Prescription of hearing aid features based on diagnostic measurements

Abstract

The invention discloses a method for prescribing hearing aid features based on diagnostic measurements. A method for setting signal processing parameters of a hearing aid includes: determining auditory contrast threshold (ACT) data for at least one ear of a hearing aid user; determining an audiogram of the hearing aid user; determining an age parameter of the hearing aid user; determining a signal processing parameter setting of a hearing aid used by the hearing aid user based on the ACT data, the audiogram and the age parameter according to a prescription protocol; and setting signal processing parameters of the hearing aid.

Description

Technical Field

[0001] The present application relates to the field of hearing aids.

[0002] The present application relates to a method for setting signal processing parameters of a hearing aid.

[0003] The present application also relates to a hearing aid fitting system.

[0004] The present application also relates to a data processing system comprising a processor and a program code.

[0005] The present application also relates to a computer program product comprising the instructions. Background Art

[0006] Hearing loss manifests in several ways, the most common being loss of audibility and difficulty hearing in noise. Currently, when fitting hearing aids to alleviate hearing loss, evidence-based fitting rules only exist for amplification or gain, addressing only the first issue. Consequently, for over 100 years, hearing aids have been fitted based on a single diagnostic measure, the pure tone audiogram, which describes the softest sounds a given client can hear across a number of different frequencies. This has been successful in prescribing amplification to address a client's audibility issues. However, as already mentioned, there is much more to hearing loss than loss of audibility; often, the ability to hear in noise is also negatively impacted, but to varying degrees and not necessarily related to the audiometric hearing loss.

[0007] To improve hearing-in-noise problems for hearing aid users, modern hearing aids include a number of different help-in-noise features, such as directional microphones (beamformers) and spectral subtraction noise reduction or (more generally) post-filtering. In recent years, these help-in-noise features have become much more powerful, which means that there is potential for many improvements in the setting of help-in-noise features for individual fitting based on specific needs. This potential has not been developed so far due to the lack of clinically feasible diagnostic measures to predict a given client's hearing-in-noise performance after receiving the aid (which can form the basis for prescribing help-in-noise features). The term "clinically feasible" involves many aspects, some of which are time efficiency and simplicity of setup by the doctor and the technology. Conventional practice is to prescribe a mass default setting of these features for all hearing aid users as a starting point, which will be optimal for the general public, but less optimal for those clients whose hearing-in-noise performance deviates from the average. This is a lost opportunity, particularly for hearing aid users who struggle disproportionately with hearing aid noise, because these users would substantially benefit from the strongest possible setting for the help in noise, and especially from a setting that enables the help in noise feature to work with the relatively simple sound environments in which these people already have problems.

[0008] Currently, hearing care professionals are encouraged (or even required in some countries) to perform speech-in-noise testing, which may be useful for prescribing noise-assistance features, but there is no clear guidance on how to use the results of speech-in-noise testing in the hearing aid fitting process. A poor initial fitting may also cause some users to abandon their hearing aids and return their hearing aids during the trial period.

[0009] Evidence-based fitting methods are also lacking for other hearing aid processing features, such as clarity and soft gain.

[0010] Therefore, there is a need for an improved fitting method that takes speech-in-noise testing into account. Summary of the Invention

[0011] method

[0012] In one aspect of the present application, a method for setting signal processing parameters of a hearing aid is provided.

[0013] Setting may refer to fitting / adjusting the signal processing parameters of the hearing aid according to the needs / requirements of the hearing aid user.

[0014] The method may include determining Audible Contrast Threshold (ACT) data for at least one ear of a hearing aid user.

[0015] For example, ACT data can be determined by providing stimulation into one or both ears of a hearing aid user and receiving a response from the user. For example, the user can provide a response via a physical response button, a user interface, or electrophysiologically (using one or more electrodes attached to the head).

[0016] For example, the spectral time modulation (STM) detection threshold (and ultimately, ACT) is determined empirically by adaptively varying the degree of modulation in the stimulus, which is delivered to the user's ears via headphones or plug-in earphones. The user is asked to respond to "target" stimuli with modulation while comparing these stimuli with "reference" stimuli that are not modulated. The threshold is the minimum degree of modulation that the user can detect. The general idea is that if a person is good at the ACT test (or the equivalent STM detection), they will also be good at distinguishing speech from background noise, even if there is only a very small difference between the speech and the background noise. Vice versa, a person with poor ACT / STM will need a larger difference / contrast between the speech and the background noise to understand the speech. Using ACT / STM to assess speech-in-noise ability has the additional advantage that the test does not use language-specific speech material but relies on artificial stimuli. In this way, ACT / STM can be used by anyone in any country, regardless of language background.

[0017] Several studies have shown that the ACT test has considerable predictive power for aided speech-in-noise performance in real listening situations. The ACT test is a clinically valid implementation of the STM test, and there is additional research evidence supporting the relationship between STM (and therefore ACT) and speech-in-noise performance [1]. Therefore, the ACT can be used during the hearing aid fitting process to estimate a user's aided speech-in-noise performance, thereby enabling the prescription of hearing aid assistance features for that user. Similarly, binaural measurements of the ACT can be used to prescribe the use of bilateral beamformer technology.

[0018] Thus, ACT can be conveniently measured right after the audiogram is measured, i.e. when the hearing aid user is already wearing headphones or plugged in earphones and has the response button in hand. Thus, ACT data can be obtained very early in the fitting process.

[0019] The method may include determining an audiogram of a hearing aid user.

[0020] The method may comprise determining an age parameter of the hearing aid user.

[0021] The age parameter may refer to the age of the hearing aid user.

[0022] The method may comprise determining signal processing parameter settings of a hearing aid used by a hearing aid user.

[0023] Signal processing parameter settings may be determined based on at least the ACT data according to a prescription protocol.

[0024] The signal processing parameter settings may be determined based on at least the audiogram according to a prescription protocol.

[0025] The signal processing parameter settings may be determined according to a prescription protocol at least according to an age parameter.

[0026] Signal processing parameter settings may be determined according to a prescription protocol based on (taking into account) ACT data, audiogram, and age parameters.

[0027] The method may comprise setting signal processing parameters of the hearing aid.

[0028] This provides an improved fitting method that takes speech-in-noise testing into account.

[0029] The ACT data may include an ACT value.

[0030] The ACT value may be a normalized contrast level (nCL) value.

[0031] 0 dB nCL may correspond to the average performance of a test population of normal hearing subjects.

[0032] 16dB nCL may correspond to the physically maximum spectral modulation degree, ie, 0dB full scale (FS).

[0033] Thus, 0 dB nCL corresponds to normal performance, positive dB nCL values indicate some degree of contrast loss, and negative dB nCL values indicate better-than-normal performance. Also, consistent with audiogram procedures, where testing can be performed up to -10 dB HL, the normalized contrast level is not adjusted beyond -4 dB nCL, two steps below 0 dB nCL. Thus, the contrast level (dBnCL) scale used for the ACT quantifies contrast loss in the same way that the hearing level (dB HL) scale quantifies audibility loss.

[0034] The ACT value can be one (combined) value for both ears.

[0035] The ACT value may be one value for each ear of the hearing aid user.

[0036] The step of determining ACT data may comprise estimating ACT data for at least one ear of the hearing aid user under the ACT test.

[0037] The step of determining ACT data may comprise receiving estimated ACT data of the hearing aid user from a database.

[0038] The step of setting the signal processing parameters of the hearing aid may comprise transmitting the determined signal processing parameter settings to the hearing aid.

[0039] The step of determining the hearing aid user's audiogram may include estimating one or more Hearing Threshold Level (HTL) values from the hearing aid user's audiogram.

[0040] The step of determining the hearing aid user's audiogram may comprise receiving a measured audiogram or an estimated HTL value from a database.

[0041] The step of determining an age parameter may comprise inputting an age parameter of a hearing aid user.

[0042] The step of determining the age parameter may comprise receiving the age parameter of the hearing aid user from a database.

[0043] The step of determining ACT data for the hearing aid user may comprise pre-processing the ACT data to reduce dimensionality.

[0044] The step of determining the audiogram of the hearing aid user may comprise pre-processing the audiogram to reduce dimensionality.

[0045] The step of pre-processing the audiogram may comprise estimating HTL values at a range of audiometric frequencies.

[0046] The step of pre-processing the audiogram may include estimating a four-frequency average, such as a pure tone average (PTA) value.

[0047] For example, the specific HTL values for the left and right ears of a hearing aid user at a range of audiometric frequencies may be used to calculate a four-frequency average across both ears, often denoted as PTA or PTA4.

[0048] The step of setting the signal processing parameters of the hearing aid according to the prescription protocol may comprise defining a plurality of prescription levels.

[0049] Each of the plurality of prescription levels may include preset signal processing parameters.

[0050] For example, the prescription level may define a noise assistance setting to assist a hearing aid user with noise hearing problems, from "very high" (a lot of assistance) to "very low" (low assistance), e.g., from "very high" to "high" to "medium" to "low" to "very low," e.g., from 1 to 5.

[0051] Defining a plurality of prescription levels may include determining a linear regression model as a prescription protocol for defining the plurality of prescription levels according to the ACT value, the audiogram, and an age parameter.

[0052] For example, the linear regression model may be estimated based on predetermined ACT data, audiograms, and / or age parameters from a plurality of users. For example, the predetermined ACT data, audiograms, and / or age parameters from a plurality of users may be determined / measured at a time prior to determining the linear regression model.

[0053] For example, the audiogram may be the PTA across both ears of the user, eg, a four-frequency average PTA4.

[0054] In other words, the coefficients of the linear regression model may be estimated / determined based on the predetermined ACT data, audiograms, and / or age parameters from a plurality of users (e.g., a test group). For example, the coefficients may include ACT value specific coefficients (k ACT ), PTA value specific coefficient (k PTA ), and / or age parameter specific coefficients (k AGE ).

[0055] For example, the coefficients may include the mean of the regression coefficients and / or the standard error of the regression coefficients.

[0056] For example, the values of the coefficients can be selected from the output of a regression model in various ways:

[0057] - You can choose the average value of each coefficient;

[0058] - a value greater or less than the average value may be selected;

[0059] - A value greater than or less than the mean value may be selected. For example, the selection may be fine-tuned by user input (e.g., user satisfaction), device return rates, refitting rates, etc. When selecting coefficient values greater than or less than the mean value, the selection may be balanced so that the mean and variance of the model predictions for the subject population remain unchanged relative to a baseline model using the mean value of the regression coefficients.

[0060] The linear regression model can take the following form:

[0061] SRT=k ACT ×ACT+k PTA ×PTA+k AGE ×Age+C

[0062] Where SRT is the estimated speech reception threshold (SRT) value, k ACT is the ACT value specific coefficient, k PTA is the PTA value specific coefficient, k AGE is an age parameter specific coefficient, ACT is a determined ACT value of at least one ear of the hearing aid user, PTA is a determined PTA value of the hearing aid user, Age is a determined age parameter of the hearing aid user, and C is a constant.

[0063] The plurality of prescription levels may be separated by a threshold value.

[0064] The threshold may be an SRT threshold.

[0065] A threshold may refer to an SRT value that defines the boundary between two prescription levels.

[0066] For example, a prescription level may refer to an interval / range of SRT values.

[0067] The linear regression model can estimate the SRT value of hearing aid users.

[0068] The SRT value may be a combined value for both ears of the hearing aid user.

[0069] An SRT value may be estimated for each ear of a hearing aid user.

[0070] A linear regression model may be estimated based on at least predetermined ACT data, audiogram, and age parameters.

[0071] The linear regression model may be estimated based on at least predetermined signal processing parameters.

[0072] Each of the one or more prescription levels may include / define / determine beamforming and / or noise reduction settings.

[0073] For example, each of the prescription levels may determine the allowed angular range for zero steering and zero depth of the adaptive beamformer.

[0074] For example, each of the prescription levels may determine the strength of the spectral subtraction type noise reduction.

[0075] For example, each of the prescription levels may determine the strength of the post-filtering noise reduction.

[0076] For example, each of the prescription levels may define a threshold value based on, for example, the overall sound level and the estimated signal-to-noise ratio, which determines when to enable the help-in-noise feature.

[0077] Each of the one or more prescription levels may include / define / determine a high frequency gain (ie, referred to as clarity) setting.

[0078] Each of the one or more prescription levels may include / define / determine a listening distance (ie, referred to as soft gain) setting.

[0079] Each of the one or more prescription levels may include / define / determine a transient noise reduction setting.

[0080] The step of determining signal processing parameter settings for the hearing aid used by the hearing aid user based on the ACT value, the audiogram and the age parameter according to the prescription protocol may comprise determining a value representing one of said prescription levels.

[0081] The method may further include automatically setting the SRT threshold for one or more prescription levels.

[0082] The method may comprise simultaneously determining ACT data for both ears of the hearing aid user.

[0083] For example, the two ears of a hearing aid user may be provided with the same stimulus, and ACT data indicating a combined ACT value may be determined. Alternatively or additionally, the ears of a hearing aid user may be provided with different stimuli, and ACT data indicating a combined ACT value may be determined.

[0084] The sound reaching the eardrum is a mixture of: (i) processed sound, picked up by the hearing aid microphone, processed, and played back through the hearing aid receiver; and (ii) unprocessed sound, which enters the ear canal from outside. Hearing aid processing manipulates only the processed sound, while the unprocessed sound remains unchanged. Therefore, the physical impact of a hearing aid's processing features on the sound representation at the eardrum, and therefore its potential effectiveness, depends largely on the relationship between these two components.

[0085] The relationship between the processed and unprocessed sound depends primarily on:

[0086] 1) The amount of amplification determined by the audiogram using the gain prescription rule,

[0087] 2) Input level, which affects the amount of amplification through dynamic range compression, and

[0088] 3) The amount of acoustic coupling, determined by how tightly the earphone seals the ear canal, thereby preventing unprocessed sound from entering.

[0089] Therefore, acoustic coupling depends on the interaction between the size and type of earpiece selected for a given hearing aid user / patient (currently recommended by the fitting software based on the audiogram) and the patient's ear canal. The amount of acoustic coupling can be described with the help of the real-ear occluded insertion gain (REOIG), which is defined as the difference between the real-ear occluded gain (REOG) and the real-ear unaided gain (REUG), thereby describing the amount of attenuation (or negative gain) obtained by the earpiece (see [2]).

[0090] This acoustic coupling is intentionally limited by including a vent in the earpiece, which allows unprocessed sound to enter the ear canal, as a very closed fit results in unpleasant problems caused by occlusion (e.g., self-voice perception, feeling of fullness, discomfort) and is therefore not preferred by patients. The typical current approach is to use an earpiece that is as open as possible while still allowing for adequate control of the acoustic feedback path between the hearing aid receiver and the hearing aid microphone. However, it has been demonstrated that patients have strongly different tolerances to different degrees of acoustic coupling (i.e., vent size and the resulting occlusion effects on self-voice perception, etc.), which can be predicted using a simple standard measure of tympanic membrane compliance (see [3]).

[0091] In the context of prescribing advanced in-noise aiding features such as directionality (e.g., via a directional microphone system) and noise reduction, the above aspects are relevant because ear openness is directly inversely proportional to the amount of signal-to-noise ratio (SNR) improvement that can be achieved, resulting in the need to balance opposing interests (comfort versus therapeutic benefit) to achieve optimal hearing aid fitting at the individual patient level. If a prediction of speech-in-noise performance is obtained (e.g., via the method of setting the signal processing parameters of a hearing aid described above, including determining ACT, audiogram, and age parameters) and converted into a specific need for SNR enhancement (e.g., by determining the signal processing parameter settings of the hearing aid as described above), it is necessary to ensure that the desired SNR enhancement can indeed be achieved with the selected hardware, ideally while balancing the need for SNR enhancement with the patient's tolerance for a closed fit.

[0092] Each of the one or more prescription levels may include / determine / define a degree of ear mold ventilation.

[0093] For example, the degree of ear mold ventilation may be determined and installed during hearing aid fitting, and in the case of active ear mold vents, the degree may be set automatically.

[0094] Each of the one or more prescription levels may include / determine / define a selection of an instant-fit dome type.

[0095] For example, an instant fit dome type may be selected during hearing aid fitting.

[0096] The method may further comprise estimating / determining acoustic coupling.

[0097] The acoustic coupling may be estimated / determined based on the Real Ear Occlusion Insertion Gain (REOIG) required to obtain the (desired) signal processing parameter settings (ie SNR enhancement) of the hearing aid.

[0098] For example, the signal processing parameter settings may be determined according to a prescription protocol based on the ACT data, audiogram, and age parameters, as described above.

[0099] The method may also include determining the (correct) earpiece type and vent size that provides the desired acoustic coupling.

[0100] For example, the desired acoustic coupling may be the acoustic coupling estimated / determined from the REOIG (as described above).

[0101] For example, earpiece and vent dimensions may be based on average REOIG measurements taken for multiple earpieces with various ear canals.

[0102] It should be noted that earpiece type and vent size alone are not perfect predictors of the amount of acoustic coupling achievable in REOIG because the earpiece interacts with the patient's ear canal.

[0103] The method may also include providing an upper limit on acoustic coupling for a balance between the determined earpiece and vent dimensions (see above) and a personalized prediction of the minimum acceptable equivalent vent area based on measured tympanic membrane compliance (see [3]).

[0104] The method may further include prescribing an earpiece type and a vent size based on the determined earpiece and vent sizes and based on the provided upper limit for acoustic coupling.

[0105] In other words, the method may include one or more of the following steps:

[0106] 1) Use ACT-, PTA-, and Age-based predictions of speech performance in noise to estimate patients' need for SNR enhancement;

[0107] 2) estimating the acoustic coupling based on the REOIG required to obtain the desired SNR enhancement determined in 1);

[0108] 3) determining the correct earpiece and vent dimensions that provide the desired acoustic coupling determined in 2) (e.g., based on average REOIG measurements* obtained for all earpieces with various ear canals);

[0109] 4) balancing the correct earpiece and vent dimensions determined in 3) with a personalized prediction of the minimum acceptable equivalent vent area based on measured tympanic membrane compliance, providing an upper limit on acoustic coupling;

[0110] 5) Prescription earpiece and vent dimensions based on 3) and 4).

[0111] *Regarding 3), it should be noted that earpiece type and vent size alone are not perfect predictors of the amount of acoustic coupling achievable in terms of REOIG, as the earpiece interacts with the patient's ear canal.

[0112] As mentioned above, earpiece type and vent size alone are not perfect predictors of the amount of acoustic coupling achievable in REOIG because the earpiece interacts with the patient's ear canal. There are several ways to address this issue.

[0113] Thus, the method may include one or more of the following:

[0114] - using the average REOIG measurement for each earpiece type obtained with a wide range of different ear canals;

[0115] - Use of personalized REOIG measurements for each earpiece type based on physiological aspects (e.g. head size, measurement of ear canal diameter, etc.);

[0116] - Use personalized REOIG measurements for each earpiece type based on tympanic membrane compliance;

[0117] - Use of personalized REOIG measurements for each earpiece type based on the estimated ear canal cavity (which is also the result of tympanometry);

[0118] -Measure actual REOIG for multiple earpiece types in individual patients.

[0119] Hearing aid fitting system

[0120] In one aspect of the present application, a hearing aid fitting system is provided.

[0121] The hearing aid fitting system may comprise a database for storing ACT data of at least one ear of a hearing aid user.

[0122] The hearing aid fitting system may comprise a database for storing audiograms of hearing aid users.

[0123] The hearing aid fitting system may comprise a database for storing age parameters of hearing aid users.

[0124] The hearing aid fitting system may include a hearing aid fitting device.

[0125] The hearing aid fitting device may be configured to receive stored ACT data from a database.

[0126] The hearing aid fitting device may be configured to receive audiogram data from a database.

[0127] The hearing aid fitting device may be configured to receive the age parameter from a database.

[0128] The hearing aid fitting device may be configured to determine signal processing parameter settings for the hearing aid according to the prescription protocol, based on the ACT value, the audiogram and the age parameter.

[0129] The hearing aid may be adapted for use by a hearing aid user.

[0130] “Based on” may mean that the prescription protocol takes into account the ACT value, audiogram and age parameters of the hearing aid user when determining the prescription level to be assigned to the hearing aid user.

[0131] The hearing aid fitting device may be configured to transmit the signal processing parameter settings to the hearing aid to set the signal processing parameters of the hearing aid.

[0132] The hearing aid fitting device may comprise a processor configured to determine signal processing parameter settings for the hearing aid.

[0133] Fitting software (computer program) for determining signal processing parameter settings of a hearing aid according to a prescription protocol may be stored on the hearing aid fitting device (eg, on a memory) and executed by the processor.

[0134] The hearing aid fitting system may further comprise an analysis unit for determining a regression model.

[0135] The linear regression model may be estimated by the analysis unit based on predetermined ACT data, audiograms, and age parameters of a plurality of users. The linear regression model may be suitable as a prescription protocol for defining a plurality of prescription levels.

[0136] For example, the audiogram may be a PTA across both ears of the user, such as a four-frequency average PTA4.

[0137] In other words, the analysis unit may estimate / determine coefficients for a linear regression model. For example, these coefficients may include coefficients specific to ACT values, coefficients specific to PTA values, and / or coefficients specific to age parameters. Furthermore, the analysis unit may estimate / determine signal processing parameters corresponding to the linear regression model. In other words, the analysis unit may be configured to determine a plurality of prescription levels, each prescription level including predetermined signal processing parameters.

[0138] The hearing aid fitting device may receive the linear regression model determined by the analysis unit. The received linear regression model may include estimated / determined coefficients.

[0139] The hearing aid fitting device may be configured to determine the prescription level for a given hearing aid user using a linear regression model using inputs of an ACT value determined from the hearing aid user, an audiogram (eg, a PTA value), and an age parameter.

[0140] hearing aids

[0141] The hearing aid may consist of or may include an air conduction type hearing aid.

[0142] The hearing aid may consist of or may include a bone conduction hearing aid.

[0143] The hearing aid may consist of or include any combination of an air conduction hearing aid and a bone conduction hearing aid.

[0144] The hearing aid may be adapted to provide frequency dependent gain and / or level dependent compression and / or frequency transposition of one or more frequency ranges to one or more other frequency ranges (with or without frequency compression) to compensate for the user's hearing impairment.

[0145] The hearing aid may comprise an output unit for providing a stimulus perceived by the user as an acoustic signal based on the processed electrical signal. The output unit may comprise a vibrator of a bone conduction hearing aid. The output unit may comprise an output transducer. The output transducer may comprise a receiver (loudspeaker) for providing the stimulus as an acoustic signal to the user (e.g. in an acoustic (air conduction based) hearing aid). The output transducer may comprise a vibrator for providing the stimulus as a mechanical vibration of the skull to the user (e.g. in a bone attached or bone anchored hearing aid). The output unit may (in addition or as an alternative) comprise a (e.g. wireless) transmitter for transmitting the sound picked up by the hearing aid (e.g. via a network, e.g. in telephone operating mode, or in a headset configuration) to another device, such as a remote communication partner.

[0146] The hearing aid may include an input unit for providing an electrical input signal representing sound. The input unit may include an input transducer, such as a microphone, for converting the input sound into the electrical input signal. The input unit may include a wireless receiver for receiving a wireless signal including or representing sound and providing the electrical input signal representing the sound.

[0147] The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the radio frequency range (3 kHz to 300 GHz), for example. The wireless receiver and / or transmitter may be configured to receive and / or transmit electromagnetic signals in the optical frequency range (e.g., infrared light 300 GHz to 430 THz or visible light such as 430 THz to 770 THz), for example.

[0148] A hearing aid may include a directional microphone system adapted to spatially filter ambient sound to enhance a target sound source among multiple sound sources in the local environment of a user wearing the hearing aid. The directional system may be adapted to detect (e.g., adaptively detect) the direction from which a particular portion of the microphone signal originates. This can be achieved in a variety of different ways, such as those described in the prior art. In hearing aids, microphone array beamformers are commonly used to spatially attenuate background noise sources. The beamformer may include a linearly constrained minimum variance (LCMV) beamformer. Many beamformer variants are available in the literature. Minimum variance distortionless response (MVDR) beamformers are widely used in microphone array signal processing. Ideally, an MVDR beamformer leaves the signal from the target direction (also known as the line-of-sight direction) unchanged while maximally attenuating sound signals from other directions. The generalized sidelobe canceler (GSC) structure is an equivalent representation of the MVDR beamformer, offering computational and digital representation advantages over a direct implementation of the original form. In other words, each of the one or more prescription levels may include beamforming and / or noise reduction settings based on the above directional microphone system.

[0149] Most sound signal sources (except the user's own voice) are relatively small compared to the size of the hearing aid, such as the distance d between the two microphones of a directional system. mic Located away from the user. The typical microphone distance in a hearing aid is on the order of 10 mm. The minimum distance from the user's sound source of interest (e.g., the sound from the user's mouth or the sound from the audio transmission device) is 0.1 m (>10 d mic ) level. For such a minimum distance, the hearing aid (microphone) will be in the acoustic near field of the sound source and the level difference of the sound signal incident on the respective microphones may be significant. The typical distance of the communication partner is greater than 1m (>100d mic The hearing aid (microphone) will be in the acoustic far field of the sound source, and the level difference of the sound signals incident on the corresponding microphones will not be obvious. The arrival time difference of the sound incident in the direction of the microphone axis (for example, in front of or behind a normal hearing aid) is ΔT = d mic / v sound =0.01 / 343[s]=29μs, where v sound The speed of sound in air at 20°C (343 m / s).

[0150] The hearing aid may include an antenna and transceiver circuitry that enables a wireless link to an entertainment device (e.g., a television), a communication device (e.g., a telephone), a wireless microphone, a separate (external) processing device, or another hearing aid. The hearing aid may thus be configured to wirelessly receive a direct electrical input signal from another device. Similarly, the hearing aid may be configured to wirelessly transmit a direct electrical output signal to another device. The direct electrical input or output signal may represent or include an audio signal and / or a control signal and / or an information signal.

[0151] For example, a hearing aid may be configured to communicate with a hearing aid fitting device via an antenna and transceiver circuitry to receive signal processing parameter settings. Similarly, a hearing aid fitting device may include an antenna and transceiver circuitry configured to communicate with a database of a hearing aid fitting system. Alternatively or additionally, the hearing aid fitting device, the database, and / or the hearing aid may be configured to communicate with each other via a wired connection.

[0152] In general, the wireless link established by the antenna and transceiver circuitry of the hearing aid may be of any type. The wireless link may be a link based on near field communication, for example an inductive link based on inductive coupling between antenna coils of a transmitter part and a receiver part. The wireless link may be based on far-field electromagnetic radiation. Preferably, the frequency used to establish the communication link between the hearing aid and the other device is below 70 GHz, for example in the range from 50 MHz to 70 GHz, for example above 300 MHz, for example in the ISM range above 300 MHz, for example in the 900 MHz range or in the 2.4 GHz range or in the 5.8 GHz range or in the 60 GHz range (ISM = Industrial, Scientific and Medical, such standardized ranges are defined, for example, by the International Telecommunication Union ITU). The wireless link may be based on standardized or proprietary technologies. The wireless link may be based on Bluetooth technology (for example Bluetooth Low Energy technology, for example LE Audio) or Ultra-Wideband (UWB) technology.

[0153] The hearing aid may consist of or form part of a portable (i.e. configured to be wearable) device, for example a device comprising a local energy source such as a battery, for example a rechargeable battery. The hearing aid may, for example, be a low-weight, easily wearable device, for example having a total weight of less than 100 g, such as less than 20 g, for example less than 5 g.

[0154] A hearing aid may include a "forward" (or "signal") path between the input and output of the hearing aid for processing audio signals. A signal processor may be located in this forward path. The signal processor may be adapted to provide frequency-dependent gain according to the specific needs of the user (e.g., hearing loss). The hearing aid may include an "analysis" path having functional components for analyzing signals and / or controlling processing of the forward path. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the frequency domain, in which case the hearing aid includes appropriate analysis and synthesis filter banks. Some or all of the signal processing in the analysis path and / or the forward path may be performed in the time domain.

[0155] The analog electrical signal representing the acoustic signal can be converted into a digital audio signal in an analog-to-digital (AD) conversion process, where the analog signal is sampled at a predetermined frequency or sampling rate f. s Sampling, f s For example, in the range from 8 kHz to 48 kHz (adapted to the specific needs of the application) at discrete time points t n (or n) provides digital samples x n (or x[n]), each audio sample is passed through a predetermined N b The bit represents the sound signal at t n The value when N b For example, in the range from 1 to 48 bits, such as 24 bits. Each audio sample thus uses N b bit quantization (resulting in 2 Nb different possible values). A digital sample x has a 1 / f s The length of time, such as 50μs, for f s = 20kHz. Multiple audio samples can be arranged in time frames. A time frame can include 64 or 128 audio data samples. Other frame lengths can be used depending on the actual application.

[0156] The hearing aid may include an analog-to-digital (AD) converter to digitize an analog input (e.g., from an input transducer such as a microphone) at a predetermined sampling rate, such as 20 kHz. The hearing aid may also include a digital-to-analog (DA) converter to convert the digital signal into an analog output signal, such as for presentation to the user via an output transducer.

[0157] The hearing aid, such as the input unit and / or the antenna and the transceiver circuit, may comprise a transform unit for converting a time domain signal into a signal in a transform domain (e.g. the frequency domain or the Laplace domain, a Z transform, a wavelet transform, etc.). The transform unit may be constituted by or include a time-frequency (TF) transform unit for providing a time-frequency representation of the input signal. The time-frequency representation may comprise an array or mapping of corresponding complex or real values of the signal in question in a specific time and frequency range. The TF transform unit may comprise a filter bank for filtering the (time-varying) input signal and providing a plurality of (time-varying) output signals, each output signal comprising a distinct frequency range of the input signal. The TF transform unit may comprise a Fourier transform unit (e.g. a discrete Fourier transform (DFT) algorithm, a short-time Fourier transform (STFT) algorithm, or a similar algorithm) for converting the time-varying input signal into a (time-varying) signal in the (time-)frequency domain. The frequency domain considered by the hearing aid, from the minimum frequency f min To the maximum frequency f max The frequency range of may include a portion of the typical human hearing range from 20 Hz to 20 kHz, for example a portion of the range from 20 Hz to 12 kHz. Typically, the sampling rate f s Greater than or equal to the maximum frequency f max twice, that is, f s ≥2f max The signals of the forward and / or analysis paths of the hearing aid may be split into NI frequency bands (e.g., of uniform width), where NI is, for example, greater than 5, such as greater than 10, such as greater than 50, such as greater than 100, such as greater than 500, at least parts of which are processed separately. The hearing aid may be adapted to process the signals of the forward and / or analysis paths in NP different frequency channels (NP ≤ NI). The frequency channels may be of uniform or non-uniform width (e.g., increasing width with frequency), overlapping or non-overlapping.

[0158] A hearing aid can be configured to operate in different modes, such as a normal mode and one or more specific modes, which can be selected by the user or automatically. The operating mode can be optimized for a specific acoustic situation or environment, such as a communication mode, for example, a telephone mode. The operating mode can include a low-power mode in which the functionality of the hearing aid is reduced (e.g., to save energy), such as disabling wireless communication and / or disabling specific features of the hearing aid. For example, the operating method can refer to and / or be set by one or more prescription levels.

[0159] The hearing aid may include a plurality of detectors configured to provide status signals related to the current network environment of the hearing aid (e.g., the current acoustic environment), and / or the current state of the user wearing the hearing aid, and / or the current state or operating mode of the hearing aid. Alternatively or additionally, one or more of the detectors may form part of an external device that communicates with the hearing aid (e.g., wirelessly). The external device may include, for example, another hearing aid, a remote control, an audio transmission device, a phone (e.g., a smartphone), an external sensor, etc.

[0160] One or more of the plurality of detectors may operate on a full-band signal (time domain). One or more of the plurality of detectors may operate on a band-split signal ((time-)frequency domain), eg in a limited number of frequency bands.

[0161] The plurality of detectors may include a level detector for estimating the current level of the signal in the forward path. The detector may be configured to determine whether the current level of the signal in the forward path is above or below a given (L-)threshold. The level detector operates on the full-band signal (time domain). The level detector operates on the band-split signal ((time-)frequency domain).

[0162] A hearing aid may include a voice activity detector (VAD) for estimating whether (or with what probability) an input signal (at a given point in time) includes a voice signal. In this specification, a voice signal may be understood to include a speech signal from a human. It may also include other forms of vocalizations (such as singing) produced by the human speech system. The voice activity detector unit may be adapted to classify the user's current acoustic environment as a "voice" or "no-voice" environment. This has the advantage that time periods containing electrical microphone signals of human vocalizations (such as speech) in the user's environment can be identified and thus separated from time periods containing only (or primarily) other sound sources (such as artificially generated noise). The voice activity detector may be adapted to also detect the user's own voice as "voice." Alternatively, the voice activity detector may be adapted to exclude the user's own voice from the "voice" detection.

[0163] A hearing aid may include a self-voice detector for estimating whether (or with what probability) a particular input sound (e.g., voice, such as speech) originates from the voice of a user of the hearing system. The microphone system of the hearing aid may be adapted to be able to distinguish the user's own voice from the voice of another person and possibly from unvoiced sounds.

[0164] The plurality of detectors may include a motion detector such as an accelerometer. The motion detector may be configured to detect movement of the user's facial muscles and / or bones, such as due to speech or chewing (eg, jaw movement), and provide a detector signal indicative of the movement.

[0165] The hearing aid may comprise a classification unit configured to classify a current situation based on an input signal from (at least part of) the detector and possibly other inputs. In this specification, a "current situation" may be defined by one or more of the following:

[0166] a) the physical environment (e.g., including the current electromagnetic environment, such as the presence of electromagnetic signals (including audio and / or control signals) intended or unintended for reception by the hearing aid, or other properties of the current environment other than acoustics);

[0167] b) Current acoustic conditions (input level, feedback, etc.);

[0168] c) the user’s current mode or state (motion, temperature, cognitive load, etc.);

[0169] d) The current mode or status of the hearing aid and / or another device communicating with the hearing aid (selected program, time elapsed since last user interaction, etc.).

[0170] The classification unit may be based on or may comprise a neural network, such as a recurrent neural network, such as a trained neural network.

[0171] Hearing aids may include acoustic (and / or mechanical) feedback control (e.g., suppression) or an echo cancellation system. Adaptive feedback cancellation has the ability to track changes in the feedback path over time. It is typically based on a linear time-invariant filter to estimate the feedback path, but the filter weights are updated over time. The filter updates can be calculated using a stochastic gradient algorithm, including some form of least mean square (LMS) or normalized LMS (NLMS) algorithm. They all have the property of minimizing the difference signal in terms of mean square, with NLMS additionally normalizing the filter updates by the square of the Euclidean norm of a reference signal.

[0172] The hearing aid may also include other suitable functions for the application in question, such as compression, noise reduction, etc. Other suitable functions may be part of one or more prescription levels.

[0173] A hearing aid may comprise a hearing instrument, such as a hearing instrument adapted to be positioned at the ear of a user or fully or partially positioned in the ear canal, such as an earphone, a headset, an ear protection device, or a combination thereof. A hearing system may comprise a loudspeaker amplifier (comprising a plurality of input transducers (e.g. a microphone array) and a plurality of output transducers such as one or more loudspeakers, and one or more audio (and possibly video) transmitters, such as for use in an audio conferencing situation), such as comprising a beamformer filter unit, such as to provide multiple beamforming capabilities.

[0174] When appropriately replaced by corresponding procedures, some or all of the structural features of the hearing aid and / or hearing aid fitting system described above, in detail in the "Detailed Description of the Invention," or defined in the claims may be combined with the implementation of the method, and vice versa. The implementation of the method has the same advantages as the corresponding hearing aid / device / system.

[0175] application

[0176] In one aspect, applications of hearing aids and hearing aid fitting systems as described above, in detail in the "Detailed Description" section, and in the claims are provided. Applications may be provided in systems including one or more hearing aids (e.g., hearing instruments), headphones, headsets, active ear protection systems, and the like, such as hands-free telephone systems, teleconferencing systems (e.g., including loudspeakers), public address systems, karaoke systems, classroom amplification systems, and the like.

[0177] Computer readable medium or data carrier

[0178] The present invention further provides a tangible computer-readable medium (data carrier) storing a computer program including program code (instructions), which, when the computer program is run on a data processing system (computer), causes the data processing system to perform (implement) at least part (such as most or all) of the steps of the method described above, described in detail in the "Specific Implementation Methods" and defined in the claims.

[0179] By way of example and not limitation, the aforementioned tangible computer-readable media may include RAM, ROM, EEPROM, CD-ROM or other optical disk storage, magnetic disk storage or other magnetic storage device, or any other medium that can be used to execute or store the desired program code in the form of instructions or data structures and that can be accessed by a computer. As used herein, disks include compact disks (CDs), laser disks, optical disks, digital versatile disks (DVDs), floppy disks, and Blu-ray disks, wherein these disks typically reproduce data magnetically, while these disks can reproduce data optically with lasers. Other storage media include storage in DNA (e.g., in synthetic DNA chains). Combinations of the above disks are also intended to be included within the scope of computer-readable media. In addition to being stored on tangible media, computer programs can also be transmitted via transmission media such as wired or wireless links or networks such as the Internet and loaded into a data processing system to be run at a location different from the tangible media.

[0180] computer program

[0181] In addition, the present application provides a computer program (product) comprising instructions, which, when run by a computer (e.g. as part of a hearing aid fitting device or a hearing aid), such as a processing unit of the hearing aid described above, causes the computer to perform (the steps of) the method described above, described in detail in the "Detailed Description of the Invention" and defined in the claims.

[0182] Data processing system

[0183] On the one hand, the present invention further provides a data processing system comprising a processor and program code, wherein the program code causes the processor to perform at least part (such as most or all) of the steps of the method described above, described in detail in the "Specific Implementation Methods" and defined in the claims.

[0184] Hearing system

[0185] In another aspect, there is provided a hearing aid comprising the device described above, in detail in the "Detailed Description of the Invention" and in the claims, and a hearing system comprising an auxiliary device.

[0186] The hearing system may be adapted to establish a communication link between the hearing aid and the auxiliary device so that information (eg control and status signals, possibly audio signals) can be exchanged or forwarded from one device to the other.

[0187] The auxiliary device may include or may consist of a remote control, a smart phone, or other portable or wearable electronic device such as a smart watch.

[0188] The auxiliary device may consist of or include a remote control for controlling the functions and operation of the hearing aid. The functions of the remote control are implemented in a smartphone, which may run an app that enables the functions of the audio processing device to be controlled via the smartphone (the hearing aid includes a suitable wireless interface to the smartphone, for example based on Bluetooth or some other standardized or proprietary solution).

[0189] The auxiliary device may be constituted by or include an audio gateway device, which is suitable for receiving multiple audio signals (for example from an entertainment device such as a TV or music player, from a telephone device such as a mobile phone, or from a computer such as a PC, a wireless microphone, etc.) and is suitable for selecting and / or combining appropriate signals (or signal combinations) from the received audio signals for transmission to the hearing aid.

[0190] The auxiliary device may consist of or may comprise a further hearing aid.The hearing system may comprise two hearing aids adapted to implement a binaural hearing system, eg a binaural hearing aid system.

[0191] For example, hearing aid signal processing parameter settings used by a hearing aid user according to a prescription protocol may be designed to be implemented in a binaural hearing system.

[0192] APP

[0193] In another aspect, the present invention further provides a non-transient application, referred to as an App. The App comprises executable instructions configured to run on an auxiliary device to implement a user interface for a hearing aid or hearing system as described above, in detail in the Detailed Description of the Invention, and in the claims. The App can be configured to run on a mobile phone, such as a smartphone, or another portable device that enables communication with the hearing aid or hearing system.

[0194] definition

[0195] As used herein, a hearing aid, such as a hearing instrument, refers to a device adapted to improve, enhance, and / or protect a user's hearing ability by receiving acoustic signals from the user's environment, generating corresponding audio signals, possibly modifying the audio signals, and providing the possibly modified audio signals as audible signals to at least one ear of the user. The audible signals may be provided, for example, in the form of acoustic signals radiated into the user's outer ear and / or acoustic signals transmitted as mechanical vibrations through the bony structure of the user's head and / or through portions of the middle ear to the user's inner ear.

[0196] The hearing aid can be configured to be worn in any known manner, such as as a unit worn behind the ear (with a tube that directs the radiated acoustic signal into the ear canal or with an output transducer, such as a loudspeaker, arranged close to or in the ear canal), as a unit arranged entirely or partially in the auricle and / or ear canal, as a unit connected to a fixed structure implanted in the skull, such as a vibrator, etc. The hearing aid can comprise a single unit or several units that communicate with each other (e.g., acoustically, electrically, or optically). The loudspeaker can be arranged in the housing together with the other components of the hearing aid, or it can itself be an external unit (possibly in combination with a flexible guiding element, such as a dome-shaped element).

[0197] Hearing aids can be adapted to the needs of specific users, such as hearing loss. The configurable signal processing circuitry of the hearing aid can be adapted to apply frequency- and level-dependent compression and amplification of the input signal. The customized frequency- and level-dependent gain (amplification or compression) can be determined during the fitting process by the fitting system based on the user's hearing data, such as an audiogram, using basic fitting principles (e.g., adaptation to speech). The frequency- and level-dependent gain can, for example, be reflected in processing parameters, uploaded to the hearing aid via an interface to a programming device (fitting system), and used by a processing algorithm executed by the configurable signal processing circuitry of the hearing aid.

[0198] A "hearing system" refers to a system that includes one or two hearing aids. A "binaural hearing system" refers to a system that includes two hearing aids and is adapted to collaboratively provide audible signals to both ears of a user. A hearing system or binaural hearing system may also include one or more "auxiliary devices" that communicate with the hearing aids and influence and / or benefit from the hearing aids' functionality. Such auxiliary devices may include at least one of the following: a remote control, a remote microphone, an audio gateway device, an entertainment device such as a music player, a wireless communication device such as a mobile phone (e.g., a smartphone) or a tablet, or another device, such as one that includes a graphical interface. A hearing aid, hearing system, or binaural hearing system may be used, for example, to compensate for the hearing loss of a hearing-impaired person, enhance or protect the hearing ability of a person with normal hearing, and / or transmit electronic audio signals to a person. A hearing aid or hearing system may, for example, form part of or interact with a public address system, active ear protection system, hands-free phone system, car audio system, entertainment (e.g., television, music playback, or karaoke) system, teleconferencing system, classroom amplification system, and the like. BRIEF DESCRIPTION OF THE DRAWINGS

[0199] Various aspects of the present invention will be best understood from the following detailed description in conjunction with the accompanying drawings. For clarity, the drawings are schematic and simplified, showing only the details necessary for understanding the present invention and omitting other details. Throughout the specification, the same reference numerals are used for identical or corresponding parts. The various features of each aspect may be combined with any or all features of the other aspects. These and other aspects, features, and / or technical effects will be apparent from and elucidated in conjunction with the following figures, in which:

[0200] Figure 1 An exemplary hearing aid fitting system according to the present invention is shown;

[0201] Figure 2 An exemplary method for setting signal processing parameters of a hearing aid according to the present invention is shown;

[0202] Figure 3 Exemplary prescription protocols and corresponding prescription levels are shown.

[0203] By the detailed description provided below, the further scope of application of the present invention will be apparent. However, it should be understood that while the detailed description and specific examples indicate the preferred embodiments of the present invention, they are provided for illustrative purposes only. For those skilled in the art, based on the following detailed description, other embodiments of the present invention will be apparent. DETAILED DESCRIPTION

[0204] The detailed description presented below in conjunction with the accompanying drawings serves as a description of a variety of different configurations. The detailed description includes specific details for providing a thorough understanding of a plurality of different concepts. However, it will be apparent to those skilled in the art that these concepts can be implemented without these specific details. Several aspects of the apparatus and method are described by a plurality of different blocks, functional units, modules, components, circuits, steps, processes, algorithms, etc. (collectively referred to as "elements"). Depending on the specific application, design limitations or other reasons, these elements may be implemented using electronic hardware, computer programs or any combination thereof.

[0205] The electronic hardware may include microelectromechanical systems (MEMS), (e.g., application specific) integrated circuits, microprocessors, microcontrollers, digital signal processors (DSPs), field programmable gate arrays (FPGAs), programmable logic devices (PLDs), gating logic, discrete hardware circuits, printed circuit boards (PCBs) (e.g., flexible PCBs), and other suitable hardware configured to perform the various functions described in this specification, such as sensors for sensing and / or recording physical properties of the environment, device, user, etc. A computer program shall be construed broadly to mean instructions, an instruction set, code, a code segment, program code, a program, a subroutine, a software module, an application, a software application, a software package, a routine, a subroutine, an object, an executable, a thread of execution, a program, a function, or the like, whether referred to as software, firmware, middleware, microcode, a hardware description language, or otherwise.

[0206] Figure 1 An exemplary hearing aid fitting system according to the present invention is shown.

[0207] Figure 1 The hearing aid fitting system 1 shown in FIG may include a database 2 and a hearing aid fitting device 3 .

[0208] The database 2 may be configured to store ACT data (e.g., ACT values) measured for at least one ear of a hearing aid user (e.g., binaural ACT data measurements may be stored), an audiogram of the hearing aid user, and an age parameter AGE of the hearing aid user. As shown, the audiogram may be pre-processed to form a PTA value before storage or in a subsequent step.

[0209] The database 2 may additionally store predetermined ACT data, audiograms, and / or age parameters determined / measured from a plurality of users.

[0210] The database 2 may additionally store a predetermined linear regression model suitable for use by the hearing aid fitting device 3 when determining the prescription level of a hearing aid for a given hearing aid user.

[0211] The hearing aid fitting system 1 may comprise an analyzing unit 4. The analyzing unit 4 may be configured to receive predetermined ACT data, audiograms, and / or age parameters determined / measured from a plurality of users from the database 2 (or from another database not shown).

[0212] The analysis unit 4 may determine a linear regression model. Thus, the linear regression model may be estimated by the analysis unit 4 based on predetermined ACT data, audiograms (e.g., PTA values), and / or age parameters from a plurality of users. The linear regression model may be suitable as a prescription protocol for defining a plurality of prescription levels. In other words, the coefficients of the linear regression model may be estimated / determined by the analysis unit 4. For example, the coefficients may include ACT value-specific coefficients, PTA value-specific coefficients, and / or age parameter-specific coefficients. Furthermore, signal processing parameters corresponding to the linear regression model may be estimated / determined by the analysis unit 4. In other words, the analysis unit 4 may be configured to determine a plurality of prescription levels, wherein each prescription level includes preset signal processing parameters.

[0213] The hearing aid fitting device 3 may be configured to receive the linear regression model or at least the coefficients of the linear regression model from the analyzing unit 4. Alternatively, the linear regression model or the coefficients may be stored at the database 2 and sent to the hearing aid fitting device 3.

[0214] The hearing aid fitting device may also receive ACT data (e.g., ACT value) measured for at least one ear of the hearing aid user, an audiogram (e.g., PTA value) of the hearing aid user, and an age parameter AGE of the hearing aid user from the database 2. Thus, the hearing aid fitting device 3 may use the ACT value, PTA value, and age parameter determined from the hearing aid user as input and determine the prescription level for a given hearing aid user using a linear regression model.

[0215] The determined prescription level for a given hearing aid user may be used to fit the hearing aid 5 of the hearing aid user.

[0216] The database 2 , the hearing aid fitting device 3 , the analysis unit 4 , and the hearing aid 5 may be configured to communicate with each other via a wired or wireless connection, as indicated by the solid and dashed lines 16 .

[0217] Figure 2 An exemplary method for setting signal processing parameters of a hearing aid according to the present invention is shown.

[0218] like Figure 2 As shown in , the method may include step 6 of determining ACT data such as ACT values of at least one ear (eg, both ears) of the hearing aid user.

[0219] The method may comprise step 7 of determining an audiogram (eg a PTA value) of the hearing aid user.

[0220] The method may comprise step 8 of determining an age parameter of the hearing aid user.

[0221] The method may include step 9 of preprocessing the ACT data and / or the audiogram to reduce dimensionality.

[0222] At step 10 , a linear regression model is determined (or alternatively, if already determined, is received) based on predetermined ACT data, audiograms (eg, PTA values), and / or age parameters from a plurality of users.

[0223] In step 11 , based on the determined linear regression model and the ACT value, PTA value, and age parameters specific to the hearing aid user, signal processing parameters of the hearing aid used by the hearing aid user may be determined according to the prescription protocol.

[0224] The method may further include step 12 of setting signal processing parameters for the hearing aid. The signal processing parameters may be set according to a prescription protocol. In other words, a plurality of prescription levels may be defined in step 13, each of which may include preset signal processing parameters.

[0225] At step 14 , defining the plurality of prescription levels may include determining a linear regression model as a prescription protocol for defining the plurality of prescription levels according to the ACT value, the audiogram, and the age parameter.

[0226] The step 12 of setting the signal processing parameters of the hearing aid may further include a step 15 of transmitting the determined signal processing parameter settings to the hearing aid.

[0227] The method may further comprise step 16 of estimating acoustic coupling. The acoustic coupling may be estimated based on the REOIG (ie, SNR enhancement) required to obtain the determined signal processing parameter settings.

[0228] The method may further comprise determining an ear piece type and a vent size, step 17. The ear piece type and vent size may be an ear piece type and vent size that provide the desired acoustic coupling estimated above.

[0229] The method may further comprise step 18 of providing an upper limit on the acoustic coupling.

[0230] The method may further include step 19 of prescribing an ear piece and a vent size based on step 17 of determining the ear piece type and vent size and step 18 of providing an upper limit for acoustic coupling.

[0231] Figure 3 Exemplary prescription protocols and corresponding prescription levels are shown.

[0232] exist Figure 3 In FIG. 1 , an exemplary table shows how the prescription level of a hearing aid user can be determined and how corresponding signal processing parameters can be determined.

[0233] From the linear regression model, the SRT of the hearing aid user can be estimated, for example, using the equation (see below):

[0234] SRT=k ACT ×ACT+k PTA ×PTA+k AGE ×Age+C

[0235] A plurality of prescription levels Pre-Lev may be defined, starting from a high (preset) SRT and progressing to a lower SRT value. The prescription levels Pre-Lev are shown as being referred to as 1 to 5, but other nomenclatures are also foreseeable.

[0236] Each prescription level may include a range of SRT levels.

[0237] The prescription levels may be separated by SRT thresholds such that each estimated SRT value of the hearing aid user corresponds to one of the prescription levels Pre-Lev.

[0238] For each Prescription Level Pre-Lev, one or more signal processing parameter settings may be defined. The amount of assistance (e.g., assistance in noise) may vary with the Prescription Level Pre-Lev. For example, at Prescription Level Pre-Lev 1, more assistance may be provided than at Prescription Level Pre-Lev 2.

[0239] exist Figure 3 In FIG, it is shown that the settings may include a beamforming and / or noise reduction setting BN, a high frequency gain (clarity) setting BR, and a listening distance (soft gain) setting SG. However, it is foreseeable that more signal processing parameter settings may be set, such as transient noise reduction.

[0240] The structural features of the apparatus described above, described in detail in the "Detailed Description of the Invention" and defined in the claims may be combined with the steps of the method of the present invention when appropriately replaced by corresponding processes.

[0241] Unless expressly stated otherwise, the singular forms "a", "the" and "the" used herein include the plural form (i.e., having the meaning of "at least one"). It should be further understood that the terms "having", "including" and / or "comprising" used in the specification indicate the presence of the described features, integers, steps, operations, elements and / or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and / or combinations thereof. It should be understood that, unless expressly stated otherwise, when an element is referred to as being "connected" or "coupled" to another element, it may be directly connected or coupled to the other element, or there may be an intermediate intervening element. The term "and / or" as used herein includes any and all combinations of one or more listed related items. Unless expressly stated otherwise, the steps of any method disclosed herein do not have to be performed in the exact order disclosed.

[0242] It should be understood that references in this specification to "an embodiment," "an embodiment," "an aspect," or features that "may" include, mean that the specific features, structures, or characteristics described in conjunction with that embodiment are included in at least one embodiment of the present invention. Furthermore, the specific features, structures, or characteristics may be combined as appropriate in one or more embodiments of the present invention. The foregoing description is provided to enable those skilled in the art to practice the various aspects described herein. Various modifications will be apparent to those skilled in the art.

[0243] The claims are not limited to the aspects shown herein, but rather have the full scope consistent with the claim language in which, unless expressly stated otherwise, elements referred to in the singular do not mean "one and only one" but rather "one or more." Unless expressly stated otherwise, the term "some" means one or more.

[0244] References

[0245] [1]Zaar, J., Simonsen, LB, Behrens, T., Dau, T., & Laugesen, S. (2019). Investigating the relationship between spectro-temporal modulation detection, aided speech perception, and directional noise reduction preference in hearing-impaired listeners. Proceedings of the International Symposium on Auditory and Audiological Research, 7, 181–188.

[0246] [2]Cubick,J.,Caporali,S.,Lelic,D.,Catic,J., Damsgaard,A.,Rose,S.,Ives,T.Schmidt,E.(2022).The Acoustics of Instant Ear Tips and TheirImplications for Hearing-Aid Fitting.Ear&Hearing,43(6),1771-1782.

[0247] [3]Carle,R.,Laugesen,S.,Nielsen,C.(2002).Observations on theRelations among Occlusion Effect,Compliance,and Vent Size.J.Am.Acad.Audiol.,13(1),25-37.

Claims

1. A method for setting signal processing parameters of a hearing aid, the method comprising: determining auditory contrast threshold (ACT) data for at least one ear of a hearing aid user; Determine the audiogram of hearing aid users; Determine the age parameters of hearing aid users; determining signal processing parameter settings for a hearing aid for use by the hearing aid user based on the ACT data, the audiogram, and age parameters according to a prescription protocol; Set the signal processing parameters for the hearing aid.

2. The method according to claim 1, wherein The ACT data includes ACT values which are normalized contrast level nCL values, where 0 dB nCL corresponds to the average performance of a test population of normal hearing subjects, and 16 dB nCL corresponds to the physically maximum spectral modulation, ie, 0 dB full scale.

3. A method according to any preceding claim, wherein: The steps to determine ACT data include: estimating ACT data for at least one ear of a hearing aid user who is undergoing an ACT test; or Estimated ACT data of a hearing aid user is received from a database.

4. A method according to any preceding claim, wherein: The steps in determining an audiogram for a hearing aid user include: estimating one or more hearing threshold level (HTL) values from a measured audiogram of the hearing aid user; or Receive the measured audiogram or estimated HTL value from the database.

5. A method according to any preceding claim, wherein: The steps to determine age parameters include: Enter the hearing aid user's age parameters; or An age parameter of a hearing aid user is received from a database.

6. A method according to any preceding claim, wherein: The steps for determining ACT data and / or audiogram for a hearing aid user include: The ACT data and / or the audiogram are preprocessed to reduce dimensionality.

7. The method according to claim 6, wherein: The step of pre-processing the audiogram comprises: Estimate HTL values at a range of audiometric frequencies; and Estimate a four-frequency average, such as a pure tone average PTA value.

8. A method according to any preceding claim, wherein: The steps for setting the hearing aid's signal processing parameters according to the prescription protocol include: A plurality of prescription levels are defined, wherein each prescription level includes preset signal processing parameters.

9. The method according to claim 8, wherein Defining multiple prescription levels includes: A linear regression model is determined as a prescription protocol for defining the plurality of prescription levels based on the ACT value, audiogram, and age parameter.

10. The method according to claim 8 or 9, wherein: The plurality of prescription levels are separated by a speech reception threshold (SRT) value, wherein the linear regression model estimates the SRT value for the hearing aid user.

11. The method according to claim 9 or 10, wherein: The linear regression model is estimated based on predetermined ACT data, audiogram, age parameters, and signal processing parameters.

12. A method according to any preceding claim, wherein: Each of the plurality of prescription levels comprises: Beamforming and / or noise reduction settings; High frequency gain (clarity) setting; Listening distance (soft gain) setting; and / or Transient noise reduction settings.

13. A method according to any preceding claim, wherein: The steps of determining the signal processing parameter settings of a hearing aid used by a hearing aid user based on the ACT value, the audiogram, and the age parameter according to the prescription protocol include: A value representing one of the prescription levels is determined.

14. A method according to any preceding claim, wherein: The method further comprises determining the acoustic coupling by estimating a real ear occluded insertion gain REOIG required to obtain the determined signal processing parameter setting of the hearing aid.

15. A hearing aid fitting system comprising: a database for storing ACT data of at least one ear of a hearing aid user, an audiogram of the hearing aid user, and an age parameter of the hearing aid user; a hearing aid fitting device configured to receive stored ACT data, audiogram, and age parameters from a database; wherein the hearing aid fitting device is configured to determine, according to the prescription protocol, signal processing parameter settings for the hearing aid used by the hearing aid user based on the ACT value, the audiogram, and the age parameter; The hearing aid fitting device may be configured to transmit the signal processing parameter settings to the hearing aid to set the signal processing parameters of the hearing aid.

16. The hearing aid fitting system according to claim 15, wherein: The hearing aid is composed of or includes an air conduction hearing aid, a bone conduction hearing aid, or any combination thereof.

17. A data processing system comprising a processor and a program code, wherein the program code causes the processor to execute at least part of the steps of the method according to any one of claims 1 to 14.

18. A computer program product comprising a computer program, the computer program comprising instructions which, when the computer program is run by a computer, cause the computer to perform the method according to any one of claims 1 to 14.

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