nicht so beschaffen, dass sich eine aktive Geräuschkompensation ideal erwirken lässt. Deshalb ist die aktive Geräuschkompensation bei dem Hörgerät 8 auf ein bestimmtes spektrales Band beschränkt.In the case of the hearing aid 8, it is not possible to dimension the
Durch geeignete Dimensionierung des Filters 18 kann gesteuert werden, in welchem Frequenzband eine aktive Geräuschkompensation besonders gut erwirkt und in welchem Frequenzband bzw. in welchen Frequenzbändern sich die aktive Geräuschkompensation suboptimal verhält. Die Konsequenz ist, dass die aktive Geräuschkompensation in gewissen Frequenzbereichen nachlässt bzw. sogar statt einer Schallauslöschung in gewissen Frequenzbändern eine Schallverstärkung stattfindet.By suitably dimensioning the
In Kombination mit dem Wissen über einen Hörverlust des Benutzers wird das Frequenzband, in dem die aktive Geräuschkompensation besonders gut arbeitet in dasjenige Frequenzband gelegt, in dem der Träger des Hörgeräts einen Störschall verhältnismäßig deutlich oder laut wahrnimmt. Umgekehrt werden die Artefakte, die in Frequenzbereichen mit schlechter Geräuschkompensation entstehen, durch den Hörverlust des Hörgeräteträgers maskiert.In combination with the knowledge of the user's hearing loss, the frequency band in which the active noise compensation works particularly well is placed in the frequency band in which the wearer of the hearing aid perceives an interfering sound relatively clearly or loudly. Conversely, the artifacts that arise in frequency ranges with poor noise compensation are masked by the hearing loss of the hearing aid wearer.
In
Der Signalpfad 20b repräsentiert den Weg des Signals des Schalls 11, wie er durch die elektronische Verarbeitung des Schalls 11 in dem in
Mittels der Übertragungsfunktion H' ist es für das bestimmte spektrale Band möglich, in dem Bereich 14 einen Schall zu erzeugen, der annähernd dieselben spektralen Eigenschaften aufweist wie der über den Störschallpfad 20a übertragene Schall. Die Übereinstimmung ist dabei so groß, dass bei einer Kompensation nur kaum hörbare Artefakte in dem spektralen Band entstehen. Günstigstenfalls ist die Übereinstimmung aber perfekt, so dass die Artefakte nicht entstehen.By means of the transfer function H 'it is possible for the specific spectral band to generate a sound in the
Durch den Invertierer 19 wird erreicht, dass das durch den Filter 18 entsprechend der Übertragungsfunktion H' gefilterte Signal in dem spektralen Band die Eigenschaften eines Kompensationsschallsignals erlangt. Das Ausgangssignal des Invertierers 19 wird anschließend mittels des in
Das in
Das Mikrofonsignal des Mikrofons 21 wird dazu mit einer Filterbank 23 spektral analysiert. In
Die Signale an den Ausgängen der Bandpassfilter 24a, 24b, 24c der Filterbank 23 werden von einem Leistungsmesser 25 miteinander verglichen. Ein Ausgangssignal eines Bandpassfilters 24a, 24b, 24c gibt dabei wieder, wie viel Energie in einem spektralen Band vorhanden ist, für welches das entsprechende Bandpassfilter 24a, 24b, 24c durchlässig ist. Der Leistungsmesser 25 ermittelt anhand der Ausgangssignale der Bandpassfilter 24a, 24b, 24c dasjenige spektrale Band, in welchem ein Geräteträger einen Störschall am deutlichsten wahrnehmen würde. Es können auch mehrere spektrale Bänder kombiniert werden.The signals at the outputs of the
Für das Bestimmen des spektralen Bands wird durch den Leistungsmesser 25 nicht unmittelbar die Verteilung der Energie herangezogen, wie sie sich an den Ausgängen der Filterbank 23 ablesen lässt. Es wird stattdessen eine spektrale Verteilung der Energie des Störschalls berechnet. Dazu wird die von der Filterbank 23 berechnete spektrale Verteilung der Energie des Mikrofonsignals zunächst mit einem Betragsspektrum einer Übertragungsfunktion für den Störschallpfad gewichtet.For the determination of the spectral band, the
Der Leistungsmesser 25 ist außerdem in der Lage, die von den Bandpassfiltern 24a, 24b, 24c empfangenen Informationen mit einer Hörkurve eines Benutzers derart zu gewichten, dass auch das subjektive Lautstärkeempfinden des Benutzers für die einzelnen spektralen Bänder berücksichtigt wird, die durch die Bandpassfilter 24a, 24b, 24c repräsentiert werden. Dies kann dazu führen, dass ein spektrales Band, in dem sich verhältnismäßig viel spektrale Energie des Störschalls befindet, dennoch nicht von dem Leistungsmesser 25 ausgewählt wird, weil der Benutzer des Hörgeräts in diesem spektralen Band ein schlechtes Hörvermögen hat. Es kann auch vorgesehen sein, das subjektive Lautheitsempfinden des Weiteren mittels eines psychoakustischen Modells zu schätzen.The
Eine Information über die ausgewählten spektralen Bänder wird von dem Leistungsmesser 25 an eine Auswahleinheit 26 übergeben. Die Auswahleinheit 26 konfiguriert eine Filtereinheit 27 in der Weise, dass das Mikrofonsignal des Mikrofons 21 nach einem Filtern durch die Filtereinheit 27 ein Kompensationsschallsignal für das von dem Leistungsmesser 25 ausgewählte spektrale Band bildet. In
Wie bereits erwähnt, ist die in
Bei der Filtereinheit 27 ist es durch ein Einschränken auf ein verhältnismäßig schmales spektrales Band für die Kompensation möglich, für dieses Band eine korrekte Laufzeit beim Prozessieren des Schalls durch das Hörgerät zu erreichen. Dabei wird hingenommen, dass in anderen Frequenzbereichen, also außerhalb der von der Recheneinheit 25 bestimmten spektralen Bänder, die Kompensation suboptimal arbeitet. Dies wird von dem Benutzer allerdings nicht wahrgenommen.In the case of the
Das Mikrofonsignal wird fortlaufend durch die Filterbank 23 spektral analysiert. Für die jeweilige spektrale Verteilung der Energie des Störschalls wird ein optimales Filter 29a bis 29d ausgewählt. Das Umschalten zwischen den Koeffizientensätzen kann zur Vermeidung von Umschaltartefakten als Umblendvorgang geschehen. Anstelle einer Tabelle mit Sätzen von Koeffizienten kann die Filtereinheit 27 als Filteralgorithmus auch als Ganzes oder zum Teil ein adaptives Filter enthalten.The microphone signal is continuously spectrally analyzed by the
Bei dem in
In dem Bediengerät sind außerdem vom Hersteller des Hörgeräts 32 entwickelte Filter 34a bis 34c gespeichert. Die Filter sind Kompensationsfilter im Sinne der Erfindung, mit denen in unterschiedlichen spektralen Bändern für das Hörgerät 32 ein Störschall kompensiert werden kann, der beim Tragen des Hörgeräts 32 durch eine in
Im Sinne der Erfindung können die Filter auch in der Weise berechnet sein, dass sie eine aktive Geräuschkompensation für typische, im Voraus ermittelte Hörverluste bewirken. Für solche typischen Hörverluste lassen sich nämlich auch im Voraus spektrale Bänder bestimmen, für die eine Kompensation nötig ist. Zum Auswählen eines Filters kann dann die mit dem Audiometer 31 gemessene Hörkurve mit den typischen Hörkurven verglichen werden. Es wird das Filter zu derjenigen typischen Hörkurve gewählt, welche die größte Ähnlichkeit zu der gemessenen Hörkurve aufweist.In the context of the invention, the filters can also be calculated in such a way that they effect active noise compensation for typical hearing losses determined in advance. For such typical hearing losses, spectral bands for which compensation is necessary can also be determined in advance. To select a filter, the hearing curve measured with the
Auch in
Der Satz von Koeffizienten zu dem ausgewählten Filter wird mittels eines Überspielgeräts 36 zum Hörgerät 32 übertragen. Im Hörgerät 32 wird der Satz von Koeffizienten dann gespeichert. In dem in
Es kann auch vorgesehen sein, sämtliche Koeffizientensätze der Filter 34a bis 34c im Hörgerät 32 selbst zu speichern und mittels des Bediengeräts 33 lediglich die Information darüber an das Hörgerät 32 zu übermitteln, welches der Filter 34a bis 34c tatsächlich benutzt werden soll.It can also be provided that all coefficient sets of the
Beim Entwurf der Filter 34a bis 34c konnte nicht berücksichtigt werden, in wieweit der spezielle Gehörgang des Trägers des Hörgeräts 32 im Zusammenwirken mit der Otoplastik des Hörgeräts 32 einen weiteren Einfluss beim Übertragen eines Umgebungsschalls in den Gehörgang hat. Es kann deshalb vorgesehen sein, dass die Übertragungsfunktionen der Filter 34a bis 34c lediglich einen prinzipiellen spektralen Verlauf beschreiben. In einem abschließendem Schritt des Anpassens des Hörgeräts 32 an den Geräteträger wird mit Hilfe von Probesignalen dann ein Skalierungsfaktor ermittelt, der in dem Hörgerät gespeichert wird. Dieser Skalierungsfaktor wird multiplikativ auf ein gefiltertes Signal angewendet, damit durch das gefilterte und skalierte Signal tatsächlich eine aktive Geräuschkompensation bewirkt wird.When designing the
Es kann auch vorgesehen sein, eine mittels des Audiometers 31 ermittelte Hörkurve dazu zu verwenden, ein Kompensationsfilter individuell für eine Hörkurve eines Geräteträgers zu entwerfen. Dies kann durch den Akustiker geschehen, der das entsprechende Programmiergerät bedient. Es kann aber auch vorgesehen sein, die ermittelte Hörkurve beispielsweise an ein Labor für Hörgeräte zu übermitteln. Ein in Abhängigkeit von der übermittelten Hörkurve und einer Übertragungsfunktion, die das Übertragungsverhalten eines Störschallpfads eines bestimmten Modells eines Hörgeräts beschreibt, kann dann ein Satz von Koeffizienten berechnet werden, der wieder an den Akustiker übermittelt wird, damit dieser den Satz von Koeffizienten in das Hörgerät überträgt.Provision can also be made to use an auditory curve determined by means of the
Die in
In dem Diagramm D1 ist eine Hörkurve 37 eines Trägers eines Hörgeräts dargestellt, wobei in dem Hörgerät das Verfahren ausgeführt wird, zu dem die in
In dem Diagramm D2 ist eine spektrale Verteilung 41 der Energie eines Schalls über der Frequenz gezeigt. Der Schall stammt aus einer Umgebung des Trägers des Hörgeräts und wird z.T. auf akustischem Wege ungewollt beispielsweise durch einen Vent des Hörgeräts als Störschall zum Trommelfell des Trägers des Hörgeräts übertragen. Bei der Verteilung 41 gibt es ein spektrales Band 42, in dem die Energie des Schalls besonders groß ist.The diagram D2 shows a
In dem Diagramm D3 ist die subjektive Wahrnehmung 43 einzelner Frequenzen des Schalls durch den Träger des Hörgeräts berechnet worden. Die subjektive Wahrnehmung 43 ergibt sich aus einer Gewichtung der Verteilung 41 der Energie des Schalls mit der Hörkurve 37 des Trägers des Hörgeräts. An der Kurve für die subjektive Wahrnehmung 43 ist zu erkennen, dass ein spektrales Band 44, für die der Träger des Hörgeräts den Schall besonders deutlich wahrnimmt, zwischen dem Bereich 42, in dem die Energie des Schalls konzentriert ist, und dem Bereich 40 liegt, in welchem der Träger des Hörgeräts verhältnismäßig gut hören kann.In diagram D3, the
Entsprechend der subjektiven Wahrnehmung 43 wird in dem Hörgerät ein Satz von Koeffizienten eines Kompensationsfilters bestimmt, mit dem sich aus einem Mikrofonsignal, welches den Schall mit der Energieverteilung 41 repräsentiert, ein Kompensationsschallsignal erzeugt werden kann. Das Kompensationsfilter ist dabei so gewählt, dass die Kompensation insbesondere für den Bereich 44 bewirkt wird. Es kann aber auch vorgesehen sein, das Kompensationsfilter nur abhängig von der Hörkurve 37 zu bestimmen. Wird das Kompensationsfilter nur abhängig von einer Hörkurve bestimmt, muss das Kompensationsfilter natürlich nur einmal, etwa bei einem Anpassen des Hörgeräts, bestimmt werden.According to the
In dem Hörgerät stehen mehrere Sätze von Koeffizienten zur Verfügung, die jeweils eine Kompensation in verschiedenen spektralen Bändern bewirken können. In dem Diagramm D4 sind für die einzelnen Sätze von Koeffizienten diejenigen Frequenzbereiche, d. h. diejenigen spektralen Bänder 45a bis 45e, eingetragen, für die jeweils ein Satz von Koeffizienten in dem Hörgerät gespeichert ist. Die spektralen Bänder. die zu weiteren Sätzen von Koeffizienten gehören, sind in dem Diagramm nicht eingetragen, um das Diagramm übersichtlich zu halten. Im Diagramm D4 ist dies durch Punkte angedeutet.Several sets of coefficients are available in the hearing aid, each of which can effect compensation in different spectral bands. In diagram D4, those frequency ranges are shown for the individual sets of coefficients; H. those
Abhängig von dem Bereich 44, in dem der Schall von dem Träger des Hörgeräts besonders gut wahrnehmbar ist, wird nun ein Satz von Koeffizienten, d.h. ein Kompensationsfilter, ausgewählt. In dem in
In dem Diagramm D5 ist eine Übertragungsfunktion 46 desjenigen Filters gezeigt, das zu dem Satz von Koeffizienten für das spektrale Band 45b gehört. Des Weiteren ist in das Diagramm D5 eine Übertragungsfunktion 47 eines Störschallpfads dargestellt, über den der Schall auf akustischem Wege von der Umgebung des Trägers des Hörgeräts als Störschall zu seinem Trommelfell gelangt. Wie aus einem Vergleich der beiden Übertragungsfunktionen 46 und 47 zu erkennen ist, stimmen die beiden Übertragungsfunktionen im Bereich des spektralen Bands 45b nahezu überein. Dadurch ist es möglich, in dem spektralen Band 45b mit einer Filtereinheit, das den entsprechenden Satz von Koeffizienten verwendet, aus einem den Schall repräsentierenden Mikrofonsignal ein Kompensationsschallsignal zu erzeugen.The diagram D5 shows a
In dem Diagramm D5 ist auch zu erkennen, dass die Grenzen eines spektralen Bands, hier des spektralen Bands 45b, keine scharfen Grenzen sein müssen. Es handelt sich bei den Grenzen um einen Übergangsbereich, in dem eine Abweichung der Übertragungsfunktion 46 des Kompensationsfilters von der Übertragungsfunktion 47 des Störschallpfads graduell immer größer wird. Um scharfe Grenzen zu erhalten, lässt sich beispielsweise ein Schwellwert für die Abweichung festlegen, der beispielsweise in Abhängigkeit von einer Wahrnehmbarkeit oder Messbarkeit von Artefakten bei der aktiven Schallkompensation bestimmt werden kann.It can also be seen in diagram D5 that the limits of a spectral band, here the
Obwohl für die Frequenzen außerhalb des spektralen Bands 45b die beiden Übertragungsfunktionen 46, 47 nicht übereinstimmen, hört der Träger des Hörgeräts dennoch keinen Störschall in diesen Frequenzen. Aus dem Graph für die subjektive Wahrnehmung 43 ist zu entnehmen, dass er in den Frequenzen außerhalb des spektralen Bands 45b einen schlecht kompensierten oder sogar verstärkten Störschall nicht wahrnimmt.Although the two
Durch die Beispiele ist gezeigt, wie mittels der Erfindung ein Kompensieren eines Störschalls ermöglicht ist, auch wenn die Hörvorrichtung nicht für ein solches Kompensieren ausgelegt ist. Für ein Berechnen eines Kompensationsschallsignals wird dabei sehr wenig Rechenkapazität benötigt.The examples show how a compensation of an interfering sound is made possible by means of the invention, even if the hearing device is not designed for such compensation. Very little computing capacity is required to calculate a compensation sound signal.
- 11
- HörgerätegehäuseHearing aid housing
- 22
- Mikrofonmicrophone
- 33
- SignalverarbeitungseinheitSignal processing unit
- 44th
- HörerListener
- 55
- Batteriebattery
- 66th
- Ohrmuschelauricle
- 77th
- GehörgangEar canal
- 88th
- HörgerätHearing aid
- 99
- VentVent
- 1010
- SchallquelleSound source
- 1111
- Schallsound
- 1212
- StörschallNoise
- 1313
- Trommelfelleardrum
- 1414th
- BereichArea
- 1515th
- KompensationsschallCompensation sound
- 1616
- HörerListener
- 1717th
- Mikrofonmicrophone
- 1818th
- Filterfilter
- 1919th
- InvertiererInverter
- 20a20a
- StörschallpfadNoise path
- 20b20b
- SignalpfadSignal path
- 2121st
- Mikrofonmicrophone
- 2222nd
- HörerListener
- 2323
- FilterbankFilter bank
- 24a, 24b, 24c24a, 24b, 24c
- BandpassfilterBand pass filter
- 2525th
- LeistungsmesserPower meter
- 2626th
- AuswahleinheitSelection unit
- 2727
- FiltereinheitFilter unit
- 2828
- AuswahlschalterSelector switch
- 29a, 29b, 29c, 29d29a, 29b, 29c, 29d
- Filterfilter
- 3030th
- ProgrammiergerätProgramming device
- 3131
- AudiometerAudiometer
- 3232
- HörgerätHearing aid
- 3333
- BediengerätControl unit
- 34a, 34b, 34c34a, 34b, 34c
- Filterfilter
- 3535
- AuswahlschalterSelector switch
- 3636
- ÜberspielgerätDubbing device
- 37, 3837, 38
- HörkurveAuditory curve
- 39, 4039, 40
- spektrales Bandspectral band
- 4141
- spektrale Verteilung der Energiespectral distribution of energy
- 4242
- spektrales Bandspectral band
- 4343
- Graph des subjektiven HörvermögensSubjective hearing graph
- 44, 45a bis 45e44, 45a to 45e
- spektrales Bandspectral band
- 46, 4746, 47
- ÜbertragungsfunktionTransfer function
- ff
- Frequenzfrequency
- D1, D2, D3, D4, D5D1, D2, D3, D4, D5
- Diagrammdiagram
- H,H'H, H '
- ÜbertragungsfunktionTransfer function
Claims (12)
- Method for compensation of an interference sound (12) in a hearing aid (8,32) by- determining a spectral band (45b) depending on a hearing ability (37),- filtering an input signal of the hearing aid (8,32), which represents a sound (11) causing the interference sound (12), in the spectral band (45b) according to a transmission function (46,H'), which is measured in the spectral band (45b) according to a transmission function (47,H) for the sound (11) on an interference sound path (20a), and- generating a compensation sound (15) by means of the input signal in inverted and filtered form.
- Method according to claim 1,
characterized in that
the spectral band (45b) is determined as a function of a spectral distribution (41) of the energy of the interference sound (12) or of a sound (11) producing the interference sound (12). - Method according to claim 2,
characterized in that
the spectral band (45b) as a function of the spectral distribution (41) of the energy of the interference sound (12) or of the sound (11) causing the interference sound (12) is determined and the determining step is repeated periodically or is continuous. - Method according to one of the preceding claims,
characterized in that
for filtering as a function of the spectral band (45b)- a filter (29a,34a) is selected from a plurality of predetermined filters (29a-29d,34a-34c); or- a filter is calculated. - Method according to one of the preceding claims,
characterized in that
during filtering, the transmission function is multiplied with a predetermined factor which describes an influence on the transmission function (H) in the specific spectral band (45b), which an interaction of the hearing aid (8,32) with an ear (6,7) of a user has. - Hearing aid (8,32) with- processing device (23,25,26) for providing a spectral band (45b) in dependence on a hearing ability (37),- a filter device (18,27) for filtering an input signal of the hearing aid (8,32), which represents a sound (11) causing the interference sound (12), in the spectral band (45b) according to a transmission function (46,H'), which in the spectral band (45b) corresponds to a transmission function (47) for the sound (11) on an interference sound (20a), and- a sound output device (16,22) for generating a compensation sound (15) using the input signal in filtered and inverted form.
- Hearing aid (8,32) according to claim 6,
characterized in that
a spectral band (45b) is generated with the processing device (23,25,26) in dependence on a spectral distribution (41) of the energy of an interference sound (12) or a sound (11) causing the interference sound (12) can be determined. - Hearing aid (8,32) according to claim 7,
characterised in that
a spectral distribution (41) of the energy of the interference sound (12) or of the sound (11) causing the interference sound (12) can be determined with the processing device (23,25,26) and the processing device (23,25,26) comprises a filter bank (23). - Hearing aid (8, 32) according to one of claims 6 to 8,
characterized in that
the filter device (18,27) comprises a recursive, linear filter. - Hearing aid (8,32) according to one of claims 6 to 9,
characterised in that
the filter device comprises an adaptive filter. - Hearing aid (8,32) according to one of claims 6 to 9,
characterized in that
a plurality of filters (29a-29d,34a-34c) is provided in said filter device (8,27), one (29a,34a) of which is selectable for filtering in dependence on the particular spectral band (45b). - Hearing aid according to one of claims 6 to 11,
characterized in that
the transmission function is formed from a spectral curve and a scaling factor.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102009012745A DE102009012745A1 (en) | 2009-03-12 | 2009-03-12 | Method for compensating for background noise in a hearing device, hearing device and method for adjusting the same |
Publications (3)
Publication Number | Publication Date |
---|---|
EP2229010A2 EP2229010A2 (en) | 2010-09-15 |
EP2229010A3 EP2229010A3 (en) | 2013-12-04 |
EP2229010B1 true EP2229010B1 (en) | 2020-08-26 |
Family
ID=42199311
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP10151957.7A Active EP2229010B1 (en) | 2009-03-12 | 2010-01-28 | Hearing aid and method for noise compensation in a hearing aid |
Country Status (4)
Country | Link |
---|---|
US (1) | US8693717B2 (en) |
EP (1) | EP2229010B1 (en) |
DE (1) | DE102009012745A1 (en) |
DK (1) | DK2229010T3 (en) |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
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DE102011087692B4 (en) * | 2011-12-05 | 2014-07-10 | Siemens Medical Instruments Pte. Ltd. | Hearing apparatus and method for improving the visibility of a portion of an input signal for a user of the hearing device |
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 (en) * | 2014-04-11 | 2015-10-16 | Parrot | AUDIO HEADSET WITH ANC ACTIVE NOISE CONTROL WITH REDUCTION OF THE ELECTRICAL BREATH |
DE102015121333A1 (en) * | 2015-12-08 | 2017-06-08 | Sennheiser Electronic Gmbh & Co. Kg | Electroacoustic transducer unit and receiver |
US10242657B2 (en) * | 2016-05-09 | 2019-03-26 | Snorehammer, Inc. | Snoring active noise-cancellation, masking, and suppression |
DE102016011719B3 (en) * | 2016-09-30 | 2017-09-07 | Rheinisch-Westfälische Technische Hochschule Aachen | Active suppression of the occlusion effect in hearing aids |
US10104459B2 (en) * | 2016-10-14 | 2018-10-16 | Htc Corporation | Audio system with conceal detection or calibration |
EP3681175B1 (en) * | 2019-01-09 | 2022-06-01 | Oticon A/s | A hearing device comprising direct sound compensation |
DK180916B1 (en) * | 2020-07-09 | 2022-06-23 | Gn Hearing As | HEARING DEVICE WITH ACTIVE VENTILATION CLICK COMPENSATION |
DE102022111300A1 (en) * | 2022-05-06 | 2023-11-09 | Elevear GmbH | Device for reducing noise when reproducing an audio signal with headphones or hearing aids and corresponding method |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2007011337A1 (en) * | 2005-07-14 | 2007-01-25 | Thomson Licensing | Headphones with user-selectable filter for active noise cancellation |
EP1940197A1 (en) * | 2006-12-27 | 2008-07-02 | Sony Corporation | Noise reducing device with controlled switching of noise reducing characteristics |
Family Cites Families (7)
Publication number | Priority date | Publication date | Assignee | Title |
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JP2894001B2 (en) * | 1991-06-06 | 1999-05-24 | 松下電器産業株式会社 | Silencer |
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 (en) | 2000-09-01 | 2003-03-10 | Nacre As | Ear terminal |
DE502006004146D1 (en) * | 2006-12-01 | 2009-08-13 | Siemens Audiologische Technik | Hearing aid with noise reduction and corresponding procedure |
GB2445984B (en) * | 2007-01-25 | 2011-12-07 | Sonaptic Ltd | Ambient noise reduction |
DK2023664T3 (en) * | 2007-08-10 | 2013-06-03 | Oticon As | Active noise cancellation in hearing aids |
-
2009
- 2009-03-12 DE DE102009012745A patent/DE102009012745A1/en not_active Withdrawn
-
2010
- 2010-01-28 DK DK10151957.7T patent/DK2229010T3/en active
- 2010-01-28 EP EP10151957.7A patent/EP2229010B1/en active Active
- 2010-03-09 US US12/719,991 patent/US8693717B2/en active Active
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2007011337A1 (en) * | 2005-07-14 | 2007-01-25 | Thomson Licensing | Headphones with user-selectable filter for active noise cancellation |
EP1940197A1 (en) * | 2006-12-27 | 2008-07-02 | Sony Corporation | Noise reducing device with controlled switching of noise reducing characteristics |
Also Published As
Publication number | Publication date |
---|---|
DE102009012745A1 (en) | 2010-09-23 |
US20100232622A1 (en) | 2010-09-16 |
DK2229010T3 (en) | 2020-11-30 |
EP2229010A2 (en) | 2010-09-15 |
EP2229010A3 (en) | 2013-12-04 |
US8693717B2 (en) | 2014-04-08 |
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