EP1594344A2 - Verfahren zur Erlangen der Eigenschaften, und Hörgerät - Google Patents

Verfahren zur Erlangen der Eigenschaften, und Hörgerät Download PDF

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Publication number
EP1594344A2
EP1594344A2 EP05405460A EP05405460A EP1594344A2 EP 1594344 A2 EP1594344 A2 EP 1594344A2 EP 05405460 A EP05405460 A EP 05405460A EP 05405460 A EP05405460 A EP 05405460A EP 1594344 A2 EP1594344 A2 EP 1594344A2
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EP
European Patent Office
Prior art keywords
signal
hearing instrument
signal processing
characteristic
ear
Prior art date
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Withdrawn
Application number
EP05405460A
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English (en)
French (fr)
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EP1594344A3 (de
Inventor
Alfred Stirnemann
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Sonova Holding AG
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Phonak AG
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Publication date
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Priority to EP05405460A priority Critical patent/EP1594344A3/de
Publication of EP1594344A2 publication Critical patent/EP1594344A2/de
Publication of EP1594344A3 publication Critical patent/EP1594344A3/de
Withdrawn legal-status Critical Current

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/021—Behind the ear [BTE] hearing aids
    • H04R2225/0216—BTE hearing aids having a receiver in the ear mould
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/023—Completely in the canal [CIC] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/025—In the ear hearing aids [ITE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/15—Determination of the acoustic seal of ear moulds or ear tips of hearing devices
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

  • the invention is in the field of hearing instruments. It more particularly relates to a method of obtaining a characteristic of acoustical circumstances in an ear canal of a user, to a hearing instrument, and to a method of fabricating a hearing instrument.
  • the acoustical output of a hearing instrument as perceived by the user depends on the environment of the hearing instrument, especially on the ear canal properties.
  • measurements in a so-called "2cc coupler” are used for modeling the effective gain provided by a hearing instrument placed in an ear canal.
  • this model system merely provides an influence of an average ear canal on the effective gain provided by a hearing instrument.
  • the accuracy of such a model system is limited.
  • the difference between the signal level in the real ear and the level in the 2cc coupler is often called "Real Ear to Coupler Difference" RECD.
  • Swiss patent 678'692 teaches to place a microphone in the user's ear canal in order to measure acoustical properties. The results are analyzed by a specific device (audiometer).
  • the hearing device comprises a microphone operable to measure the acoustic pressure in the ear canal and a control circuit for real-time adjustment of the gain characteristic if the measured acoustic pressure does not correspond to a reference acoustic pressure.
  • a feedback control uses up a lot of calculation power.
  • a hearing instrument comprising at least one microphone operable to determine a sensing signal representative of an acoustic signal at a place in front of the user's eardrum is used.
  • a hearing instrument including multiple components (such as a hearing instrument comprising an in-the-ear (ITE) component (earpiece) and a behind-the-ear (BTE) component), said microphone may be physically located in the innermost component (earpiece) or may be located elsewhere and connected to the place the signal is collected from.
  • ITE in-the-ear
  • BTE behind-the-ear
  • This microphone in this text - independent of its physical location - is called “inner microphone” in contrast to the at least one “outer microphone” which converts the acoustic signal incident on the hearing instrument (or a component thereof) from the outside into an electric signal to be transformed in an output signal.
  • the inner microphone is not placed at the position from where the acoustic signal is collected, it is connected to the position by sound conducting means.
  • sound conducting means may comprise a sound conducting tube, possibly including cerumen protection and/or a specifically adapted end geometry for ideal sound incoupling.
  • the means may comprise a channel within a housing or other sound conductors.
  • the acoustic signal may for example be a signal in a closed or not closed volume between an ITE (or ITC or CIC) hearing instrument and the eardrum or a volume between an earpiece of a hearing instrument and the eardrum.
  • an acoustic signal in front of the eardrum, an acoustic signal is produced.
  • the inner microphone creates a sensing signal representative of the acoustic signal
  • the signal processing unit of the hearing instrument determines a characteristic of acoustical circumstances in the user's ear canal based thereon and memorizes values indicative of the characteristic.
  • a signal processing unit may comprise a single digital signal processor (DSP) possibly including analog-to-digital (A/D) and digital-to-analog (D/A) conversion stages.
  • DSP digital signal processor
  • An analog amplifier may be also integrated or may be provided separately. This includes, as an example, a class D amplifier that is directly fed by a pulse width modulated signal from the signal processing unit and which redundantizes a classical D/A converter.
  • the signal processing unit may comprise two or more communicatively coupled entities, for example a digital signal processor and physically separate A/D and/or D/A converters. It may also comprise a plurality of processors and/or other digital and/or analog signal processing elements.
  • the signal processing unit also comprises a data memory, which is for example integrated in the digital signal processor(s) or in another element or which may be provided as separate data memory. Different elements constituting the signal processing unit do not need to be physically grouped together but may even be distributed between different hearing instrument components.
  • the hearing instrument's signal processing unit may calculate a characteristic of the ear canal which is used for optimized signal processing, for example for adapting a gain to the individual properties of the ear canal (vent leakage, impedance, etc.). Therefore, on the one hand, a separate device for measuring ear canal characteristic is not necessary, and the user of the hearing instrument does not have to go to the hearing aid professional in order to adapt the hearing instrument to the ear canal characteristic.
  • the approach in accordance with the invention eliminates the need for a control loop - as has been presented in the state of the art - which would use up a lot of calculating power.
  • a stored characteristic may not only be used for controlling and correcting the actually perceived signal by way of a gain adjustment but may be used for other purposes as well, including diagnostic purposes, as will be explained in the following.
  • a transfer characteristic is evaluated by the hearing instrument, i.e. by the digital signal processing (DSP) unit.
  • the transfer characteristic is representative of the acoustic coupling from the processed electric signal, as presented at the DSP output, to the real-ear acoustic signal.
  • the transfer characteristic may be stored in any way suitable to store a characteristic. Examples of values representative of a transfer function include:
  • the values may for example be stored in the signal processing unit as the RECD values. Storing of RECD values for signal processing has been known in state-of-the-art hearing instruments. In state-of-the-art hearing instruments, however, the RECD values are determined indirectly during a fitting process. One advantage of the first aspect of the invention, therefore, may be to simplify the fitting process.
  • a signal representative of an output of the digital signal processing stage is compared with the sensing signal in order to obtain the transfer characteristic and to obtain a gain adjustment to the real ear situation.
  • the digital signal processing stage (DSP) output is the signal after the signal processing steps including hearing loss correction, noise reduction steps, etc.
  • the DSP output may but need not be the physical output of a signal processing 'chip'. Rather, often a signal processing chip comprises a digital-to-analog conversion stage or a processing stage transforming the digital signal into a pulse width modulated signal, which stage may be thought of as being arranged downstream of a DSP output.
  • the hearing instrument comprises
  • the quantity measuring the gain of the data acquisition stage (which gain is governed by the location of the microphones on the hearing instrument and their physical properties) is the input sensitivity SENSIN.
  • the gain of the outcoupling is governed by the output sensitivity of the receiver(s) and the properties of the real ear (impedance, etc.).
  • the output sensitivity SENSOUT of a hearing instrument is usually known for the 2cc coupler situation. The difference between this known output sensitivity and the real-ear output sensitivity is known as the RECD.
  • the individual RECD is the only unknown quantity of the system, since the input sensitivity as well as the output sensitivity on the coupler are known.
  • ACOUSTIC COUPLING is quantified.
  • the DSP gain is situation dependent. It is influenced by user chosen programs (for example direction sensitive or omnidirectional), environmental conditions (adaptive noise suppression, possibly for special kinds of noise), etc. Therefore, in general the relationship between an input signal and an output signal is non-linear.
  • the acoustic coupling as part of the pure electro-acoustic system is approximately linear and that it therefore may be viewed as independent of the sound level and as a consequence also independent of the DSP GAIN, which latter may vary dynamically depending on the situation.
  • the acoustic coupling may be characterized by an essentially time independent transfer function T ( f ), where f denotes the frequency.
  • T ( f ) the transfer function is independent of the DSP gain and at least approximately also of the acoustic signal produced by the receiver, since the DSP-output-to-real-ear-sound-pressure-transfer is at least approximately linear. The spectrum of the signal is cancelled out when the transfer function is measured.
  • the approach presented here includes using for the comparison a signal which is representative of the electric input signal of the receiver.
  • the signal used for the comparison may be the receiver input signal before Digital-to-Analog conversion and amplification, i.e. a signal at least approximately proportional to the receiver input signal.
  • the rate with which a transfer characteristic is obtained is at least 1000, preferably at least 1'000'000 times lower than the signal processing unit's sampling rate.
  • the transfer characteristic may for example be obtained only during the fitting process and/or once every day (when the hearing instrument is switched on), once every hour, upon incidence of certain events (for example initiation by the user, battery replacement, etc.), or the like.
  • the interval between updates is for example always greater than 1 s, preferably greater than 1 min. or even greater than 1 h.
  • the transfer characteristic may, as mentioned above, for example be memorized by way of storing parameters of a transfer function T ( f ). Alternately, instead of a transfer function, gain correction parameters may be directly stored, so that no explicit calculation of the transfer function T ( f ) is necessary.
  • the art provides yet further alternatives of characterizing a transfer between a (digital) electric signal and a real-ear acoustic signal, which further alternatives may also be used in accordance with the invention.
  • the transfer from the DSP output to the signal in the ear canal (the acoustic coupling) is linear, it may be characterized by comparing a DSP output representing any acoustic signal with the corresponding real ear acoustic signal.
  • an arbitrary acoustic signal may be incident on the hearing instrument at a measuring time. It is not necessary to use a particular signal with a particular frequency characteristic for this.
  • the arbitrary input signal may be replaced or supplemented by a special processor generated measuring signal supplied to the receiver. By this, the coherence and thus the quality of the measurement may be improved.
  • the measuring signals may be on a non-audible level and may provide the desired functionality nevertheless due to appropriately longer averaging.
  • Possible suited measuring signals are for example Maximum Length Sequence (MLS) signals, which as such are known in the art and are not described any further here.
  • MLS Maximum Length Sequence
  • the transfer characteristic may be used for adjusting a gain of the hearing instrument, which gain is then specifically adapted to the individual circumstances.
  • the adaptation to the individual circumstances does not necessarily cause a lot of computing power to be used. Rather, the same correction parameters may be used during a long period and in largely different circumstances, nevertheless yielding a good and appropriate correction.
  • the presence of a hearing aid professional and of special equipment is not necessary in order to make this specific adaptation.
  • the hearing instruments nowadays comprise at least two input microphones ("outer microphones" in this text) in order to enable beamforming.
  • the hearing instruments also comprise an equal number of Analog-to-Digital (A/D) converters.
  • the inner microphone does not necessitate a further A/D converter.
  • the hearing instrument comprises a switch by which alternatively the output of one outer microphone and of the inner microphone may be connected to the input of one of the A/D converters. This makes possible, that for occasional measurements of the transfer characteristic, the beamforming functionality is at least partially interrupted, and the characteristic may be measured without interrupting the hearing aid operation and without additional hardware.
  • a similar approach may be chosen for hearing instruments with only one outer microphone.
  • a single A/D converter input may be alternatively switched between the outer and the inner microphone.
  • a processor generated signal is used, and the hearing aid operation has to be interrupted.
  • this procedure for example only has to be done initially when the hearing instrument is positioned at is operating place and is therefore not even necessarily perceived by the user.
  • the transfer characteristic may, in addition to influencing the gain characteristic of the signal processing unit or as an alternative thereto, also be used for other purposes.
  • the transfer characteristic may be used for estimating the ear canal transfer function.
  • a testing probe may be placed close (closer than 5 mm) to the eardrum and used to measure the sound level there.
  • this may be done by a hearing aid professional only (due to the danger of damaging the eardrum), brings about additional efforts, and is imprecise due to the influence of the testing probe's finite size on the acoustical circumstances.
  • the ear canal transfer may be estimated based on the measured acoustic coupling. This may be done using any estimation method known in the art. It may for example be based on electro-acoustical models, statistic models, discrimination or decision tree based, neuronal networks, fuzzy logic, etc.
  • a second additional or alternative use is an estimate of the ear impedance.
  • the ear impedance is a basis for hearing instrument optimization and for modeling in general.
  • ear impedance measurement requires a laborious calibration of the system and measurement of the complex acoustic coupling transfer function.
  • the corresponding 1-microphone theory has been published in EP 1 316 783. The content of this publication is explicitly referred to, especially concerning the teaching in paragraphs [0012] to [0025] and [0027] to [0042] of the A2 publication.
  • a third additional or alternative use is an automatic on/off switch based on the measured acoustic coupling. This use is based on the insight that the acoustic coupling is characteristic of the situation where the hearing instrument is in place in or at the user's ear. As soon as the hearing instrument is removed, the acoustic coupling changes drastically, in which case the hearing instrument may switch off or switch to a standby-mode automatically. For this use, the acoustic coupling has to be measured repeatedly and permanently. This, however, does not imply the measurement to be real-time. A measurement once every split second, second, or plurality of seconds or even minutes may be sufficient.
  • the acoustic coupling is used for making a diagnosis.
  • This may be a diagnosis on the hearing instrument hard- or software or on the middle ear.
  • a clogging of the vent, the microphone or of the receiver outlet may be detected.
  • the inner microphone of a hearing instrument according to the invention may also be used to measure other transfer functions than the transfer characteristic of the path from the digital signal to the acoustic signal in the ear canal.
  • a first example of such other characteristic is the "real ear occluded gain" transfer function.
  • the user also perceives the acoustic signal bypassing the hearing instrument, through vent and guided by the human tissue, the instrument casing, etc.
  • the output-input-relationship of this bypassing signal is called the real ear occluded gain (REOG).
  • REOG real ear occluded gain
  • the electro-acoustical amplification path of the hearing instrument is switched off, and the stimulating signal corresponds to the signal incident from outside, potentially supported by an additional source.
  • a second example of such other characteristic is the measurement of the acoustical feedback limit, i.e. the maximum achievable acoustical amplification for compensating the hearing loss.
  • the acoustical feedback limit is not identical to the limit determined by the maximal DSP gain and standard RECD. It rather corresponds to the individual maximal acoustic gain.
  • the acoustical feedback limit is not primarily dependent on the acoustic coupling, but depends on the path vent (+ housing + tissue) - outcoupling - transfer to the outer microphone. This transfer is covered if the transfer from the inner microphone to the outer microphone is measured.
  • Measurement of the acoustical feedback limit in accordance with this aspect of the invention therefore, comprises supplying the receiver with a processor generated signal and comparing the sensing signal obtained by the inner microphone with the signal produced by at least one outer microphone upon incidence of the signal transmitted from the receiver back via vent, housing and human tissue.
  • hearing aid devices that are therapeutic devices improving the hearing ability of individuals, primarily according to diagnostic results.
  • Such hearing aid devices may be Behind-The-Ear (BTE) hearing aid devices or In-The-Ear (ITE) hearing aid devices (including the so called In-The-Canal (ITC) and Completely-In-The-Canal (CIC) hearing aid devices, as well as partially and fully implanted hearing aid devices).
  • BTE Behind-The-Ear
  • ITE In-The-Ear
  • ITC In-The-Canal
  • CIC Completely-In-The-Canal
  • the term stands for devices which may improve the hearing of individuals with normal hearing, e.g. in specific acoustical situations as in a very noisy environment or in concert halls, or which may even be used in the context of remote communication or of audio listening, for instance as provided by headphones.
  • the hearing devices addressed by the present invention are so-called active hearing devices which comprise at the input side at least one acoustical to electrical converter, such as a microphone, at the output side at least one electrical to acoustical converter, such as a loudspeaker (often also termed “receiver"), and which further comprise a signal processing unit for processing signals according to the output signals of the acoustical to electrical converter and for generating output signals to the electrical input of the electrical to mechanical output converter.
  • the signal processing circuit may be an analog, digital or hybrid analog-digital circuit, and may be implemented with discrete electronic components, integrated circuits, or a combination of both. In the context of this application, signal processing units comprising digital signal processing means are preferred.
  • the hearing instrument of Figure 1 comprises at least one outer acoustic-to-electric converter (microphone) 1 (often, two or even three acoustic-to-electric converters are available in each hearing instrument), a signal processing unit (SPU) 3 operable to apply a time- and/or frequency-dependent gain to the input signal or input signals S I resulting in an output signal So and at least one electric-to-acoustic converter (receiver) 5.
  • the hearing instrument further comprises an inner acoustic-to-electric converter 6.
  • FIG 2 very schematically an ear canal 8 with an inserted in-the-ear-canal component, namely an otoplastic 7, of a behind-the-ear hearing instrument is illustrated.
  • an in-the-ear-canal component or an in-the-ear component of a hearing instrument in the context of this application is also called earpiece.
  • the sound output signal is guided from the receiver to an interior of the ear canal 8 by means of a sound conducting tube 9 held by the otoplastic 7.
  • the otoplastic 7 is an element shaped to fit in the user's ear, which comprises next to holding means for holding the sound conducting tube also a vent 2 for pressure equalization.
  • the vent and, more generally, the earpiece or the hearing instrument may have any shape as such know in the art including large vents (such as IROS venting), or limited open fittings (with or without otoplastics).
  • the inner microphone 6 is integrated in the otoplastic.
  • the eardrum is denoted by 10, the volume between the eardrum and the otoplastic by 11.
  • the inner microphone may be placed in an interior of the earpiece (or the CIC, ITC, or ITE hearing instrument) and may be connected to the volume 11 by a channel. It may also be arranged adjacent to the sound conduction means from the receiver to the volume or adjacent to the vent.
  • a digital signal processor (a core part of the signal processing unit) and preferably the entire signal processing unit is placed in the behind-the-ear component (not shown), together with the outer microphone(s), the receiver, and a battery compartment.
  • the hearing instrument comprises a sensing signal transmission wire 4 connecting the inner microphone with the signal processing unit.
  • Signal transmission between the inner microphone and the signal processing unit may as an alternative be wireless, in which case, however, the in-the-ear-canal component has to comprise an energy source.
  • the inner microphone is placed in the earpiece, whereas the outer microphone and the receiver are arranged in the behind-the-ear component.
  • a sound conducting connection sound conducting tube 9
  • an electrical signal conducting connection between the inner microphone and the behind-the-ear-component.
  • the outer microphone in the earpiece, although this alternative is clearly less preferred.
  • the instrument may also be an in-the-ear (ITE) or in-the-canal (ITC) hearing instrument, including a completely-in-the-canal (CIC) hearing instrument.
  • ITE in-the-ear
  • ITC in-the-canal
  • CIC completely-in-the-canal
  • the outer microphone(s) is/are for example placed on an outside facing side of the instrument, whereas the inner microphone is placed on the inside facing the eardrum or is connected to the inside by sound conducting means.
  • the in-the-ear component is often the only constituent of the hearing instrument, i.e. the hearing instrument may consist of its in-the-ear-canal component.
  • the in-the-ear component may be an in-the-ear-canal component of the kind described in the European patent application 05 405 022.4.
  • the outer microphone 1 produces an (analog) electric signal which is the input signal S I for the signal processing unit.
  • the signal processing unit comprises a signal collecting stage 12.
  • the signal collecting stage 12 preferably includes an analog-to-digital converter and may include further functionality such as analysis, the calculation of noise reduction parameters, etc.
  • the signal processing unit further comprises a signal processing stage 13, where the input signal is transferred into a (digital) output signal. This may include having a frequency dependent gain act upon the signal, which frequency dependent gain may depend on parameters such as acoustic signal direction of incidence, signal level, detected noise levels, etc.
  • Signal collecting stage 12 and signal processing stage 13 may together have the functionality of any known or yet to be developed signal management in hearing instrument technology.
  • the frequency dependent gain may, according to a preferred embodiment of the invention, be further dependent on a transfer characteristic, as will be explained in the following.
  • the output signal DSP Out of the signal processing stage 13 is converted into an analog electric signal, amplified and converted into an acoustic signal.
  • 21 denotes a digital-to-analog converter
  • 22 an amplifier
  • 5 a receiver
  • 23 the sound conduction by tubing (if, for example, the hearing instrument is of the behind-the-ear-type) and the influence of the earmold (otoplastic).
  • conversion of the DSP Out signal into the real-ear acoustic signal in front of the eardrum is denoted by a single step “acoustic coupling” in the figure.
  • acoustic coupling As explained, for the purpose of the first aspect of the invention, it is sufficient to measure the acoustic coupling as a whole. Knowledge of the mechanisms underlying the individual steps - as represented in Fig. 4 - is not necessary.
  • the acoustic coupling 15 includes the digital-to-analog conversion and the amplification by the analog amplifier.
  • the term "acoustic coupling" therefore, in this description is used for the sum of steps leading to the conversion of the processed digital output signal into the real-ear acoustic signal in the ear canal.
  • the ear canal sound pressure level pc in the volume 11 in front of the eardrum is sensed by the inner microphone 6.
  • the sensing signal S sens output by the inner microphone 6 is compared to a signal DSP Out representative of the receiver input by an analyzer 14.
  • the transfer characteristic may for example be represented by explicitly known parameters of a transfer function T ( f ) or as an alternative by appropriate gain correction values, etc.
  • the transfer characteristic is supplied to the signal processing stage and preferably has an influence on the effective gain values.
  • the DSP may control the analyzer 14; it may for example trigger a measurement, define the measurement parameter, etc.
  • the gain calculated by the signal processing unit based on the input signal and pre-stored information is corrected by a corresponding increase in said frequency region.
  • a simplified example of an evaluation of a gain correction C ( f ) is very schematically shown in Figure 5 .
  • the acoustic coupling transfer function T ( f ) of a signal 51 is compared with an average transfer function 52 which may have been obtained as an average of a large number of measurements or by a measurement with a 2cc coupler, which is factory stored in the signal processing unit and to which the uncorrected gain calculation is adapted.
  • a gain correction C ( f ) is evaluated.
  • the gain correction may be stored in the signal processing unit and be applied to the gains evaluated thereby during operation of the hearing instrument. Since the acoustic coupling is linear and the acoustic coupling transfer function essentially time and acoustic signal independent, so is the gain correction. Therefore, applying the once evaluated gain correction C to the input signal a plurality of times always results in an appropriately corrected gain.
  • the dots 54 in the right panel of figure 5 illustrate a discretized version of the gain correction for the case the gain is evaluated discretely in a number of frequency bands. Applying the gain correction may then just be an addition of the correction values C f to the calculated gain values.
  • the correction values C f are indicative of the transfer characteristic, and storing a number of discrete gain correction values C f is also a preferred way of storing the characteristic in the signal processing unit.
  • a signal of a different stage in the signal processing may be used, for example an input signal of the signal processing stage 13 (tapped at point A in the figure).
  • the acoustic coupling is approximately linear and that it therefore may be viewed as independent of the sound level and as a consequence also independent of the operations of the signal collecting stage 12 and of the signal processing stage 13.
  • the analyzer can characterize the acoustic coupling once (or repeatedly with a repetition rate that is small compared to the sampling rate of the digital signal processor, for example during the fitting process and once every hour, or once every day), and the characterization parameters - for example parameters of a transfer function - may be stored.
  • the characteristic may in the following be used for setting an appropriate, situation adapted gain or the like.
  • FIG. 6 shows an alternative embodiment of a hearing instrument.
  • the illustrated hearing instrument is distinct from the hearing instrument of Fig. 3 in that it comprises a signal generator 17 for generating a measuring signal in order to potentially enhance the quality of the measurement.
  • the measuring signal may be admixed to the processed input signal, or it may be used instead of the latter.
  • the corresponding adding stage 18 and switch 19 are also illustrated in the figure.
  • the hearing instrument of Figure 7 is of the type comprising at least two outer microphones in order to enable beamforming.
  • Each outer microphone is allocated an Analog-to-Digital converter 31.1, 31.2 (which may be integrated in a signal processing unit and which is comprised in the signal collecting stage 12 in the above figures; if the A/D converters are not integrated, instead of two separate A/D converters, in practice often a dual A/D converter comprising two inputs and two outputs will be used).
  • the inner microphone output signal has to be analog-to-digital-converted in the case of digital signal processing.
  • Corresponding analog-to-digital converters are not shown separately in Fig. 3 and 6, but are assumed to be integrated in the analyzer 14.
  • the hearing instrument of Figure 7 comprises a switch 32 by which alternatively the output of one outer microphone 1.2 and of the inner microphone 6 may be connected to the input of one of the A/D converters.
  • the functionality of the analyzer is shown as integrated in the digital signal processor 33.
  • FIGs 8-11 illustrate different operation modes of the hearing instrument of either of the hearing instruments sketched in the previous Figures.
  • a real ear occluded gain (REOG) characteristic is measured.
  • the amplification path of the hearing instrument is switched off, and merely the output signals of the outer microphone 1 and of the inner microphone 6 are compared to provide a REOG transfer characteristic.
  • a set-up for measuring the real-ear acoustical feedback limit is shown in Figure 9 .
  • a measuring signal generated by the signal generator 17 is output via the receiver, preferably in a situation, where no or little external noise is present.
  • the analyzer compares the sensing signal S Sens by the inner microphone with the signal S I detected by the outer microphone. From this comparison, the analyzer can compute the individual maximum gain which information is used by the signal processing stage 13 in subsequent signal processing.
  • Figure 10 illustrates the estimation of the ear canal transfer characteristic. By this estimation, the difference between the real-ear sound level at the place of the inner microphone and at the position of the eardrum is addressed.
  • the ear canal transfer 41 is illustrated by a corresponding box in the figure.
  • the ear canal transfer characteristic estimator 42 is provided with appropriate means of estimating the ear canal transfer characteristic from the acoustic coupling transfer characteristic.
  • the additional processing stage 61 serves for calculating or estimating the ear impedance (IM).
  • the additional processing stage 61 determines whether or not the hearing instrument is properly worn by the user. This allows the hearing instrument to control a corresponding smart on/off-switch by which for example the consumption of electricity may be drastically reduced in case the hearing instrument is not worn.
  • the further processing stage calculates a quantity (DIAG) which may be used for diagnosing a status of either the person wearing the hearing instrument or the hearing instrument itself or both.
  • IMG a quantity

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP05405460A 2005-08-03 2005-08-03 Verfahren zum Erlangen akustischer Eigenschaften, Hörgerät und dessen Herstellungsverfahren Withdrawn EP1594344A3 (de)

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WO2006125679A3 (en) * 2006-07-13 2007-05-31 Phonak Ag Hearing device and method for supplying audio signals to a user wearing such hearing device
EP1830602A1 (de) 2006-03-01 2007-09-05 Phonak AG Methode zur Erwerbung von Einstellungsparameter eines Hörgerätes, und ein Hörgerät
WO2008017326A1 (en) * 2006-08-07 2008-02-14 Widex A/S Hearing aid, method for in-situ occlusion effect and directly transmitted sound measurement and vent size determination method
EP2056624A1 (de) * 2008-04-10 2009-05-06 Oticon A/S Verfahren zur Steuerung eines Hörgeräts und Hörgerät
EP2073570A1 (de) 2007-12-18 2009-06-24 Oticon A/S Adaptives Hörgerät und Verfahren zur Bereitstellung eines Hörgerätes
WO2010046481A1 (de) * 2008-10-24 2010-04-29 Hortmann Guenther Implantierbares hörgerät mit im innenohr implantierbarem monitorwandler
WO2010083896A1 (en) * 2009-01-23 2010-07-29 Sony Ericsson Mobile Communications Ab Acoustic in-ear detection for earpiece
US7813520B2 (en) 2006-07-13 2010-10-12 Phonak Ag Hearing device and method for supplying audio signals to a user wearing such hearing device
US8045737B2 (en) 2006-03-01 2011-10-25 Phonak Ag Method of obtaining settings of a hearing instrument, and a hearing instrument
WO2012149945A1 (en) * 2011-05-05 2012-11-08 Sony Ericsson Mobile Communications Ab Method for determining an impedance of an electroacoustic transducer and for operating an audio playback device
WO2013075255A1 (en) * 2011-11-22 2013-05-30 Phonak Ag A method of processing a signal in a hearing instrument, and hearing instrument
EP2611218A1 (de) * 2011-12-29 2013-07-03 GN Resound A/S Hörgerät mit verbesserter Ortung
CN103458347A (zh) * 2011-12-29 2013-12-18 Gn瑞声达A/S 具有改进的定位的助听器
WO2014032726A1 (en) * 2012-08-31 2014-03-06 Widex A/S Method of fitting a hearing aid and a hearing aid
EP2750410A1 (de) * 2012-12-28 2014-07-02 GN Resound A/S Hörgerät mit verbesserter Lokalisation
EP2846559A1 (de) * 2013-09-05 2015-03-11 Oticon A/s Verfahren zur Durchführung einer RECD-Messung mit einer Hörhilfevorrichtung
EP2070384B1 (de) 2007-07-27 2015-07-08 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung gesteuert durch ein perzeptives modell und entsprechendes verfahren
US9100762B2 (en) 2013-05-22 2015-08-04 Gn Resound A/S Hearing aid with improved localization
US9148733B2 (en) 2012-12-28 2015-09-29 Gn Resound A/S Hearing aid with improved localization
US9148735B2 (en) 2012-12-28 2015-09-29 Gn Resound A/S Hearing aid with improved localization
US9264811B1 (en) 2014-04-16 2016-02-16 Audyssey Laboratories EQ correction for source device impedance and output device impedance interactions
US9338561B2 (en) 2012-12-28 2016-05-10 Gn Resound A/S Hearing aid with improved localization
EP3038384A1 (de) * 2014-12-23 2016-06-29 Oticon A/s Hörgerät zur schätzung eines gegenwärtigen tatsächlichen ohr-zu-koppler-unterschieds
US9432778B2 (en) 2014-04-04 2016-08-30 Gn Resound A/S Hearing aid with improved localization of a monaural signal source
CN103503478B (zh) * 2011-05-05 2016-11-30 索尼移动通信株式会社 用于确定电声换能器的阻抗和用于操作音频播放装置的方法
CN106921904A (zh) * 2017-04-27 2017-07-04 维沃移动通信有限公司 一种耳机的音质调整方法及终端
CN109480846A (zh) * 2017-09-13 2019-03-19 大北欧听力公司 估计耳朵几何形状的方法及相关听力设备
US10939215B2 (en) 2019-03-29 2021-03-02 Sonova Ag Avoidance of user discomfort due to pressure differences by vent valve, and associated systems and methods
EP3787316A1 (de) * 2018-02-09 2021-03-03 Oticon A/s Hörgerät mit einer strahlformerfiltrierungseinheit zur verringerung der rückkopplung
US11202159B2 (en) 2017-09-13 2021-12-14 Gn Hearing A/S Methods of self-calibrating of a hearing device and related hearing devices
US11917372B2 (en) 2021-07-09 2024-02-27 Starkey Laboratories, Inc. Eardrum acoustic pressure estimation using feedback canceller

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EP1830602A1 (de) 2006-03-01 2007-09-05 Phonak AG Methode zur Erwerbung von Einstellungsparameter eines Hörgerätes, und ein Hörgerät
US8045737B2 (en) 2006-03-01 2011-10-25 Phonak Ag Method of obtaining settings of a hearing instrument, and a hearing instrument
US7813520B2 (en) 2006-07-13 2010-10-12 Phonak Ag Hearing device and method for supplying audio signals to a user wearing such hearing device
WO2006125679A3 (en) * 2006-07-13 2007-05-31 Phonak Ag Hearing device and method for supplying audio signals to a user wearing such hearing device
WO2008017326A1 (en) * 2006-08-07 2008-02-14 Widex A/S Hearing aid, method for in-situ occlusion effect and directly transmitted sound measurement and vent size determination method
US8059847B2 (en) 2006-08-07 2011-11-15 Widex A/S Hearing aid method for in-situ occlusion effect and directly transmitted sound measurement
AU2006347144B2 (en) * 2006-08-07 2010-08-12 Widex A/S Hearing aid, method for in-situ occlusion effect and directly transmitted sound measurement and vent size determination method
EP2070384B1 (de) 2007-07-27 2015-07-08 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung gesteuert durch ein perzeptives modell und entsprechendes verfahren
EP2073570A1 (de) 2007-12-18 2009-06-24 Oticon A/S Adaptives Hörgerät und Verfahren zur Bereitstellung eines Hörgerätes
US8320573B2 (en) 2007-12-18 2012-11-27 Oticon A/S Adaptive hearing device and method for providing a hearing aid
EP2056624A1 (de) * 2008-04-10 2009-05-06 Oticon A/S Verfahren zur Steuerung eines Hörgeräts und Hörgerät
WO2010046481A1 (de) * 2008-10-24 2010-04-29 Hortmann Guenther Implantierbares hörgerät mit im innenohr implantierbarem monitorwandler
WO2010083896A1 (en) * 2009-01-23 2010-07-29 Sony Ericsson Mobile Communications Ab Acoustic in-ear detection for earpiece
CN102293012A (zh) * 2009-01-23 2011-12-21 索尼爱立信移动通讯有限公司 耳机的耳内声检测
US8705784B2 (en) 2009-01-23 2014-04-22 Sony Corporation Acoustic in-ear detection for earpiece
CN102293012B (zh) * 2009-01-23 2016-04-13 索尼爱立信移动通讯有限公司 用于耳机的耳内声检测的设备和方法
WO2012149945A1 (en) * 2011-05-05 2012-11-08 Sony Ericsson Mobile Communications Ab Method for determining an impedance of an electroacoustic transducer and for operating an audio playback device
CN103503478A (zh) * 2011-05-05 2014-01-08 索尼爱立信移动通讯有限公司 用于确定电声换能器的阻抗和用于操作音频播放装置的方法
CN103503478B (zh) * 2011-05-05 2016-11-30 索尼移动通信株式会社 用于确定电声换能器的阻抗和用于操作音频播放装置的方法
WO2013075255A1 (en) * 2011-11-22 2013-05-30 Phonak Ag A method of processing a signal in a hearing instrument, and hearing instrument
EP2783522B1 (de) 2011-11-22 2018-07-18 Sonova AG Verfahren zur abschätzung einer akustischen übertragungsgrösse durch ein hörgerät und hörgerät dafür
US9271666B2 (en) 2011-11-22 2016-03-01 Sonova Ag Method of processing a signal in a hearing instrument, and hearing instrument
US8638960B2 (en) 2011-12-29 2014-01-28 Gn Resound A/S Hearing aid with improved localization
CN103458347A (zh) * 2011-12-29 2013-12-18 Gn瑞声达A/S 具有改进的定位的助听器
CN103458347B (zh) * 2011-12-29 2016-08-03 Gn瑞声达A/S 具有改进的定位的助听器
EP2611218A1 (de) * 2011-12-29 2013-07-03 GN Resound A/S Hörgerät mit verbesserter Ortung
WO2014032726A1 (en) * 2012-08-31 2014-03-06 Widex A/S Method of fitting a hearing aid and a hearing aid
US9693159B2 (en) 2012-08-31 2017-06-27 Widex A/S Method of fitting a hearing aid and a hearing aid
US9148735B2 (en) 2012-12-28 2015-09-29 Gn Resound A/S Hearing aid with improved localization
US9148733B2 (en) 2012-12-28 2015-09-29 Gn Resound A/S Hearing aid with improved localization
US9338561B2 (en) 2012-12-28 2016-05-10 Gn Resound A/S Hearing aid with improved localization
EP2750410A1 (de) * 2012-12-28 2014-07-02 GN Resound A/S Hörgerät mit verbesserter Lokalisation
US9100762B2 (en) 2013-05-22 2015-08-04 Gn Resound A/S Hearing aid with improved localization
US9374638B2 (en) 2013-09-05 2016-06-21 Oticon A/S Method of performing an RECD measurement using a hearing assistance device
CN104427455A (zh) * 2013-09-05 2015-03-18 奥迪康有限公司 使用助听装置进行recd测量的方法
EP2846559A1 (de) * 2013-09-05 2015-03-11 Oticon A/s Verfahren zur Durchführung einer RECD-Messung mit einer Hörhilfevorrichtung
CN104427455B (zh) * 2013-09-05 2019-09-10 奥迪康有限公司 使用助听装置进行recd测量的方法
US9432778B2 (en) 2014-04-04 2016-08-30 Gn Resound A/S Hearing aid with improved localization of a monaural signal source
US9264811B1 (en) 2014-04-16 2016-02-16 Audyssey Laboratories EQ correction for source device impedance and output device impedance interactions
EP3038384A1 (de) * 2014-12-23 2016-06-29 Oticon A/s Hörgerät zur schätzung eines gegenwärtigen tatsächlichen ohr-zu-koppler-unterschieds
US9807522B2 (en) 2014-12-23 2017-10-31 Oticon A/S Hearing device adapted for estimating a current real ear to coupler difference
CN106921904B (zh) * 2017-04-27 2019-03-05 维沃移动通信有限公司 一种耳机的音质调整方法及终端
CN106921904A (zh) * 2017-04-27 2017-07-04 维沃移动通信有限公司 一种耳机的音质调整方法及终端
US11558700B2 (en) 2017-09-13 2023-01-17 Gn Hearing A/S Methods of estimating ear geometry and related hearing devices
EP3457714A1 (de) * 2017-09-13 2019-03-20 GN Hearing A/S Verfahren zur schätzung der ohrgeometrie und entsprechende hörgeräte
CN109480846A (zh) * 2017-09-13 2019-03-19 大北欧听力公司 估计耳朵几何形状的方法及相关听力设备
US11202159B2 (en) 2017-09-13 2021-12-14 Gn Hearing A/S Methods of self-calibrating of a hearing device and related hearing devices
CN109480846B (zh) * 2017-09-13 2024-05-28 大北欧听力公司 估计耳朵几何形状的方法及相关听力设备
EP3787316A1 (de) * 2018-02-09 2021-03-03 Oticon A/s Hörgerät mit einer strahlformerfiltrierungseinheit zur verringerung der rückkopplung
US11363389B2 (en) 2018-02-09 2022-06-14 Oticon A/S Hearing device comprising a beamformer filtering unit for reducing feedback
CN115119125A (zh) * 2018-02-09 2022-09-27 奥迪康有限公司 一种听力装置
US10939215B2 (en) 2019-03-29 2021-03-02 Sonova Ag Avoidance of user discomfort due to pressure differences by vent valve, and associated systems and methods
US11647342B2 (en) 2019-03-29 2023-05-09 Sonova Ag Avoidance of user discomfort due to pressure differences by vent valve, and associated systems and methods
US11343616B2 (en) 2019-03-29 2022-05-24 Sonova Ag Avoidance of user discomfort due to pressure differences by vent valve, and associated systems and methods
US11917372B2 (en) 2021-07-09 2024-02-27 Starkey Laboratories, Inc. Eardrum acoustic pressure estimation using feedback canceller

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