Patent Application
20130223634
The present application relates to binaural fitting of hearing aids. The disclosure relates specifically to a method of fitting a binaural hearing aid system to a user. The application furthermore relates to a binaural hearing aid system, to a hearing aid fitting system and to a hearing aid system.
The disclosure may e.g. be useful in applications such as binaural hearing aid systems fitted to a user with an asymmetrical hearing loss.
The auditory system of a person with an asymmetrical hearing loss adapts over time to the asymmetry. If the person is supplied with a binaural fitting (a hearing instrument on each ear) the standard fitting process will try to optimize the hearing of both ears independently. From an objective point of view, this may be the correct way, but due to the long term adaptation the auditory system will perceive the acoustic sensation to be asymmetrical.
Hearing impaired persons typically have a long term progression in their hearing deficit. Even normal hearing persons may perceive a different sound impression from left and right ear (due to minor hearing ability differences between the left and right ears). The human brain is used to receive different intensities or sound impression and “autocorrects” them. It is hence relevant to consider whether hearing aid users really benefit from hearing aids fully compensating their hearing disability independently on each ear (based on a monaural evaluation). Typically a fitting rationale for calculating appropriate frequency dependent gains from a user's (frequency dependent) hearing thresholds (audiogram) calculates only monaural (‘per ear’) gains, and assume that correction in case of a the binaural fitting boils down to a level adjustment to each independent calculation. The level adjustment provides that gains on both ears are reduced by a certain (identical) amount (e.g. between 0 and 5 dB). This means that a traditional fitting rationale (e.g. NAL-RP or NAL-NL2 (NAL=National Acoustic Laboratories, Australia))—in case of a binaural fitting—results in two independent fittings.
Generally the first time acceptance of hearing aids is low for various reasons. The aforementioned effect of asymmetrical hearing loss is amongst them. It is intended to reduce or avoid this effect.
WO2008109491A1 deals with an audiogram classification system including categories for configuration, severity, site of lesion and/or symmetry of an audiogram. A set of rules can be provided for selecting the categories, wherein the set of rules ignore one or more local irregularities on an audiogram.
In the present disclosure it is proposed to integrate the hearing loss (HL) data of the two ears of a person into a binaural audiogram (one audiogram representing left AND right ears) as a base for any fitting rationale. Binaural audiograms only makes sense as long as the hearing losses of the left and right ears are within certain limits of each other (‘reasonable similar’). If the differences are big (‘asymmetric loss’), the fitting rationale should calculate gains individually for each ear based on two monaural audiograms.
Use of the proposed binaural audiogram only makes sense for binaural hearing aid fittings. The scheme does not require binaural hearing aid processing (exchange of data between the hearing instruments of the binaural fitting), but may benefit from such processing.
An object of the present application is to provide an alternative scheme for fitting a binaural hearing aid system for a person with a small or moderate asymmetrical hearing loss.
In an aspect, the present application describes an algorithm to calculate the target gain for a first fit of an asymmetrical hearing loss.
Objects of the application are achieved by the invention described in the accompanying claims and as described in the following.
A method:
The general aspects of the method (algorithm) can be described by the following steps:
Provide hearing loss data for left and right ears, e.g. audiograms;
Determine the similarity of the two audiograms;
Classify the two audiograms based on their degree of similarity;
Determine the resulting binaural audiogram(s) to be used in target gain calculations for the left and right hearing instruments based on the assigned class of similarity.
In an aspect of the present application, an object of the application is achieved by a method of fitting a binaural hearing aid system to a user, the binaural hearing aid system comprising first and second hearing instruments adapted for being located at or in the right and left ear, respectively, of a user, the first and second hearing instruments being adapted to apply a frequency dependent gain to an input signal according to a user's hearing impairment, and for presenting an enhanced output signal to the user. The method comprises, providing first hearing loss data for a right ear of a user;
providing second hearing loss data for a left ear of a user;
determining a hearing loss difference measure indicative of a difference between said first and second hearing loss data;
classifying the degree of similarity of the first and second hearing loss data based on said hearing loss difference measure into at least two different hearing loss classes SIMILAR and DIFFERENT;
determining basic hearing loss data to form the basis for calculating sets of frequency dependent target gain values for each of the first and second hearing instruments depending on said hearing loss classes, wherein said basic hearing loss data are identical for the first and second hearing instruments, if said hearing loss class is SIMILAR; and calculating the sets of frequency dependent target gain values for each of the first and second hearing instruments based on said basic hearing loss data.
An advantage of the method is that it may increase the first time acceptance of the hearing aid system compared to previous fitting schemes.
The hearing loss of (an ear of) a user at a particular frequency is defined as the deviation in hearing threshold from the hearing threshold of a normally hearing person. Hearing loss is typically graphically illustrated in an audiogram, where a user's hearing loss has been measured at a number of frequencies over the frequency range of interest (typically below 8 kHz).
An audiogram of an ear of a user shows the hearing loss (in dB HL) versus frequency (typically depicted on a logarithmic scale). In other words an audiogram illustrates the deviation from normal hearing in that it graphically depicts the hearing threshold at the ear in question minus the hearing threshold of a normal hearing person (in dB).
The term ‘target gain’ is intended to indicate a (frequency dependent) gain that ideally should be applied to an input signal of a hearing instrument for a specific ear of a given user (for whom the target gain values are specifically calculated, based on the user's hearing loss) to compensate for the user's hearing impairment. In a practical situation, this target gain value (sometimes termed the ‘requested gain’) may differ from the actually applied gain. This can have a variety of causes, e.g. risk of feedback (lowering the intended gain to avoid howl) or compression (attenuating the input signal for high level inputs) or noise reduction (gain may be suppressed to avoid amplifying (unwanted) noise). In other words the target gain may be ‘overridden’ on request of other algorithms (or sensors) having other foci than applying an appropriate gain for compensating the user's hearing impairment.
In an embodiment, the target gains of a particular hearing instrument are determined from the hearing loss (or corresponding hearing threshold) data using conventional hearing threshold based prescription rules. In an embodiment, the target gains of a particular hearing instrument are determined using a fitting algorithm, such as NAL-RP, NAL-NL2 (National Acoustic Laboratories, Australia), DSL (National Centre for Audiology, Ontario, Canada), ASA (American Seniors Association), VAC (Veterans Affairs Canada), etc., using hearing threshold or hearing loss data.
Typically, the fitting algorithm is executed on a separate processing device, e.g. a PC, having a communication interface (e.g. a programming interface, e.g. a wireless interface) to the binaural hearing aid system (e.g. to each of the hearing instruments) whereby the appropriate frequency dependent target gain for the hearing instrument in question is determined. The target gains may subsequently be transferred to the hearing instrument in question (e.g. via the programming interface). Alternatively, the hearing loss data may be transferred to the hearing instruments via the programming interface and the target gains may be determined in the hearing instruments (e.g. by executing a specific ‘fitting algorithm’ in the hearing instruments using the hearing loss data as inputs).
In an embodiment, the hearing loss data for each ear of the user are recorded based on measurement of the user's hearing threshold at a number NHL of predetermined frequencies.
In an embodiment, the hearing loss data to form the basis for calculating sets of frequency dependent target gain values for the two hearing instruments of a binaural hearing aid system by classifying the similarity of audiograms for the left and right ears of a user are based on air conduction hearing loss data (ACHL(f)).
In an embodiment, a so-called bone conduction hearing threshold (BCHL(f)) is determined for the left and right ears of the user.
In an embodiment, a conductive hearing loss (the ‘air-bone gap’, ABG(f)) is determined for the left and right ears of the user as the difference between the air conduction and bone conduction hearing thresholds (ABG(f)=ACHL(f)−BCHL(f), [dB HL]).
In an embodiment the method comprises identifying audiograms exhibiting a conductive hearing loss smaller than a predefined value (e.g. represented by an ABG-measure, ABGM). In an embodiment, the ABG-measure for a given ear is a sum of ABG(fi)-values, [dB HL], i=1, 2, . . . , NHL, NHL being a number frequencies contributing to the ABG-measure, ABGM being smaller than a predefined value ABGMpd). Preferably, cases that do not fulfill such criterion are handled separately (i.e. each ear is treated individually as recommended by today's fitting rationals), because such losses may have different causes that need different treatment.
In an embodiment, the hearing loss difference measure HLDM depends on the difference between the values of hearing losses of the first and second ears HL1(f)−HL2(f) determined at a number NHLDM of frequencies.
The classification of the hearing loss difference between the right and left ears is used to determine the target gain values in the left and right hearing instruments. In an embodiment, classification of the hearing loss difference between the right and left ears is used to determine the time development of the gain values in the left and right hearing instruments from initial gain values to the target gain values (e.g. the modification algorithm). In an embodiment, a rate of change of initial gains towards target gains is controlled in dependence of the ‘classification’ of the hearing loss difference, e.g. slower the larger the difference.
In an embodiment, hearing loss data for each ear of a user are recorded (e.g. by an audiologist) based on measurement of the user's hearing threshold at a number (NHL) of predetermined frequencies, e.g. at f1=250 Hz, f2=500 Hz, f3=1 kHz, f4=2 kHz, f5=4 kHz, f6=8 kHz (here NHL=6). The hearing loss may be determined at a larger or smaller number NHL of frequencies than 6.
In an embodiment, NHLDM is equal to 1. In general, however, NHLDM is larger than 1. In an embodiment, NHLDM is equal to NHL. In an embodiment, the hearing loss difference measure is determined as a sum of said differences, e.g.
HLDM
SUM
=SUMi[|HL
1(fi)−HL2(fi)|][dB], i=1−NHLDM,
where |x| denotes the absolute value of x, and SUMi[xi] denotes a summation of elements xi for all i.
Other hearing loss difference measures may be used depending on the application, e.g. a sum of hearing loss differences (without using the absolute value |x|), a sum of squares of hearing loss values, or a sum of squares of differences in hearing loss values.
In an embodiment, NHL and/or NHLDM are/is in the range from 2 to 10, e.g. equal to 5 or 8. In an embodiment, f1=500 Hz, f2=1 kHz, f3=2 kHz, f4=3 kHz, and f5=4 kHz. In an embodiment, f1=250 Hz, f2=500 Hz, f3=1 kHz, f4=1.5 kHz, f5=2 kHz, f6=3 kHz, 17=4 kHz, and f8=6 kHz.
In an embodiment, a criterion for classifying the degree of similarity of the first and second hearing losses comprises that the hearing loss difference measure HLDM (e.g. HLDMSUM) is within predefined limits.
In an embodiment, the number NHLC of hearing loss classes is two. In an embodiment, the number NHLC of hearing loss classes is three or more.
In an embodiment, the method comprises that the hearing loss classes comprise the classes, EQUAL, SIMILAR and DIFFERENT.
In an embodiment, the first and second hearing losses are defined as being EQUAL or SIMILAR if HLDMSUM is smaller than or equal to a first predefined threshold value HLDMSUM,TH1 and DIFFERENT if HLDMSUM is larger than said first predefined threshold value HLDMSUM,TH1.
In an embodiment, the first and second hearing losses are defined as being EQUAL if HLDMSUM is smaller than or equal to a first predefined threshold value HLDMSUM,TH1 and DIFFERENT if HLDMSUM is larger than a second predefined threshold value HLDMSUM,TH2 and SIMILAR if HLDMSUM is larger than the first predefined threshold value HLDMSUM,TH1 but smaller than or equal to the second predefined threshold value HLDMSUM,TH2.
In an embodiment, the first and second hearing losses are defined as being (EQUAL or) SIMILAR if HLDMSUM divided by the number of frequencies NHLDM at which hearing loss is measured and which contribute to the hearing loss difference measure HLDMSUM is smaller than or equal to a predefined value, e.g. 20 dB, i.e. (HLDMSUM/NHLDM)≦20 dB. Other difference measures may be used, e.g. a difference between the average values AVGi(HLj) over frequency i=1, 2, . . . , NHLDM (j=1, 2), e.g. |AVGi(HL1)−AVGi(HL2)| are smaller than predefined values, e.g.≦20 dB. In an embodiment, AVGi(HLj) is a weighted average.
In an embodiment, the first and second hearing losses are defined as being EQUAL if (HLDMSUM/NHLDM) is smaller than or equal to a first predefined value, e.g. ≦12 dB. In an embodiment, the first and second hearing losses are defined as being SIMILAR if (HLDMSUM/NHLDM) is larger than a first predefined value, but smaller than or equal to a second predefined value, e.g. 12 dB<(HLDMSUM/NHLDM)≦20 dB.
In an embodiment, the first and second hearing losses are defined as being DIFFERENT if (HLDMSUM/NHLDM) is larger than a second predefined value, e.g. >20 dB.
In an embodiment, the criterion for classifying the degree of similarity of the first and second hearing losses comprises that the difference between the first and second hearing losses at one or more frequencies fi, i=1, 2, . . . , NHLDM is/are smaller than (a) predefined threshold value(s) HLD(fi)TH.
In an embodiment, the first and second hearing losses are defined as being (EQUAL or) SIMILAR if no single hearing loss difference for any of the frequencies NHLDM at which hearing loss is measured and which contribute to the hearing loss difference measure HLDMSUM is more than 30 dB (i.e. HLD(fi)≦30 dB for all i=1, 2, . . . , NHLDM).
In an embodiment, the first and second hearing losses are defined as being DIFFERENT if HLD(fi)>30 dB for at least one i=1, 2, . . . , NHLDM.
In an embodiment, the first and second hearing losses are defined as being EQUAL if HLD(fi)≦20 dB for all i=1, 2, . . . , NHLDM.
In an embodiment, the criterion for classifying the degree of similarity of the first and second hearing losses comprises that HLDMSUM is within predefined limits as well as that the difference between the first and second hearing losses at one or more frequencies fi, i=1, 2, . . . , NHLDM is/are smaller or larger than (a) predefined threshold value(s) HLD(fi)TH.
In an embodiment, different strategies for determining target gain values in the first and second hearing instruments are used for different hearing loss difference classifications. The term ‘gain strategy’ is here intended to mean the strategy for determining first and second (frequency dependent) target gains of the first and second hearing instruments based on the first and second (basic) hearing loss data.
In an embodiment, the basic hearing loss data are identical for the first and second hearing instruments, if said hearing loss class is EQUAL. In an embodiment, the first and second hearing losses being defined as being EQUAL results in applying the same target gains for fitting the first and second hearing instruments. In an embodiment, the better audiogram HL-value from both sides is used to determine the target gains (i.e. for both instruments) for hearing loss class EQUAL. Preferably, the basic hearing loss data for the hearing loss class EQUAL used in the calculation of target gain values in the first and second hearing instruments are determined as the value MIN{HL1(fi); HL2(fi)}, where MIN denotes the minimum function, HL1(fi) and HL2(fi) are the hearing loss values at the ith frequency fi for the first (right) and second (left) ears, respectively, of the user, and i=1, 2, . . . , NHL. A binaural audiogram for hearing loss class EQUAL based on these hearing loss data may thus be generated.
In an embodiment, the first and second hearing losses being defined as being SIMILAR results in applying the same target gains for fitting the first and second hearing instruments. In an embodiment, the better audiogram HL-value from both sides is used plus 1/3 of the difference between the hearing loss values of the respective ears to determine the target gains for the hearing loss class SIMILAR. Preferably, the basic hearing loss data for the hearing loss class SIMILAR used in the calculation of target gain values in the first and second hearing instruments are determined as the value MIN{HL1(fi); HL2(fi)}+(⅓)| HL1(fi)−HL2(fi) , where MIN denotes the minimum function, HL1(fi) and HL2(fi) are the hearing loss values at the ith frequency fi for the first (right) and second (left) ears, respectively, of the user, i=1, 2, . . . , NHL, and |x| denotes the absolute value of x. A binaural audiogram for hearing loss class SIMILAR based on these hearing loss data may thus be generated.
In an embodiment, said basic hearing loss data are different for the first and second hearing instruments, if said hearing loss class is DIFFERENT. Preferably, the first and second hearing losses being defined as being DIFFERENT results in applying different target gains for fitting the first and second hearing instruments. In an embodiment, the hearing loss data for the hearing loss class DIFFERENT used in the calculation of target values in the first and second hearing instruments are the respective relevant hearing loss data HL1(fi) and HL2(fi), i=1, 2, . . . , NHL for the first and second ears, respectively. Preferably, the audiogram HL-value from the respective sides are used to determine the target gains of the respective hearing instruments for hearing loss class DIFFERENT (i.e. for each instrument HI1 and HI2, the respective relevant hearing loss data HL1(fi) and HL2(fi), i=1, 2, . . . , NHL, are used to determine a target gain for the instrument in question), thus leading to different target gains for the first and second hearing instruments.
In an embodiment, the method comprises the step of storing the sets of frequency dependent target gain values, or gain values originating therefrom, for each of the first and second hearing instruments in respective memory units.
In an embodiment, the method comprises storing sets of basic gain values (e.g. equal to the target gain values or to modified target gain values) reflecting the user's hearing impairment. In each of the first and second hearing instruments current gain values may—at a specific time (during normal operation of the hearing instruments)—be determined from the stored basic gain values, but adapted to given acoustic environment conditions, e.g. based on one or more processing algorithms (e.g. noise reduction, compression, feedback, etc.).
In an embodiment, the first and second sets of stored basic gain values are equal to said sets of first and second frequency dependent target gain values, respectively. In an embodiment, the first and second sets of stored basic gain values are equal to said sets of first and second frequency dependent target gain values, respectively modified (e.g. diminished) with predefined amounts.
In an embodiment, the first and second sets of stored basic gain values are modified over a period of time (during normal operation of the hearing instruments) from initial values towards the target gain values. In an embodiment, the first and second sets of stored basic gain values are modified over a period of time according to a specific modification algorithm. This may be advantageous for a first time user of the binaural hearing aid system. In an embodiment, the frequency dependent gains applied in the first and second hearing instruments are increased (e.g. in predetermined steps) over a period of time (e.g. months) from the initial gain values towards the target gain values determined according to the present disclosure. Thereby the (typical) way of slowly increasing the gains towards intended values is combined with the fitting procedure of the present disclosure (to allow a (first time) user to get accustomed to the system over a certain period of time).
A binaural hearing aid system:
In an aspect, a binaural hearing aid system comprising first and second hearing instruments adapted for being located at or in the right and left ear, respectively, of a user is furthermore provided by the present application. Each of the first and second hearing instruments comprises an input transducer for providing an electric input signal representing an audio signal; an output transducer for converting a processed electric signal to a stimulus perceivable as sound to the user;
a forward path being defined between the input and output transducers, the forward path comprising a signal processing unit being adapted to apply time and frequency dependent gain values to an input signal according to a user's hearing impairment;
a memory unit comprising a set of target gain values;
wherein said target gain values are determined by a method described above, in the ‘detailed description of embodiments’ and in the claims.
It is intended that the process features of the method described above, in the ‘detailed description of embodiments’ and in the claims can be combined with the system, when appropriately substituted by corresponding structural features and vice versa. Embodiments of the system have the same advantages as the corresponding method.
In an embodiment, the binaural hearing aid system comprises a programming interface to a hearing aid fitting system for exchanging data between said fitting system and the binaural hearing aid system. In an embodiment, the first and second hearing instruments of the binaural hearing aid system each comprises a programming interface to a hearing aid fitting system for exchanging data between said fitting system and the binaural hearing aid system.
In an embodiment, the target gain values are transferred to the memory units of the respective first and second hearing instruments of the binaural hearing aid system via said programming interface.
In an embodiment, the sets of frequency dependent target gain values for each of the first and second hearing instruments are stored in the respective memory units.
In an embodiment, the binaural hearing aid system is adapted to apply first and second sets of frequency dependent current gain values in each of the first and second hearing instruments, respectively.
In an embodiment, the binaural hearing aid system is adapted to use first and second sets of stored basic gain values of the first and second hearing instruments, respectively, as a basis for determining said first and second sets of current frequency dependent gain values, respectively.
In an embodiment, the first and second hearing instruments each comprises a timing unit for providing a timing control signal indicative of an elapsed time.
In an embodiment, the first and second sets of stored basic gain values are equal to said sets of first and second frequency dependent target gain values, respectively. In an embodiment, the first and second sets of stored basic gain values are equal to said sets of first and second frequency dependent target gain values, respectively modified (e.g. diminished) with predefined amounts.
In an embodiment, the binaural hearing aid system is adapted to modify the first and second sets of stored basic gain values over a period of time from initial values towards the target gain values. In an embodiment, the binaural hearing aid system is adapted to modify the first and second sets of stored basic gain values over a period of time according to a specific gain modification algorithm, e.g. executed in the signal processing unit.
In an embodiment, the binaural hearing aid system is adapted to provide that the gain modification algorithm provides modified gain values from initial gain values to target gain values depending on a timing control signal.
In an embodiment, the binaural hearing aid system is adapted to provide that said modified gain values are equal to said target gain values when said timing control signal is larger than a predefined end time value.
In a further aspect, the binaural hearing aid system comprises an auxiliary device.
In an embodiment, the system is adapted to establish a communication link between the hearing instrument and the auxiliary device to provide that information (e.g. control and status signals, possibly audio signals) can be exchanged or forwarded from one to the other.
In an embodiment, the auxiliary device is or comprises an audio gateway device adapted for receiving a multitude of audio signals (e.g. from an entertainment device, e.g. a TV or a music player, a telephone apparatus, e.g. a mobile telephone or a computer, e.g. a PC) and adapted for selecting and/or combining an appropriate one of the received audio signals (or combination of signals) for transmission to the hearing instrument.
In an embodiment, the auxiliary device is or comprises a remote control device for controlling operating parameters of the hearing instruments.
In an embodiment, the auxiliary device is or comprises a programming unit, e.g. for running a fitting software of the hearing instrument(s), for adapting the functionality (including processing parameters) of the hearing instrument(s) to the needs of a particular user.
The first and second hearing instruments of the binaural hearing aid systems may be largely identical in function, but be different in processing during operation, e.g. due to different gain profiles used in the signal processing units of the first and second hearing instruments.
General properties of each of the first and second hearing instruments are exemplified in the following (various aspects of digital hearing aids are described in [Schaub; 2008]):
The hearing instruments comprise an output transducer for converting an electric signal to a stimulus perceived by the user as an acoustic signal. In an embodiment, the output transducer comprises a number of electrodes of a cochlear implant or a vibrator of a bone conducting hearing device. In an embodiment, the output transducer comprises a receiver (speaker) for providing the stimulus as an acoustic signal to the user.
The hearing instruments comprise an input transducer for converting an input sound to an electric input signal. In an embodiment, the hearing instruments comprise a directional microphone system adapted to enhance a target acoustic source among a multitude of acoustic sources in the local environment of the user wearing the hearing instrument.
In an embodiment, the hearing instruments each comprise an antenna and transceiver circuitry for wirelessly receiving a direct electric input signal from another device, e.g. a communication device or another hearing instrument. In an embodiment, the direct electric input signal represents or comprises an audio signal and/or a control signal and/or an information signal.
The hearing instruments comprise a forward or signal path between an input transducer (microphone system and/or direct electric input (e.g. a wireless receiver)) and an output transducer. A signal processing unit is located in the forward path. The signal processing unit is adapted to provide a frequency dependent gain according to a user's particular needs. In an embodiment, the hearing instruments further comprise an analysis path comprising functional components for analyzing the input signal (e.g. determining a level, a modulation, a type of signal, an acoustic feedback estimate, a change of processing parameters, etc.). In an embodiment, some or all signal processing of the analysis path and/or the signal path is conducted in the frequency domain. In an embodiment, some or all signal processing of the analysis path and/or the signal path is conducted in the time domain.
In an embodiment, the hearing instruments comprise an analogue-to-digital (AD) converter to digitize an analogue input and provide a digitized electric input. In an embodiment, the hearing instruments comprise a digital-to-analogue (DA) converter to convert a digital signal to an analogue output signal, e.g. for being presented to a user via an output transducer.
In an embodiment, the hearing instruments each comprise an acoustic (and/or mechanical) feedback suppression system. In an embodiment, the hearing instruments further comprise other relevant functionality for the application in question, e.g. compression, noise reduction, etc.
A hearing aid fitting system:
A hearing aid fitting system comprising a processor and program code means for causing the processor to perform the steps of the method described above, in the ‘detailed description of embodiments’ and in the claims is furthermore provided by the present application. The hearing aid fitting system is particularly adapted for determining processing parameters (e.g. target gain values) for first and second hearing instruments of the binaural hearing aid system to a particular user.
The hearing aid fitting system preferably comprises a programming interface to the binaural hearing aid system, such as to a hearing instrument of the binaural hearing aid system, such as to each of the first and second hearing instruments of the binaural hearing aid system.
A hearing aid system:
A hearing aid system is furthermore provided by the present application. The hearing aid system comprises a binaural hearing aid system as described above, in the ‘detailed description of embodiments’ and in the claims AND a hearing aid fitting system for adapting processing parameters of the binaural hearing aid system to a particular user. The hearing aid system is particularly adapted for storing specifically determined processing parameters (e.g. target gain values) for a particular user in each of the first and second hearing instruments of the binaural hearing aid system.
Use of a binaural hearing aid system:
In an aspect, use of a binaural hearing aid system as described above, in the ‘detailed description of embodiments’ and in the claims is furthermore provided.
Further objects of the application are achieved by the embodiments defined in the dependent claims and in the detailed description of the invention.
As used herein, the singular forms “a,” “an,” and “the” are intended to include the plural forms as well (i.e. to have the meaning “at least one”), unless expressly stated otherwise. It will be further understood that the terms “includes,” “comprises,” “including,” and/or “comprising,” when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. It will also be understood that when an element is referred to as being “connected” or “coupled” to another element, it can be directly connected or coupled to the other element or intervening elements may be present, unless expressly stated otherwise. Furthermore, “connected” or “coupled” as used herein may include wirelessly connected or coupled. As used herein, the term “and/or” includes any and all combinations of one or more of the associated listed items. The steps of any method disclosed herein do not have to be performed in the exact order disclosed, unless expressly stated otherwise.
The disclosure will be explained more fully below in connection with a preferred embodiment and with reference to the drawings in which:
The figures are schematic and simplified for clarity, and they just show details which are essential to the understanding of the disclosure, while other details are left out. Throughout, the same reference numerals are used for identical or corresponding parts.
Further scope of applicability of the present disclosure will become apparent from the detailed description given hereinafter. However, it should be understood that the detailed description and specific examples, while indicating preferred embodiments of the disclosure, are given by way of illustration only. Other embodiments may become apparent to those skilled in the art from the following detailed description.
Hearing loss is typically graphically illustrated in an audiogram, where a user's hearing loss has been measured at a number of frequencies over the frequency range of interest (typically below 8 kHz).
The hearing loss (HL) of (an ear of) a user at a particular frequency is defined as the deviation in hearing threshold level (HTL) from the hearing threshold level of a normally (‘norm’) hearing person, in other words HLu(f) [dB HL]=HTLu(f)−HTLnorm(f) [dB SPL], f=frequency, ‘u’=‘user’, and ‘norm’=normally hearing person. This relativity to ‘normal data’ is typically expressed by denoting the audiogram data in ‘dB HL’.
In the following, the terms ‘hearing loss’ and ‘hearing threshold’ are used interchangeably and when used in an audiogram framework assumed to represent the same entity (provided in dB HL).
Hearing loss may be seen as a sum of contributions from so-called conductive losses in the outer and middle ear and from so-called sensorineural losses in the inner ear. The conductive losses may be due to external ear canal losses, losses of the eardrum or losses of the bones of the middle ear. Sensorineural losses may be due to damage or malfunction of the hair cells of the inner ear or the connections between the inner ear and the brain.
In a normal hearing test using an ear phone for playing soft sounds at different (pure tone) frequencies, the so-called air conduction hearing threshold (ACHL) is determined (the sounds reach the ear drum and the middle and inner ear via sound vibrations in the air). Air conduction hearing loss (ACHL) are indicated in the audiograms of
Similarly a so-called bone conduction hearing threshold (BCHL) can be determined using a vibrator transmitting sound vibrations to the skull of the person, where the sounds thus reach the inner ear through the bones of the skull (bypassing the outer and middle ear). Bone conduction hearing loss (BCHL) is indicated in the audiograms of
A conductive hearing loss (also termed the ‘air-bone gap’, ABG) can be determined as the difference between the air conduction and bone conduction hearing thresholds (ABG=ACHL−BCHL) in dB HL.
In an embodiment, the hearing loss data to form the basis for calculating sets of frequency dependent target gain values for the two hearing instruments of a binaural hearing aid system by classifying the similarity of audiograms for the left and right ears of a user are based on air conduction hearing loss data (ACHL(f)).
The air conduction hearing threshold (ACHL) is a composite measure of two different hearing loss contributions: a) the conductive part (ABG) and b) the sensorineural part. A hearing threshold for the sensorineural part may be represented by the bone conduction threshold (BCHL). If the air conduction threshold ACHL is equal to the bone conduction threshold BCHL, the conductive hearing loss is insignificant and a possible hearing loss is attributable to the inner ear and/or nerves to the brain, etc. (sensorineural hearing loss).
It may be advantageous to identify hearing loss data (e.g. audiograms) exhibiting a substantial conductive loss, i.e. having a significant air-bone gap as defined by an appropriate ABG-measure (e.g. a sum of ABG(fi)-values, [dB HL], i=1, 2, . . . , NHL, being larger than a predefined value ABGpd). Preferably such cases are handled separately (i.e. not according to the method of the present disclosure), because such losses may have different causes that need different treatment. In an embodiment the method of fitting a binaural hearing aid system to a user comprises identifying audiograms exhibiting a conductive hearing loss smaller than a predefined value (e.g. represented by an ABG-measure ABGpd that ensures that the conductive part of the hearing loss is insignificant).
There are different possibilities to measure similarity between (audiogram) data or curves ranging from simple differences between individual (curve) data to complex formula. In an embodiment, a rather simple approach is adopted by the introduction of a hearing loss difference measure (HLDM) with absolute differences and (possibly weighted) sums of such individual difference elements (e.g. taken at different frequencies, HLDMSUM=SUMi(wi|HL1(fi)−HL2(fi)|), where |HL1(fi)−HL2(fi) | is the absolute value of the difference between hearing loss values of the first and second ears at the frequency wi is a weight (e.g. between 0 and 1) of the ith term of the sum, i=1, 2, . . . , NHL., where NHL is a number of predetermined frequencies, contributing to the hearing loss difference measure). The multiplication with specific weights allows a control of the influence of specific frequency components on the calculated measure (HLDM). Setting a weight to zero for a given component excludes that component from the calculation. In an embodiment, all weights wi are equal to 1.
The following parameters are defined:
Air conduction hearing thresholds or hearing losses
AC
HL(fi) [dB HL], i=1, 2, . . . , NHL
Bone conduction hearing thresholds
BC
HL(fi) [dB HL], i=1, 2, . . . , NHL
Air bone gap
AC
HL(fi)−BCHL(fi) [dB HL], i=1, 2, . . . , NHL
A hearing loss difference measure may be based on one or more of the above parameters and relate to a single value (e.g. a maximum value at a single frequency at one ear or to a maximum difference value between the two ears at a single frequency) or to differences of values (at left and right ears), to a (possibly weighted) sum of values, to absolute values, to relative values, etc.
In the following ‘hearing loss classes’ and ‘audiogram classes’ are intended to have the same meaning. In an embodiment, the above mentioned special audiograms (e.g. having an air-bone gap measure larger than a predefined value) are identified in advance of the following classification and treated separately.
For the calculation of target gains of a binaural hearing aid system (e.g. for a first fitting), the following three hearing loss classes of asymmetry are used:
Audiograms are “EQUAL” (cf.
Audiograms are “SIMILAR” (cf.
Audiograms are “DIFFERENT” (cf.
If the audiograms are graduated as SIMILAR and EQUAL on both sides, the same target gains are used in both hearing instruments.
If the audiograms are graduated as DIFFERENT, the target gains are different in the first and second hearing instruments (and there is no difference to the prior art fitting scheme).
Example RULES for the classification:
The audiograms are considered to be “EQUAL” if:
Sum of differences for the frequencies 500 Hz, 1 kHz, 2 kHz, 3 kHz, 4 kHz is below or equal to 55 dB
No single frequency difference for 250 Hz, 500 Hz, 1 kHz, 1.5 kHz, 2 kHz, 3 kHz, 4 kHz and 6 kHz is more than 20 dB
Consequence: The target which is used for the fitting is the same for both sides.
For the calculation of the target gains a common hearing loss is calculated. Therefore the better audiogram HL-value from both sides is used, resulting in a binaural audiogram used for fitting both hearing instruments of the binaural hearing aid system.
The audiograms are considered to be “SIMILAR” if:
Sum of differences for the frequencies 500 Hz, 1 kHz, 2 kHz, 3 kHz, 4 kHz is below or equal to 90 dB
No single frequency difference for 250 Hz, 500 Hz, 1 kHz, 1.5 kHz, 2 kHz, 3 kHz, 4 kHz and 6 kHz is more than 30 dB
Consequence: The target which is used for the fitting is the same for both sides.
For the calculation of the target gains a common hearing loss is calculated. Therefore the better audiogram HL-value is used plus 1/3 of the difference between both values, resulting in a binaural audiogram used for fitting both hearing instruments of the binaural hearing aid system.
The audiograms are considered to be “DIFFERENT” if:
Sum of differences for the frequencies 500 Hz, 1 kHz, 2 kHz, 3 kHz, 4 kHz is larger than 90 dB
At least one single frequency difference for 250 Hz, 500 Hz, 1 kHz, 1.5 kHz, 2 kHz, 3 kHz, 4 kHz and 6 kHz is more than 30 dB
Consequence: The targets are calculated independently (as is usually done in the prior art).
With reference to
Hearing loss classification SIMILAR:
Hearing loss classification EQUAL:
Hearing loss classification DIFFERENT:
Each hearing instrument (HI-1, HI-2) comprises a memory (MEM) for storing basic processing parameters and/or data relating to a user's hearing impairment (e.g. hearing loss data) and/or basic (frequency dependent) gain values (e.g. the target gain values), from which current gain values appropriate in a given acoustic situation can be determined. The memory unit is operationally connected to the signal processing unit SPU allowing the signal processing unit to store and/or access data in the memory (MEM) as appropriate. In the embodiment of
One of the or both hearing instruments may in an embodiment comprise an oscillator (VCO, e.g. a voltage controlled oscillator, e.g. a voltage controlled crystal oscillator) for providing a sufficiently accurate timing input to the timing unit (TU) thereby allowing the timing unit to estimate an elapsed time with appropriate accuracy, e.g. in that the timing unit comprises a real time clock circuit and that an energy source of the hearing instrument ensures a constant functioning of the clock (even when the hearing instrument is not in use/powered down). Alternatively, the timing unit (TU) is adapted to receive a signal representative of the present time from another device, e.g. from a cell phone or from a radio time signal (e.g. DCF77 or MSF).
In an embodiment, the binaural hearing aid system further comprises an audio gateway device for receiving a number of audio signals and for transmitting at least one of the received audio signals to the hearing instruments (e.g. via wireless transceiver ANT, Rx/Tx providing audio input signal INw in
a shows the basic steps of the method for calculating target gain values for a binaural hearing aid system aimed as outlined in the following:
Start.
S1: Determining 1st and 2nd hearing losses HL for right and left ears, respectively, of a user;
S2: Determining a hearing loss difference measure HLDM;
S3: Classifying the degree of similarity of the 1st and 2nd hearing losses based on the HLDM;
S4: Determining the HL data to form the basis for calculating initial frequency dependent target gains TG for each of the 1st and 2nd Hs depending on the classification;
S5: Calculating target gains TG from the HL data using a fitting algorithm for each of the 1st and 2nd Hls; and
S6: Storing the target gains TG in the 1st and 2nd Hls. End.
The hearing losses and target gains are determined or calculated as a function of frequency f, e.g. at a number of predetermined frequencies fi.
In an embodiment, the method (e.g. step 1) comprises determining a conductive part (ABG(f)) of a hearing loss for the right and left ears, respectively, of a user. In an embodiment, the method is terminated, if the conductive part of the hearing loss for one or both ears of the user is larger than a predetermined amount (e.g. defined by an air-bone gap measure ABGM); and otherwise continued.
b shows an embodiment of the method wherein gain values are modified over time from an initial set to a target set of gain values. The method comprises an additional step S5b and slightly modified step S6 (S6a, S6b) (compared to the method illustrated in
S1: Determining 1st and 2nd hearing losses HL for right and left ears, respectively, of a user;
S2: Determining a hearing loss difference measure HLDM;
S3: Classifying the degree of similarity of the 1st and 2nd hearing losses based on the HLDM;
S4: Determining the HL data to form the basis for calculating initial frequency dependent target gains TG for each of the 1st and 2nd Hls depending on the classification;
S5a: Calculating target gains TG from the HL data using a fitting algorithm for each of the 1st and 2nd Hls;
S5b: Calculating initial frequency dependent basic gains from the target gains TG for each of the 1st and 2nd Hls;
S6a: Storing the target gains TG and the initial basic gains in the 1st and 2nd Hls;
S6b: Using the initial frequency dependent basic gains BG to determine current gains applied in the 1st and 2nd Hls;
S7: Determining a timing signal indicative of an elapsed time;
S8: Determine modified basic gain values from the initial gain values based on the timing control signal and a predefined modification scheme;
S9: Using the modified basic gain values to determine current gains applied in the 1st and 2nd Hs;
S10: Question: Modified BG=TG?
If NO, go to step S7;
If YES, end procedure.
The invention is defined by the features of the independent claim(s). Preferred embodiments are defined in the dependent claims. Any reference numerals in the claims are intended to be non-limiting for their scope.
Some preferred embodiments have been shown in the foregoing, but it should be stressed that the invention is not limited to these, but may be embodied in other ways within the subject-matter defined in the following claims.
[Schaub; 2008] Arthur Schaub, Digital hearing Aids, Thieme Medical. Pub., 2008.
WO2008109491A1 (AUDIOLOGY INC) Dec. 8, 2008.
| Number | Date | Country | Kind |
|---|---|---|---|
| 12157413.1 | Feb 2012 | EP | regional |
| Number | Date | Country | |
|---|---|---|---|
| 61604537 | Feb 2012 | US |
