T he present i nvention relates to a method of operati ng a heari ng aid system. The present invention also relates to a hearing aid system adapted to carry out said method.

BACK GROUN D OF T H E INV E NTION

Generally, a hearing aid system according to the i nvention is understood as meaning any device which provides an output signal that can be perceived as an acoustic signal by a user or contributes to providing such an output signal, and which has means which are customized to compensate for an individual hearing loss of the user or contribute to compensati ng for the heari ng I oss of the user. They are, i n parti cul ar, heari ng ai ds which can be worn on the body or by the ear, in particular on or in the ear, and which can be fully or partially implanted. However, some devices whose main ai m is not to compensate for a hearing loss, may also be regarded as hearing aid systems, for example consumer electronic devices (televisions, hi-fi systems, mobile phones, M P3 players etc.) provided they have, however, measures for compensating for an individual hearing loss.

Within the present context a traditional hearing aid can be understood as a small, battery-powered, microelectronic device designed to be worn behind or in the human ear by a hearing-impaired user. Prior to use, the hearing aid is adjusted by a hearing aid fitter according to a prescription. T he prescription is based on a hearing test, resulting in a so-called audiogram, of the performance of the hearing-impaired user's unaided heari ng. The prescri ption is developed to reach a setti ng where the heari ng aid wi 11 alleviate a hearing loss by amplifying sound at frequencies in those parts of the audible frequency range where the user suffers a hearing deficit. A hearing aid comprises one or more microphones, a battery, a microelectronic circuit comprising a signal processor, and an acoustic output transducer. The signal processor is preferably a digital signal processor. The hearing aid is enclosed in a casing suitable for fitting behind or in a human ear.

Within the present context a hearing aid system may comprise a single hearing aid (a so cal led monaural heari ng aid system) or comprise two heari ng aids, one for each ear of the hearing aid user (a so called binaural hearing aid system). Furthermore, the hearing aid system may comprise an external device, such as a smart phone having software applications adapted to i nteract with other devices of the hearing aid system. Thus, withi n the present context the term 'hearing aid system device may denote a heari ng aid or an external device.

T he mechanical design has developed into a number of general categories. As the name suggests, Behind-T he-E ar (BTE) hearing aids are worn behind the ear. To be more precise, an electronics unit comprising a housing containing the major electronics parts thereof is worn behi nd the ear. A n earpiece for emitti ng sound to the heari ng aid user is worn in the ear, e.g. in the concha or the ear canal. In a traditional BTE hearing aid, a sound tube is used to convey sound from the output transducer, which in hearing aid terminology is normally referred to as the receiver, located in the housing of the electronics unit and to the ear canal. In some modern types of hearing aids, a conducting member comprising electrical conductors conveys an electric signal from the housing and to a receiver placed in the earpiece in the ear. Such hearing aids are commonly referred to as Receiver-In-The-E ar (RIT E) hearing aids. In a specific type of RITE hearing aids the receiver is placed inside the ear canal. T his category is sometimes referred to as Receiver-In-Canal (RIC) hearing aids.

In-T he-E ar (ITE) hearing aids are designed for arrangement in the ear, normally in the funnel-shaped outer part of the ear canal. In a specific type of IT E heari ng aids the hearing aid is placed substantially inside the ear canal. T his category is sometimes referred to as Completely-In-Canal (CIC) hearing aids. This type of hearing aid requi res an especial ly compact design i n order to al low it to be arranged i n the ear canal, while accommodating the components necessary for operation of the hearing aid.

Hearing loss of a hearing impaired person is quite often frequency- dependent. This means that the heari ng loss of the person varies dependi ng on the frequency. Therefore, when compensati ng for heari ng losses, it can be advantageous to uti I ize frequency- dependent amplification. Hearing aids therefore often provide to split an input sound signal received by an input transducer of the heari ng aid, into various frequency intervals, also called frequency bands, which are independently processed. In this way, it is possible to adjust the input sound signal of each frequency band individually to account for the hearing loss in respective frequency bands. T he frequency dependent adjustment is normally done by implementing a band split filter and compressors for each of the frequency bands, so-called band split compressors, which may be summarised to a multi-band compressor. In this way, it is possible to adjust the gain individually in each frequency band depending on the hearing loss as well as the input level of the input sound signal in a specific frequency range. For example, a band split compressor may provide a higher gain for a soft sound than for a loud sound in its frequency band.

T he filter banks used in such multi-band compressors are well known within the art of hearing aids but are nevertheless based on a number of tradeoffs. Most of these tradeoffs deal with the frequency resol uti on as wi 11 be further descri bed bel ow.

T here are some very clear advantages of having a high- resol uti on filter bank. The higher the frequency resolution, the better individual periodic components can be disti nguished from each other. This gives a much finer signal analysis and enables more advanced signal processing. Especially noise reduction and speech enhancement schemes may benefit from a higher frequency resolution.

However, a filter bank with a high frequency resolution generally introduces a correspondingly long delay, which for most people will have a detrimental effect on the perceived sound quality.

It has therefore been suggested to reduce the delay incurred by filter banks, such as Discrete Fourier T ransform (DFT) and Finite Impulse Response (FIR) filter banks by: applying a ti me-varying fiIter with a response that corresponds to the frequency dependent target gains that were otherwise to be applied to the frequency bands provided by the filter banks. However, this solution still requi res that the frequency dependent gai ns are calculated i n an analysis part of the system, and i n case the analysis part comprises fi Iter banks, then the determined frequency dependent gains wi 11 be del ayed rel ative to the signal that the gai ns are to be appl i ed to usi ng the ti me- varyi ng f i Iter. F urthermore, the ti me-varyi ng f i Iter i n itself wi 11 i nherently i ntroduce a delay although this delay is generally significantly shorter than the delay introduced by the fi Iter banks. It has furthermore been suggested i n the art to mi ni mize the delay i ntroduced by the ti me-varyi ng f i Iter by i mpl ementi ng the ti me-varyi ng fi Iter as mini mum- phase. While low delay processing is attractive it remains a challenge to design digital filter minimum phase synthetization algorithms that don't require more processing resources than are available in contemporary hearing aid systems.

It is therefore a feature of the present i nvention to provide an i mproved method of operati ng a hearing aid system with low delay signal processi ng.

It is another feature of the present invention to provide a hearing aid system adapted to provide such a method of operating a hearing aid system.

SUM MA RY OF T H E INV E NTION

The i nvention, i n a f i rst aspect, provides a method of operati ng a heari ng aid system comprisi ng the steps of:

- analyzi ng an i nput signal i n order to provide a frequency dependent target gai n that is adapted to at least one of suppressing noise, enhancing a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid system;

- determi ni ng the real cepstrum of the frequency dependent target gai n;

- usi ng the real cepstrum of the frequency dependent target gai n to provi de a desi red mi ni mum phase fi Iter i mpulse response;

- updating a digital filter, configured to provide the frequency dependent target gain, to provide the desired minimum phase filter impulse response,

wherei n at least one of the steps of:

- determi ni ng the real cepstrum of the frequency dependent target gai n, and

- usi ng the real cepstrum of the frequency dependent target gai n to provi de a desi red mi ni mum phase fi Iter i mpulse response,

is carried out by applying at least one of a discrete cosine transformation and a discrete si ne transformation.

T his provides an i mproved method of operati ng a heari ng aid system with respect to especially processing delay.

T he invention, in a second aspect, provides a hearing aid system comprising in a main signal branch:

an acoustical-electrical input transducer (301), a ti me-varyi ng digital filter (302) and an electrical -acoustical output transducer (303); and comprising, in an analysis signal branch:

an analysis filter bank (304), a frequency dependent target gai n calculator (305), a natural logarithm calculator (306), a smoothing filter (307), a discrete cosine transformation circuit (308), a cepstrum domain window (309), a discrete sine transformation circuit (310), a digital combiner (311), an exponential calculator (312), a minimum phase filter transfer calculator (313), a minimum phase impulse response calculator (314) and a main digital filter coefficient calculator (315).

T his provides a hearing aid system with improved means for operating a hearing aid system.

T he invention, i n a thi rd aspect, provides a non Jransitory computer readable medium carrying instructions which, when executed by a computer, cause the foil owing method to be performed:

- analyzi ng an i nput signal i n order to provide a frequency dependent target gai n that is adapted to at least one of suppressing noise, enhancing a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid system;

- determi ni ng the real cepstrum of the frequency dependent target gai n;

- usi ng the real cepstrum of the frequency dependent target gai n to provi de a desi red mi ni mum phase fi Iter i mpulse response;

- updating a digital filter, configured to provide the frequency dependent target gain, to provide the desired minimum phase filter impulse response,

wherei n at least one of the steps of:

- determi ni ng the real cepstrum of the frequency dependent target gai n, and

- usi ng the real cepstrum of the frequency dependent target gai n to provi de a desi red mi ni mum phase fi Iter i mpulse response,

is carried out by applying at least one of a discrete cosine transformation and a discrete si ne transformation.

F urther advantageous features appear from the dependent clai ms. Sti 11 other features of the present i nventi on wi 11 become apparent to those ski 11 ed i n the art from the f ol I owi ng descri pti on wherei n the i nventi on wi 11 be ex pi ai ned i n greater detail.

BRIE F DE SCRIPTION OF TH E DRAWINGS

By way of example, there is shown and described a preferred embodiment of this invention. As will be realized, the invention is capable of other embodiments, and its several details are capable of modification in various, obvious aspects all without departing from the invention. Accordingly, the drawings and descriptions will be regarded as illustrative in nature and not as restrictive. In the drawings:

Fig. 1 illustrates highly schematically a hearing aid system according to an

embodiment of the prior art;

Fig. 2 illustrates highly schematically a method of operating a hearing aid system accordi ng to an embodi ment of the i nventi on; and

Fig. 3 illustrates highly schematically a hearing aid of a hearing aid system accordi ng to an embodi ment of the i nventi on.

DETAIL E D D ESCRIPTION

In the present context the term signal processi ng is to be understood as any type of hearing aid system related signal processing that includes at least: noise reduction, speech enhancement and heari ng compensation.

Reference is first made to Fig. 1, which illustrates highly schematically a hearing aid system 100 accordi ng to an embodi ment of the pri or art.

T he hearing aid system 100 comprises an acoustical-electrical i nput transducer 101 , i.e. a microphone, an analog-digital converter (A DC) 102, a time-varying filter 103, a digital-analog converter (DA C) 104, an electro-acoustical output transducer, i.e. the hearing aid speaker 105, an analysis filter bank 106 and a gain calculator 107.

According to the embodiment of Fig. 1, the microphone 101 provides an analog input signal that is converted i nto a digital i nput signal by the analog-digital converter 102. However, in the foil owing, the term digital input signal may be used interchangeably with the term i nput signal and the same is true for al I other signals referred to i n that they may or may not be specifically denoted as digital signals.

T he digital input signal is branched, whereby the input signal, in a first branch (that may also be denoted the main signal branch), is provided to the time-varying filter 103 and, in a second branch (that may also be denoted the analysis signal branch), provided to the analysis filter bank 106. T he digital input signal, in the first branch, is filtered by the ti me-varyi ng filter 103 that applies a frequency dependent target gai n. This filtered digital signal is subsequently provided to the digital-analog converter 104 and further on to the acoustical-electrical output transducer 105 for conversion of the signal i nto sound.

T he digital input signal, in the second branch, is split into a multitude of frequency band signals by the analysis filter bank 106 and provided to the gain calculator 107 that determi nes a frequency dependent target gai n that is adapted to at least one of suppressing noise, enhancing a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid system, and based on the frequency dependent target gai n derives correspond! ng f i Iter coeff i ci ents for the ti me-varyi ng fi Iter 103.

The frequency dependent (and ti me-varyi ng) target gai n may be adapted to i mprove speech intelligibility or suppressi ng noise or customizing the sound or all of the above in addition to being adapted to alleviating an individual hearing deficit.

T he analysis filter bank 106 may be implemented in the time- domain or in the frequency domain using e.g. Discrete FourierT ransformation (DFT).

T he digital-analog converter 104 may be implemented as a sigma-delta converter, e.g. as disclosed in E P-B1-793897. However, in the foil owing the terminology digital- analog converter is used i ndependent of the chosen i mplementation.

Methods for deriving filter coefficients for a digital filter in order to adapt the digital fi Iter to be of mi ni mum phase and provide a frequency dependent target gai n are well known in the prior art. As one specific example of a prior art method the following approach may be used: In a fi rst step an i nput signal is analyzed i n order to provide a frequency dependent target gai n that is adapted to at least one of suppress! ng noise, enhanci ng a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid system.

In a second step obtaining the real cepstrum the complex cepstrum

of the desi red frequency dependent target gai n taki ng the i nverse F ouri er

transformation (IFT) of the (natural) logarithm of the frequency dependent target gai n. Generally the relation between the real cepstrum, the complex cepstrum, the frequency dependent target gai n and the fi Iter transfer function f given by:

and consequently that the real cepstrum given by:

In the following the inverse Fourier transformation (IFT) may also be abbreviated IDT F to emphasize that most signal processi ng today is digital, but i n the present context the two terms may be used interchangeably.

In a third step applying a window function to the real cepstrum of the frequency dependent target gai n ( f-l(k) }, whereby the complex cepstrum represent! ng the desi red minimum phase filter impulse response is provided:

T hus the window function I min is the unique function that can reconstruct the minimum phase complex cepstrum from the real cepstrum representing the frequency dependent target gai n.

T he discrete and finite window function Lin is given as:

Wherein N is the length of the lDT F used to provide the real cepstrum, f¾Sis the K ronecker delta function and n is the cepstrum variable.

In a fourth step applying a Fourier transformation to the provided complex cepstrum and hereby providing a logarithmic filter transfer function that is mi nimum phase. In a fifth step determining a filter transfer function (Hmin(k)) that is minimum phase by applying an exponential function to the provided logarithmic filter transfer function.

In a sixth step applying an inverse Fourier transformation to the filter transfer function that is mi ni mum phase and hereby providi ng the desi red mi ni mum phase fi Iter i mpulse response (hmin(n)). In a fi nal and seventh step usi ng the desi red mi ni mum phase fi Iter i mpulse response to derive fi Iter coefficients that wi 11 make the digital fi Iter mi ni mum phase and provide the desi red frequency dependent target gai n.

The i nventors have found that the efficiency of the methods for derivi ng the fi Iter coefficients can be significantly improved if the real cepstrum of the desired frequency dependent target gain is obtained by applying a discrete Cosine transformation (DCT) instead of applying an inverse discrete Fourier transformation.

According to a first aspect the efficiency improvement is obtained because the calculations requi red to provide the real cepstrum of the frequency dependent target gain can be significantly simplified by utilizing that the logarithm of the frequency dependent target gai n may be configured as a real and even function.

Using a standard ID FT the real cepstrum the frequency dependent target

gain can be expressed as:

Wherein, epresents the complex cepstrum, log is the natural logarithm,

represents the fi Iter transfer function, epresents the frequency dependent target gain and wherein N represents the length of the Fourier transformation. Utilizing that both the cosine function and the logarithm of the frequency dependent target gain may be configured as even functions i.e. that:

then the expression (eq. 5), for the real cepstrum can be further simplified:

Wherein

T hus by changing variables such that we get:

and when leaving out normalization and scale factors we see that the derived expression for the real part of the cepstrum the form of a type I Discrete Cosine T ransform DCTi (wherein the normalization and scale factors have been left out):

T hus, by usi ng the DCTi rather than the i nverse Fourier transform the computational load is reduced with about a factor of four. First a factor of two is gained because the DCT i only calculates a real cepstrum. Secondly another factor of two is gained because the only calculated up to N/2 +1 (see eq. 7) relative to the N-length IDFT (see

eq. 5) as a consequence of both the cosine function and the logarithm function being even. Furthermore, an additional efficiency improvement may be obtained by applying the because the window function given by eq. 4 can be simplified as a consequence of the cosine transformation only providing a real cepstrum with real and positive values and therefore the half of the n-values (i.e. the n-values larger than N/2), which are zeroed out by the window function of equation (4) are not calculated by the DCT i.

A ccordi ng to the present embodi ment the desi red mi ni mum phase fi Iter i mpulse response imay therefore be derived by first determining the complex cepstrum the complex cepstrum represent! ng the desi red mi ni mum phase fi Iter

impulse response) by multiplying the real cepstrum with the window function

and subsequently applying the fourth to sixth steps as given above, i.e.:

H owever, accordi ng to a variation of the present embodi ment the desi red mi ni mum phase impulse response determi ned di rectly from the complex cepstrum represent! ng the desi red mi ni mum phase f i Iter transfer f uncti on a si mple recursive formula:

The use of this formula is advantageous i n that the requi rements to heari ng aid system memory is li mited. It is furthermore noted that this variation is particularly

advantageous for mi ni mum phase fi Iter lengths that are not too long, si nee the complexity of the calculations and thereby the required current consumption scales with the filter length squared and as such may become unattractive if very long filters (such as longer than 40 fi Iter coefficients) are requi red. Generally, a Fourier transformation or inverse Fourier transformation, accordi ng to the invention, are carried out using a transformation that is selected from a group comprising: discrecte Fourier transformation (D FT), discrecte time Fourier

transformation (DT FT), Hartley T ransformation and polynomial functions converging towards the DT FT for input signal sample lengths approaching infinity.

Reference is now made to Fig. 2, which illustrates highly schematically a method 200 of operati ng a heari ng aid system accordi ng to an embodi ment of the i nvention.

In a fi rst step 201 , an i nput signal is analyzed i n order to provide a frequency dependent target gai n that is adapted to at least one of suppress! ng noise, enhanci ng a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid system.

In a second step 202, a DCTi of a logarithm of the frequency dependent target gai n is obtained and hereby is provided a real cepstrum of the frequency dependent target gain.

In a variation the logarithm of the frequency dependent target gain is smoothed by a digital filter that is configured to li mit the bin to bin variation of the frequency dependent target gain to be below a pre- determined threshold, whereby it may be ensured that a given digital fi Iter length is sufficient to represent the smoothed frequency dependent target gain while also being of minimum phase.

In a third step 203, the real cepstrum is used to provide a desired minimum phase filter impulse response.

In a fourth and fi nal step 204, a digital fi Iter, configured to provide the frequency dependent target gai n, is updated i n order to provide the desi red mi ni mum phase fi Iter impulse response.

Hereby is provided a method of operating a hearing aid system 200 with a very low processing delay, that is particularly processing efficient.

A ccordi ng to an embodi ment, the desi red mi ni mum phase fi Iter i mpulse response is optimized based on a cost function derived from perceptual criteria in order to achieve the best possible sound quality. In this way an optimum compromise between perceived sound qual ity and matchi ng of the resulti ng frequency dependent gai n with the i niti al ly determi ned frequency dependent target gai n is achieved. In a variation of this embodiment, the optimum compromise is determined based on user interaction and in a further variation the user interaction is controlled by an interactive personalization scheme, wherei n a user is prompted to select between different setti ngs of the two filters and based on the user responses the i nteractive personalization scheme finds an optimized setting. Further details on one example of such an interactive personalization scheme may be found e.g. i n WO-A 1 - 2016004983.

A method of opti mizi ng the fi Iter coefficients based on user preference through an interactive personalization scheme is particularly attractive because it is difficult to predict i n advance the cost function that best suits the i ndividual user's preferences. T herefore effective optimization may be achieved using an interactive personalization scheme.

Generally the inventors have found that al I D FT's and ID FT's required to carry out a minimum phase fi Iter synthetizati on may be replaced by either a Discrete Cosinus T ransformation (DCT) of the Type I or a Discrete Sinus T ransformation (DST) of the Type I respectively whereby an even more processing efficient method of minimum phase fi Iter synthetizati on is achieved.

According to a first aspect it has already been disclosed above how the calculation of an ID FT of a logarithm of a frequency dependent target gai n, i n order to provide a real cepstrum, may advantageously be carried out by calculating a DCT of type I of the logarithm of the frequency dependent target gai n.

A ccordi ng to a second aspect the i nventors have found that use of a D ST i may be used to further i mprove efficiency. C onsider now the wi ndow function see eq. (4), that is used to provide the complex cepstrum epresenti ng the desi red

mi ni mum phase fi Iter i mpulse response by multi plyi ng the wi ndow function

and the real cepstrum see eq. (3)).

The i nventors have realized that the real part of the Fourier transform of the complex cepstrum equal to the Fourier transform of the real cepstrum .e: Here from it follows that the wi ndow functi on i ntroduces a phase component and considering now the imaginary part of the Fourier transform of the multiplication of the window functi on the real cepstrum find:

T hat is recognized as a discrete sine transformation of Type I (DSTi) and consequently it is possible to replace the step of applying a Fourier T ransform with a step of applying a DSTi and hereby savi ng processi ng resources si mi lar to what was achieved above when replacing an ID FT with a DCTi.

According to a third aspect, consider now that because the real cepstrum a real functi on and because the wi ndow functi on y i ntroduces a phase component,

see eq. (14), then it fol I ows that for the Fourier T ransform of the complex cepstrum h i n the following is denoted the minimum phase logarithmic filter

transfer function fi nd:

Wherefrom it follows that the real part of which in the following is denoted even and that the i magi nary part of which i n the fol I owi ng is denoted odd. Now in order to determine the desired filter transfer function that is mi ni mum phase we determi ne the exponential of the mi ni mum phase logarithmic fi Iter transfer function

Wherein epresents the desired filter transfer function that is minimum

phase, wherein epresents the frequency dependent target gai n, which

is clear by recognizing that the real part of the filter transfer function that is mi nimum phase (i.e. not been changed as part of the modifications in the cepstral domain and therefore the original values of the previously defined frequency dependent target gain (i.e. can simply be re-used for determining the real part

of the filter transfer function that is minimum phase (i.e. and wherein

descri bed above may be determi ned as the discrete si ne transformation of

the complex cepstrum represent! ng the desi red mi ni mum phase fi Iter i mpulse response. T hus iepresents the phase function of the desi red mi ni mum phase fi Iter

impulse response.

It is worth noting that equation (16) represents a particularly efficient way of providing the minimum phase filter transfer function that corresponds to a previously defined frequency dependent target gain due to the re-use of the frequency dependent target gain and the use of the more efficient DST i instead of a conventional Fourier

T ransform.

Now the desired minimum phase impulse response (hmin(n)) may be determined as the ID FT of the mi ni mum phase fi Iter transfer function that i n order to i mprove readabi lity in the following will be denoted Hmin(k) instead of

and usi ng that al I odd functions sum to zero:

It can now be seen that the fi rst term can be simplified to a DCT of type I and that the second term can be simplified to a DST of type I, wherefrom it follows that further efficiency improvements may be achieved.

According to an additional variation the logarithm of the frequency dependent target gai n vector is fi Itered with a zero phase smoothi ng fi Iter, One example of such a fi Iter is a bit shifted smoothing filter characterised in being provided by adding a vector represent! ng the logarithm of the frequency dependent target gai n with a bit shifted and scaled version of itself and this specific bit shifted smoothing filter is particularly advantageous in being computationally very efficient.

F urthermore accordi ng to an advantageous aspect the smoothi ng of the frequency dependent target gai n may be used to ensure that the avai I abl e number of f i Iter coefficients for the mini mum phase digital filter is sufficient to provide a reasonable approxi mation of the frequency dependent target gai n.

Furthermore, it can be advantageous to carry out the smoothing before the logarithm of the frequency dependent target gai n is transformed i nto the cepstrum domai n, because this enables the initial value of the frequency dependent target gai n to be reused when determi ni ng the desi red mi ni mum phase fi Iter i mpulse response.

Reference is now given to Fig. 3, which illustrates highly schematically a hearing aid 300 of a hearing aid system according to a particularly advantageous embodiment of the invention. T he hearing aid 300 is similar to the hearing aid 100 accordi ng to the embodiment of Fig. 1 except in that specific details concerning the filter synthesizati on requi red to provi de fi Iter coeffi ci ents to the ti me-varyi ng f i Iter 302 (that i n the following also may be denoted main digital filter) such that the desired frequency dependent target gain Is provided by the time-varying digital filter 302 while also being minimum phase.

In Fig. 3 some of the arrows are drawn In bold In order to Illustrate a multitude of frequency bands that are Initially provided by the analysis filter bank 304. The frequency band signals, which are at least derived from the at least one acoustical- electrical Input transducer 301, are provided to a frequency dependent target gain calculator 305 where! n a frequency dependent target gain adapted to at least

one of suppressing noise enhancing a target sound, customizing the sound to a user preference and alleviating a hearing deficit of an Individual wearing the hearing aicl Is determined. According to the present embodiment the number of frequency bands Is

15, but In variations may be In the range between say 3 and 512.

The frequency dependent target gal n Is provided to a natural logarithm calculator 306 and therefrom to a smooth! ng fi Iter 307 that Is configured to II mit the bi n to bi n variation of frequency dependent target gain to be below a pre- determined threshold In order to ensure that the chosen length of the ti me-varying filter 302 Is sufficient to represent the desired frequency dependent target gain while being of minimum phase.

The smoothed frequency dependent target Is branched and provided both to a digital combi ner 311 and to a discrete cosi ne transformation cl rcuit 308 that provides a real cepstrum of the frequency dependenttargetgaln (CR(n)). Next a cepstrum domain window 309 Is applied to the real cepstrum of the frequency dependent target gain In order to provide a complex cepstrum epresenti ng the desired minimum phase

filter Impulse response.

The complex cepstrum then provided to a discrete sine transformation circuit

310 and therefrom to the digital combiner 311 wherein the discrete sine transformation of the complex cepstrum which represents a phase function, Is combined with the logarithmic and smoothed frequency dependent target gal n.

Subsequently the combined output from the digital combiner 411 Is provided to an exponential calculator 312 that applies an exponential function and together with the ml nl mum phase fi Iter transfer calculator 313 provides a filter transfer function that Is minimum pha¾ as already explained with neferenceto equation (16). The mini mum phase filter transfer function Is then provided to a minimum phase impulse response calculator 314 wherein a discrete cosine transformation is applied to the product of the real part of the filter transfer function and a normalization function and adding the result to the result of applying a discrete sine transformation to the impginary part of the filter transfer function whereby a desired mini mum phase filter

Impulse response is provided.

In the final step the desired mini mum phase filter impulse response is provided to the main digital filter coefficient calculator 315 that determines the corresponding filter coeffl cents and updates the main filter 302 with the coefficients. Thus the hearing aid 300 provides a single minimum phase digital filter 302 adapted to provideat least one of suppressing noise, enhancing a target sound customizing the sound to a user preference and alleviating a hearing deficit of an individual wearing the hearing aid

In further variations the methods and selected parts of the hearing aid systems according to the disclosed embodiments may also be Implemented In systems and devices that are not hearing aid systems (i.e. they do not comprise means for compensating a hearing loss), but nevertheless comprise both acoustical-electrical input transducers and electro-acoustical output transducers. Such systems and devices are at present often referred to as hearables. However, a headset is another example of such a system

In still other variations a nonjansitory computer readable medium carrying

instructions which, when executed by a computer, cause the methods of the disclosed embodiments to be performed.

Other modifications and variations of the structures and procedures will be evident to those skilled in the art