EP1830602A1 - Methode zur Erwerbung von Einstellungsparameter eines Hörgerätes, und ein Hörgerät - Google Patents

Methode zur Erwerbung von Einstellungsparameter eines Hörgerätes, und ein Hörgerät Download PDF

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EP1830602A1
EP1830602A1 EP06405088A EP06405088A EP1830602A1 EP 1830602 A1 EP1830602 A1 EP 1830602A1 EP 06405088 A EP06405088 A EP 06405088A EP 06405088 A EP06405088 A EP 06405088A EP 1830602 A1 EP1830602 A1 EP 1830602A1
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Prior art keywords
gain
signal
ear
hearing instrument
transfer
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French (fr)
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EP1830602B1 (de
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Alfred Stirnemann
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Sonova Holding AG
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Phonak AG
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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
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing
    • 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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H04R25/507—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing implemented by neural network or fuzzy logic

Definitions

  • the invention is in the field of signal processing in hearing instruments. It more particularly relates to a method for obtaining a real ear acoustic coupling quantity representative of the acoustic coupling of a hearing instrument to the user's ear, to a method for setting a fitting parameter in a digital hearing instrument, and to a hearing instrument.
  • the acoustic coupling of the hearing instrument at the ear plays an important role.
  • the acoustic coupling includes the transmission of the electrical signal from the power amplifier through receiver, hook and tubing (in the case of a behind-the-ear hearing instrument), ear mold and ear canal to the eardrum.
  • this transmission path is not directly specified. Rather, conventionally, for modeling the effective gain provided by a hearing instrument placed in an ear canal, measurements in a so-called "2cc coupler" are used. However, 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.
  • RECD Real Ear to Coupler Difference
  • the fitting software supplies a value, which depends on the hearing instrument style (whether the hearing instrument is a behind-the-ear (BTE), in-the-ear (ITE), in-the-ear-canal (ITC), completely-in-the-canal (CIC) etc. hearing instrument).
  • BTE behind-the-ear
  • ITE in-the-ear
  • ITC in-the-ear-canal
  • CIC completely-in-the-canal
  • the influences of the electro acoustic hearing instrument characteristics receiveriver, hook damping
  • Such individual differences may be up to 10-15 dB, due to the different residual ear canal volume and ear drum impedance.
  • the RECD may be corrected by the so-called vent loss to account for the effect of a vent in the earpiece of the hearing instrument.
  • An “acoustic coupling quantity” is any quantity that relates to the relation between an output of the hearing instrument and the sound impinging on the user's eardrum.
  • Acoustic coupling quantities include the RECD, the CORFIG (Coupler Response for Flat Insertion Gain), the REOG (Real Ear Open Gain), combinations of these, combinations of these with anatomical transfer quantities, and others.
  • An anatomical transfer quantity is any quantity that relates to how a given sound wave input is affected by the diffraction and reflection properties of the head, pinna, and torso, before the sound reaches the eardrum.
  • Anatomical transfer functions also called head related transfer functions, HRTFs are examples of anatomical transfer quantities and include MLE (basically the dependence of the sound level on the exact position close to the ear), and the OEG.
  • the aforementioned object is achieved by the method for obtaining a real ear acoustic coupling quantity or an anatomical transfer quantity as defined in independent claim 1.
  • the invention also concerns a method for setting a fitting parameter, and a hearing instrument.
  • a real ear acoustic coupling quantity representative of the acoustic coupling of a hearing instrument to the user's ear or an anatomical transfer quantity - for example the Real-Ear-to-Coupler-Difference (RECD), the Microphone Location Effect (MLE), the Coupler Response for Flat Insertion Gain (CORFIG), and/or the Real Ear Open Gain (REOG) - is obtained from a transfer function representative of an acoustic transfer from the receiver to the outer microphone such as a signal feedback threshold gain.
  • the obtained (predicted) quantity may be used for setting a fitting parameter of the hearing instrument, for example a gain correction.
  • the named transfer function is a transfer function from either or a combination of the receivers to either or a combination of the outer microphones.
  • the invention is based on the surprising insight that there is a relation between the individual real ear acoustic coupling and anatomical transfer quantities - indicative of the "forward" transfer of sound to the ear, towards the ear drum, such as the RECD - and transfer functions representative of an acoustic transfer from the receiver to the outer microphone ("backward” transfer) such as the feedback threshold.
  • Such "backward” transfer functions are, under certain circumstances, comparably easy to determine, and can be measured using the built-in standard components of a hearing instrument.
  • Figure 1 shows the fundamental relations between (logarithmic) gain values in the hearing instrument referring to the example of a BTE hearing instrument, where the at least one receiver is placed in the behind-the-ear component and is connected to the earpiece via hook and tubing. A feedback path via the vent is assumed.
  • Fig. 1 shows the fundamental relations between (logarithmic) gain values in the hearing instrument referring to the example of a BTE hearing instrument, where the at least one receiver is placed in the behind-the-ear component and is connected to the earpiece via hook and tubing. A feedback path via the vent.
  • 2ccG denotes the 2cc Gain (the acoustic gain realized in the 2cc coupler)
  • SENSIN the input sensitivity, which is mainly governed by the properties of the at least one microphone of the hearing instrument
  • SENSOUT the output sensitivity, which primarily depends on the properties of the at least one receiver
  • GDSP the gain produced by the digital signal processing stage
  • MLE the microphone location effect
  • r/h the influence of the coupling of the at least one receiver to the hook and the influence of the hook
  • t/m the influence of tubing and earmold
  • canal the gain in the ear canal, i.e. from the earmold to the eardrum.
  • vent path is the gain of the signal transmitted back from the ear canal through the vent to the microphone (which is the predominant cause of feedback), and "REAG” is the real ear aided gain.
  • Level A (highlighted by a dashed arrow) represents a first situation where the hearing instrument is connected to a 2cc coupler, and the acoustic gain 2ccG being the difference between the logarithmic Sound pressure level (SPL) in the 2cc coupler and the SPL in the free field is measured.
  • Level B refers to a second situation where a test signal is supplied to the at least one receiver, this situation defining the RECD.
  • Level C addresses the third situation, where the hearing instrument is inserted into the user's ear.
  • RECD r / h + t / m + canal - SENSOUT
  • vent path attenuation can be approximated by ventpath ⁇ 20 ⁇ log d 2 8 ⁇ r ⁇ l , where d is the vent diameter, l the length of the vent, and r the distance between the vent and the microphone.
  • FIG. 2 shows the measured correlation, for a variety of behind-the-ear hearing instruments worn by different persons, between the feedback threshold and the RECD, both as a function of the frequency.
  • stronger correlations are represented by dark shadings, whereas light shadings represent weak correlations.
  • the correlation between the feedback threshold and the low frequency RECD is predominantly positive, whereas for higher frequencies above 1.5-2 kHz, there is a strong negative correlation between the RECD and the feedback threshold.
  • a generalized model for example a multiple input/multiple output model, which is used to predict the acoustic coupling quantity (for example directly represented by a fitting/gain parameter) for different frequency bands.
  • the generalization does not. In other words, it is not excluded that a generalized model can possibly also account for feedback contributions by other channels, such as 'mechanical' feedback (due to vibrations of casing, human tissue, etc.) and others.
  • the invention allows to directly estimate the individual's RECD based on a measurement, which is often performed anyway when a hearing instrument is fitted. Whereas the measurement itself addresses only one parameter, the estimate incorporates effects such as vent loss, leakage, remaining ear canal volume, eardrum impedance, and tubing. Thus, systematic fitting errors are avoided, and an individual hearing instrument frequency characteristics is obtained. It is not necessary to perform laborious measurements such as the mentioned "RECD direct" measurement. Since the ordinary input microphone (or input microphones) may be used for a measurement of the feedback threshold, no extra hardware is required. If the method according to the invention further is combined with the feedback threshold measurement method of EP 1309 255 / EP 05/019858.9 , the measurement for obtaining initial hearing instrument settings is also very quick.
  • RECD other real ear acoustic coupling quantities and feedback threshold are assumed to be dependent only on the frequency for a given hearing instrument and a given user in a given surrounding. They can be represented by a corresponding curve, i.e. a function of the frequency. In practice, the curves are often represented by a number of discrete values, each representing a frequency band. In the case of more than one outer microphones, the predicted quantity may also be dependent on the direction. Of course, it is not excluded that the predicted quantity may also depend on further variables.
  • the RECD and possibly other quantities may be determined from the named transfer function by a fitting software external to the hearing instrument. This may be done during a fitting process.
  • the fitting software may supply the RECD values to the hearing instrument, which RECD values may replace the default RECD values stored in the hearing instrument. These values may then be used directly as a gain correction.
  • the computation of the RECD (or other quantity) may be done by the digital signal processor of a hearing instrument itself. This may ultimately lead to a "self-fitting" hearing instrument which may adjust itself, so that merely the desired sound level has to be actively chosen by a hearing professional or even a user. It is also not excluded that the real ear acoustic coupling quantity is represented directly by way of fitting parameter values.
  • the feedback threshold is used as an input quantity for computing a signal processing unit gain, which gain may lie below the feedback threshold.
  • fitting parameters of the hearing instrument influencing the instrument's gain in operation below the feedback threshold are set based on values obtained by a feedback threshold measurement.
  • the feedback threshold therefore, is used to influence the hearing instrument's (or its signal processing unit's) gain characteristic not only by setting a maximum gain below the feedback threshold, but for a large range of different input signal strengths (sound intensities).
  • the gain may be influenced for all sound intensities between the user's hearing threshold level and a maximum sound intensity being a threshold of noise pain or a maximum level of comfortable hearing.
  • the gain G in the signal processing unit is for example computed to be a function of the feedback threshold and further parameters, which preferably include the frequency (or frequency band) and the signal intensity and may further include the time, history, user defined settings, average signal length, cepstral values, etc.
  • the gain may further be limited by the feedback threshold as a maximum gain.
  • the feedback threshold gain has an influence on G(f) not only by setting a frequency dependent upper limit but also for G(f) values well below the feedback threshold.
  • acoustic coupling quantities may be used for influencing a hearing instrument's gain characteristics.
  • the OEG may be used not to set gain parameters of the hearing instrument, but to calculate a correction to the input signal, which correction accounts for the difference between the free field sound level and the level measured at the place of the outer microphone(s).
  • a frequency band OEG correction may be applied to the digitized electric input signal before gain values are calculated by the signal processing unit.
  • 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 hearing instrument may also be an earprotector where the output acoustic signal level may be lower than the input acoustic signal level.
  • the hearing devices addressed by the present invention are so-called active hearing devices which comprise at the input side at least one acoustic to electrical converter, such as a microphone, at the output side at least one electrical to acoustic 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 acoustic 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 devices may optionally comprise further active components including an inner acoustic-to-electric converter which is placed on the proximal side of an earpiece (in contrast to the standard outer microphones which are on the distal side of the earpiece).
  • the hearing instrument of Figure 3 comprises at least one acoustic-to-electric converter (microphone) 1. Often, two or even three acoustic-to-electric converters are available in each hearing instrument.
  • the hearing instrument further comprises a signal processing unit (SPU) 3 operable to apply a time- and/or frequency-dependent gain to the input signal or input signals S 1 resulting in an output signal S O and at least one electric-to-acoustic converter (receiver) 5.
  • SPU signal processing unit
  • the feedback path 7 is also shown in the figure.
  • a quantity representative of the real ear acoustic coupling which quantity is preferably sound level independent.
  • An example of such a quantity is the RECD.
  • the models for obtaining a real ear acoustic coupling quantity which are described in the following, all refer to the example of the RECD. It is to be noted, however, that they also apply for predicting other acoustic coupling quantities or anatomical transfer quantities such as the CORFIG, the OEG, the MLE etc.
  • Figure 4 shows the basic configuration for the estimation of the RECD in a number of frequency bands from the feedback threshold represented in a number of frequency bands. Any model by which an RECD may be calculated from the feedback threshold may be applied.
  • Figure 5 depicts a first example of such a model, namely a linear transformation of the feedback threshold spectrum to yield the RECD spectrum.
  • the linear transformation may be represented by an n x n-Matrix of constant values, where n is the number of bands.
  • the matrix is an n x m matrix.
  • N measurements of both, the feedback threshold and of the RECD are performed (for example, measurements may be performed with N different persons or with different persons in different situations).
  • the RECD may be measured using a known method such as a measurement using a probe microphone placed in the ear.
  • the system of matrix equations for the N measurements is over-determined.
  • all data are obtained using the same hearing instrument or hearing instrument type on different persons and/or under different circumstances.
  • the thus-obtained values are instrument specific or instrument-type specific. It is, however, also possible to use measurements obtained with various different hearing instruments. Then, universal values, which may be less accurate for certain situations but still are useful, are obtained.
  • the matrix M contains 400 coefficients. It may be expected that not all of them do have a real statistical significance.
  • a further model useable for the RECD prediction is therefore depicted in Figure 6 .
  • the model is, like the model of Fig. 5, based on transformation matrix.
  • the matrix In contrast to the model of Fig. 5, the matrix only comprises coefficients of a certain statistical significance.
  • the coefficients are obtained (row by row) by a stepwise regression process, where for example first a least square solution for the most significant coefficient is found, and subsequently the next significant coefficients are calculated. This procedure is terminated after a few steps, typically after 1-4 steps, depending on the desired level of accuracy.
  • Fig. 6 entails an increased modeling effort, compared to the model of Fig. 5, and is based on a nonlinear stepping process, it brings about a reliable estimation without there being the extreme outliners. Also, once the model is established, the estimation of the RECD entails very little computational cost.
  • FIG. 7 Yet a further model is shown in Figure 7 .
  • the model is based on the clustering and classification approach.
  • a number N of experimentally obtained RECD curves are clustered, i.e. classes of the real ear acoustic coupling quantity or anatomical transfer quantity are formed. This may for example be done by the well-established procedure of k-means clustering.
  • Clustering yields a limited number of RECD curves (four RECD curves in the example of Fig. 7) being the cluster means of the RECD curve clusters.
  • a classification function is established, which is for example based on the discriminant analysis.
  • prediction then includes the steps of classifying new, measured feedback threshold data in accordance with the classification function and then assigning it to the RECD curve that is the cluster means of the cluster the data have been classified to belong to.
  • This method features the substantial advantage that it brings about a well defined and controllable output, namely, the obtained RECD curve is one of a limited number - four in Fig. 7 - of known RECD curves.
  • the disadvantage is that the output is not a continuous function of the feedback threshold, and the model is non-linear. Also, the modeling effort is substantial.
  • FIG. 8 Yet another model is depicted in Figure 8 .
  • a general neural net is proposed for the linkage of input data with output values.
  • the input values will be feedback threshold values in different frequency bands, whereas the output values are RECD values in different frequency bands.
  • the neural network model is established based on measurements of both, RECD and corresponding feedback threshold curves. Methods of training so-called feedforward neural networks are known in the art and will not be described here.
  • the neural network may be implemented using appropriate hardware. Alternatively, it may be provided by means of a suitable software.
  • This model features the advantage of being capable of modeling also complex nonlinear relations.
  • the disadvantage is that the modeling does not provide a unique solution, that it is non-linear and that the modeling effort may also be substantial.
  • the generalization of this kind may be applied to all models previously described referring to Figs. 5 through 8.
  • An example relating to the linear transformation is shown in Figure 10 .
  • the transfer matrix T comprises a feedback threshold transfer constituent M as well as an additional predictor constituent M v .
  • the additional predictor variables account for a frequency dependent correction curve to be (logarithmically) added to the RECD obtained by the transfer matrix constituent M.
  • Also combinations are possible, for example the classifying of transfer matrices as in Figs. 5 and 6 according to values of predictor variables (except the feedback threshold).
  • the RECD curves (or other quantities) obtained may be used as fitting parameters or for setting fitting parameters in a hearing instrument.
  • the curve is evaluated by or is supplied to the signal processing stage and preferably has an influence on the effective gain values. For example, if the curve reveals that the real ear acoustic signal in a particular frequency region is suppressed stronger than average, 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 11 .
  • the RECD as a function of the frequency - represented by a curve 13 - From the curve 13, a gain correction C ( f ) is evaluated.
  • the RECD applied as 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 RECD is linear and 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 15 in the right panel of Fig. 11 illustrate a discretised 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 (or a subtraction of the stored RECD values) to the calculated gain values. Storing a number of discrete RECD or gain correction values C f is also a preferred way of storing the RECD in the signal processing unit.

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EP06405088.3A 2006-03-01 2006-03-01 Methode zur Erwerbung von Einstellungsparameter eines Hörgerätes, und ein Hörgerät Active EP1830602B1 (de)

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Cited By (7)

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EP2203000A1 (de) * 2008-12-23 2010-06-30 GN Resound A/S Adaptive Verstärkungsrückkopplungskorrektur
EP2214424A2 (de) * 2009-02-02 2010-08-04 Siemens Medical Instruments Pte. Ltd. Verfahren zur Ermittlung des akustischen Rückkopplungsverhaltens eines Hörgeräts anhand von geometrischen Daten eines Ohrs
WO2013075255A1 (en) * 2011-11-22 2013-05-30 Phonak Ag A method of processing a signal in a hearing instrument, and hearing instrument
CN104248439A (zh) * 2013-06-27 2014-12-31 深圳先进技术研究院 鼓膜声压检测方法和系统
EP2846559A1 (de) * 2013-09-05 2015-03-11 Oticon A/s Verfahren zur Durchführung einer RECD-Messung mit einer Hörhilfevorrichtung
US9712908B2 (en) 2013-11-05 2017-07-18 Gn Hearing A/S Adaptive residual feedback suppression
CN114745649A (zh) * 2022-03-22 2022-07-12 清华大学 基于耦合腔麦克风的真耳分析测试系统

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EP1624719A2 (de) 2005-09-13 2006-02-08 Phonak Ag Verfahren zur Bestimmung einer Rückkopplungsschwelle in einem Hörgerät

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EP1309255A1 (de) 2000-08-15 2003-05-14 Stephen Royle Fussumhüllung
EP1594344A2 (de) 2005-08-03 2005-11-09 Phonak Ag Verfahren zur Erlangen der Eigenschaften, und Hörgerät
EP1624719A2 (de) 2005-09-13 2006-02-08 Phonak Ag Verfahren zur Bestimmung einer Rückkopplungsschwelle in einem Hörgerät

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10602282B2 (en) 2008-12-23 2020-03-24 Gn Resound A/S Adaptive feedback gain correction
EP2203000A1 (de) * 2008-12-23 2010-06-30 GN Resound A/S Adaptive Verstärkungsrückkopplungskorrektur
EP2214424A2 (de) * 2009-02-02 2010-08-04 Siemens Medical Instruments Pte. Ltd. Verfahren zur Ermittlung des akustischen Rückkopplungsverhaltens eines Hörgeräts anhand von geometrischen Daten eines Ohrs
EP2214424A3 (de) * 2009-02-02 2015-01-07 Siemens Medical Instruments Pte. Ltd. Verfahren zur Ermittlung des akustischen Rückkopplungsverhaltens eines Hörgeräts anhand von geometrischen Daten eines Ohrs
EP2783522B1 (de) 2011-11-22 2018-07-18 Sonova AG Verfahren zur abschätzung einer akustischen übertragungsgrösse durch ein hörgerät und hörgerät dafür
WO2013075255A1 (en) * 2011-11-22 2013-05-30 Phonak Ag A method of processing a signal in a hearing instrument, and hearing instrument
US9271666B2 (en) 2011-11-22 2016-03-01 Sonova Ag Method of processing a signal in a hearing instrument, and hearing instrument
CN104248439A (zh) * 2013-06-27 2014-12-31 深圳先进技术研究院 鼓膜声压检测方法和系统
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
US9374638B2 (en) 2013-09-05 2016-06-21 Oticon A/S Method of performing an RECD measurement using a hearing assistance device
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
EP2846559A1 (de) * 2013-09-05 2015-03-11 Oticon A/s Verfahren zur Durchführung einer RECD-Messung mit einer Hörhilfevorrichtung
US9712908B2 (en) 2013-11-05 2017-07-18 Gn Hearing A/S Adaptive residual feedback suppression
CN114745649A (zh) * 2022-03-22 2022-07-12 清华大学 基于耦合腔麦克风的真耳分析测试系统
CN114745649B (zh) * 2022-03-22 2023-03-17 清华大学 基于耦合腔麦克风的真耳分析测试系统

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