various embodiments are described hereinafter with reference to the figures . like reference numerals refer to like elements throughout . like elements will , thus , not be described in detail with respect to the description of each figure . it should also be noted that the figures are only intended to facilitate the description of the embodiments . they are not intended as an exhaustive description of the claimed invention or as a limitation on the scope of the claimed invention . in addition , an illustrated embodiment needs not have all the aspects or advantages shown . an aspect or an advantage described in conjunction with a particular embodiment is not necessarily limited to that embodiment and can be practiced in any other embodiments even if not so illustrated , or if not so explicitly described . the new method and hearing aid will now be described more fully hereinafter with reference to the accompanying drawings , in which various examples of the new binaural hearing aid system are shown . the new method and binaural hearing aid system may , however , be embodied in different forms and should not be construed as limited to the examples set forth herein . like reference numerals refer to like elements throughout . like elements will , thus , not be described in detail with respect to the description of each figure . fig1 shows a behind - the - ear ( bte ) hearing aid 10 in its operating position with the bte housing 12 behind the ear , i . e . behind the pinna 100 , of the user . the bte housing 12 conventionally accommodates a front microphone ( not visible ) and a rear microphone ( not visible ) for conversion of a sound signal into respective audio sound signals . the illustrated bte hearing aid 10 has an in - the - ear ( ite ) microphone 26 positioned in the outer ear of the user outside the ear canal at the free end of an arm 30 . the arm 30 is flexible and the arm 30 is intended to be positioned inside the pinna 100 , e . g . around the circumference of the conchae 102 behind the tragus 104 and antitragus 106 and abutting the antihelix 108 and at least partly covered by the antihelix for retaining its position inside the outer ear of the user . the arm may be pre - formed during manufacture , preferably into an arched shape with a curvature slightly larger than the curvature of the antihelix 104 , for easy fitting of the arm 30 into its intended position in the pinna . the arm 30 contains electrical wires ( not visible ) for interconnection of the ite microphone 26 with other parts of the bte hearing aid circuitry . in one example , the arm 30 has a length and a shape that facilitate positioning of the ite microphone 26 in an operating position below the triangular fossa . an earpiece 24 may alternatively , or additionally , hold one ite microphone that is positioned at the entrance to the ear canal when the earpiece is positioned in its intended position in the ear canal of the user . the ite microphone 26 is connected to an nd converter ( not shown ) and optional to a pre - filter ( not shown ) in the bte housing 12 , with electrical wires ( not visible ) contained in a sound transmission member 20 . a processor is also accommodated in the bte housing 12 and configured to generate a hearing loss compensated output signal based on the audio sound signals , an output signal of the at least one ite microphone , and a monaural audio signal . the hearing loss compensated output signal is transmitted through electrical wires contained in the sound signal transmission member 20 to a receiver ( not visible ) for conversion of the hearing loss compensated output signal to an acoustic output signal for transmission towards the eardrum of the user . the receiver ( not visible ) is contained in the earpiece 24 that is shaped ( not shown ) to be comfortably positioned in the ear canal of the user for fastening and retaining the sound signal transmission member 20 in its intended position in the ear canal of the user as is well - known in the art of bte hearing aids . fig2 is a block diagram illustrating one example of signal processing in the new hearing aid 10 , e . g . the hearing aid shown in fig1 . the hearing aid 10 has an ite microphone 26 to be positioned in the outer ear of the user . an output signal 28 of the ite microphone 26 is digitized and optionally pre - processed , such as pre - filtered , in a pre - processor 30 , and an output 32 of the pre - processor 30 is input to a processor 34 . the hearing aid 10 also comprises an electronic input 36 , such as an antenna , a telecoil , etc ., for provision of a received 38 signal representing sound emitted by a sound source ( not shown ) and received at the input 36 that is not coupled to a microphone that is accommodated in a housing of the hearing aid 10 . the sound emitted by the sound source may be recorded with a spouse microphone ( not shown ) carried by a person that the hearing aid user desires to listen to . the output signal of the spouse microphone is encoded for transmission to the hearing aid 10 using wireless or wired data transmission , preferably wireless data transmission . the receiver and decoder 40 receive the transmitted data representing the spouse microphone output signal and decode the received signal 38 into the monaural audio signal 42 . the monaural audio signal 42 is filtered with a filter 44 in such a way that a user can locate the position of the sound source from which the monaural signal 42 originates . the filter 44 is controlled by processor 34 based on the , optionally pre - processed , output signal 32 of the ite microphone 26 and the monaural audio signal 42 , and possibly an output signal 46 of the filter 44 providing feedback to the processor 34 . the processor 34 controls the filter 44 in such a way that spatial cues in the acoustic sound signal received by the ite microphone 26 are transferred , or substantially transferred , to the filtered monaural audio signal 46 , whereby spatial cues of the acoustic sound signal received by the ite microphone 26 are transferred , or substantially transferred , to the filtered monaural audio signal 46 so that a user perceives a sensation of direction towards a sound source from which the monaural audio signal originates ; or , a user perceives localization of the sound source . for example , based on the monaural signal , the user may receive acoustic signals at his or her eardrums with an interaural time difference and / or an interaural level difference sufficient for the perceived position of the sound source from which the monaural signal originates , to be shifted outside the head and laterally with relation to the orientation of the head of the user of the binaural hearing aid system , preferably into a perceived position corresponding to the actual position of the sound source , e . g . laterally within ± 45 ° of the actual position . the filtered monaural audio signal 46 is input to a processor 48 for hearing loss compensation . the hearing loss compensated signal 50 is output to a receiver 52 that converts the signal 50 into an acoustic signal for transmission towards the ear drum of the user . the processor 34 may for example control the filter 44 to phase shift the monaural audio signal 42 with a phase shift θ , wherein θ is based on the output signal 32 of the ite microphone 26 , and / or to multiply the monaural audio signal 42 with a gain based on the output signal 32 of the ite microphone . for example , the processor 34 may be configured to calculate a cross - correlation between the monaural audio signal 42 and the output signal 32 of the ite microphone 26 and to determine the phase shift θ to correspond to the maximum value of the cross - correlation and , thus , to correspond to the phase shift between the monaural audio signal 42 and the output signal 32 of the ite microphone 26 and / or the gain as the ratio between the monaural signal phase shifted with the determined phase shift θ and the output signal 32 of the ite microphone 26 . in this way , the output signal 46 of the filter 44 will contribute to the interaural time difference and / or the interaural level difference , respectively , in substantially the same way as the acoustic signal received by the ite microphone 26 would have done in absence of the hearing aid . for example , in a binaural hearing aid system with a hearing aid for the left ear and a hearing aid for the right ear as shown in fig2 , the monaural audio signal is received in both hearing aids and the respective filters 44 may output signals intended for the right ear and left ear of the user of the binaural hearing aid system that are phase shifted and / or amplified based on the respective cross - correlations as disclosed above , whereby the filtered monaural signals 46 in the hearing aids obtain substantially the same interaural time difference and / or substantially the same interaural level difference as the corresponding acoustic signals arriving at the ears in absence of the hearing aids so that the perceived position of the sound source from which the monaural signal originates is shifted outside the head and laterally with relation to the orientation of the head of the user of the binaural hearing aid system into a perceived position corresponding to the actual position of the sound source . likewise , if the hearing aid shown in fig2 is used as a monaural hearing aid , the phase shift and / or amplification of the filter 44 introduce an interaural time difference and / or interaural level difference with respect to the naturally received sound at the other ear of the user , corresponding to the position of the sound source from which the monaural audio signal originates . additionally , the processor 34 may control the transfer function of the filter 44 to be an appropriate one of the right part or left part of a selected hrtf with the interaural time difference and / or interaural level difference corresponding to the phase shift θ and / or gain , respectively , determined with the cross - correlation so that the user perceives the received monaural audio signal to be emitted by the sound source at its current position with relation to the user . the new hearing aid circuitry shown in fig2 may operate in the entire frequency range of the hearing aid 10 . the hearing aid 10 shown in fig2 may be a multi - channel hearing aid in which the ite microphone audio signal 28 and the monaural audio signal to be processed are divided into a plurality of frequency channels , and wherein the signals are processed individually in each of the frequency channels . for a multi - channel hearing aid 10 , fig2 may illustrate the circuitry and signal processing in a single frequency channel . the circuitry and signal processing may be duplicated in a plurality of the frequency channels , e . g . in all of the frequency channels . for example , the signal processing illustrated in fig2 may be performed in a selected frequency band , e . g . selected during fitting of the hearing aid to a specific user at a dispenser &# 39 ; s office . the selected frequency band may comprise one or more of the frequency channels , or all of the frequency channels . the selected frequency band may be fragmented , i . e . the selected frequency band need not comprise consecutive frequency channels . the plurality of frequency channels may include warped frequency channels , for example all of the frequency channels may be warped frequency channels . the ite microphone 26 may be connected conventionally as an input source to the processor 48 of the hearing aid so that in some situations , conventional hearing loss compensation may be selected , and in other situations the filtered monaural audio signal 46 may be selected for hearing loss compensation in processor 48 . an arbitrary number n of ite microphones may substitute the ite microphone 26 , and a combination of output signals from the n ite microphones may be combined in a ite signal combiner to form the , optionally pre - processed , output signal 32 , e . g . as a weighted sum . the weights may be frequency dependent . fig3 shows a hearing aid 10 similar to the hearing aid of fig2 ; however with an example of filtering of the monaural audio signal 42 that is different from the examples explained in connection with fig2 . the explanation of similar components and features is not repeated , but reference is made to the description of fig2 . in the hearing aid 10 of fig3 , the filter 44 is a digital adaptive filter with filter coefficients controlled by the processor 34 including adaptive controller 54 . the controller 54 controls the adaptation of the filter coefficients to minimize the difference 56 between the filtered monaural audio signal 46 and the , optionally pre - processed , output signal 32 of the ite microphone 26 . the difference 56 is provided by subtractor 58 of the processor 34 . in this way , the filtered monaural audio signal 46 approximates the , optionally pre - processed , output signal 32 of the ite microphone 26 , and thus also substantially attains a transfer function corresponding to an hrtf of the user , since the ite microphone 26 is positioned in a position in the outer ear of the user , wherein the hearing aid transfer functions are substantially equal to the right ear part or the left ear part of the hrtfs of the user . the , optionally pre - processed , output signal 32 of the ite microphone 26 has a short time spectrum denoted s iec ( f , t ) ( iec = in the ear component ). the short time spectrum of the monaural audio sound signal 42 is denoted s ( f , t ). pre - processing may include , without excluding any form of processing ; adaptive and / or static feedback suppression , adaptive or fixed beamforming and pre - filtering . the adaptive controller 54 is configured to control the filter coefficients of adaptive filter 44 so that the filter output 46 corresponds to the , optionally pre - processed , output signal 32 of the ite microphone 26 as closely as possible . the ite microphone 26 operates as monitor microphone for generation of an electronic sound signal 46 with the desired spatial information of the current sound environment . thus , the filter coefficients are adapted to obtain an exact or approximate solution to the following minimization problem : wherein p is the norm - factor , and w ( f ) is a frequency weighting factor , e . g . w ( f )= 1 . the algorithm controlling the adaption could ( without being restricted to ) e . g . be based on least mean square ( lms ) or recursive least squares ( rls ), possibly normalized , optimization methods in which p = 2 . for example , in the event that the incident sound field consist of sound emitted by a single speaker , the emitted sound having the short time spectrum x ( f , t ); then , under the assumption that the ite microphone 26 reproduces the actual hrtf perfectly then the following signals are provided : where h ( f ) is the transfer function of the monaural audio signal 42 . after sufficient adaptation , the hearing aid transfer function of the monaural audio signal 42 will be equal the actual hrtf so that if the speaker moves and thereby changes the hrtf , the adaptive filter 44 , i . e . the controller 54 adjusting the filter coefficients , adapt towards the new hrtf . the time constants of the adaptation are set to appropriately respond to changes of the current sound environment . the new hearing aid circuitry shown in fig3 may operate in the entire frequency range of the hearing aid 10 . the hearing aid 10 shown in fig3 may be a multi - channel hearing aid in which the ite microphone audio signal 28 and the monaural audio signal to be processed are divided into a plurality of frequency channels , and wherein the signals are processed individually in each of the frequency channels . for a multi - channel hearing aid 10 , fig3 may illustrate the circuitry and signal processing in a single frequency channel . the circuitry and signal processing may be duplicated in a plurality of the frequency channels , e . g . in all of the frequency channels . for example , the signal processing illustrated in fig3 may be performed in a selected frequency band , e . g . selected during fitting of the hearing aid to a specific user at a dispenser &# 39 ; s office . the selected frequency band may comprise one or more of the frequency channels , or all of the frequency channels . the selected frequency band may be fragmented , i . e . the selected frequency band need not comprise consecutive frequency channels . the plurality of frequency channels may include warped frequency channels , for example all of the frequency channels may be warped frequency channels . the ite microphone 26 may be connected conventionally as an input source to the processor 48 of the hearing aid so that in some situations , conventional hearing loss compensation may be selected , and in other situations the filtered monaural audio signal 46 may be selected for hearing loss compensation in processor 48 . an arbitrary number n of ite microphones may substitute the ite microphone 26 , and a combination of output signals from the n ite microphones may be combined in a ite signal combiner to form the , optionally pre - processed , output signal 32 , e . g . as a weighted sum . the weights may be frequency dependent . fig4 shows a hearing aid 10 similar to the hearing aids of fig2 and 3 , respectively ; however , with an example of filtering of the monaural audio signal 42 that is different from the examples explained in connection with fig2 and 3 . the explanation of similar components and features is not repeated , but reference is made to the descriptions of fig2 and 3 . in fig4 , the filter 44 amplifies the monaural audio signal 42 with gain values that are determined so that the signal magnitudes of the filtered monaural audio signal 46 are identical to , or substantially identical to , the signal magnitudes of the , optionally pre - processed , output signal 32 of the ite microphone 26 at a plurality of frequencies , whereby spatial cues in the , optionally pre - processed , output signal 32 of the ite microphone 26 , are transferred to the filtered monaural audio signal 46 . the processor 60 performs a spectral analysis of the , optionally pre - processed , output signal 32 of the ite microphone 26 , and the signal magnitude calculator 62 calculates signal magnitudes of the , optionally pre - processed , output signal 32 of the ite microphone 26 at a plurality of frequencies . likewise , the processor 64 performs a spectral analysis of the monaural audio signal 42 , and the signal magnitude calculator 66 determines signal magnitudes of the monaural audio signal 42 at the plurality of frequencies . the gain processor 68 calculates gain values at respective frequencies of the plurality of frequencies based on a ratio between calculated signal magnitudes of monaural audio signal 42 and signal magnitudes of the , optionally pre - processed , output signal 32 of the ite microphone 26 , and outputs the determined gain values to the filter 44 that is connected for multiplying the monaural audio signal 42 with the determined gain values at the respective frequencies . the monaural audio signal 42 is processed so that differences in signal magnitudes between the monaural audio signal 42 and the ite audio sound signal 32 are reduced . the processing may be performed in a selected frequency range , or in a plurality of selected frequency ranges , or in the entire frequency range in which the hearing aid circuitry is capable of operating . the determined gain values at the plurality of frequencies may be converted to corresponding filter coefficients of a linear phase filter inserted into the signal path of the monaural sound signal 42 , or , the gain values may be applied directly to the monaural sound signal 42 in the frequency domain . the new hearing aid circuitry shown in fig4 may operate in the entire frequency range of the hearing aid 10 . the hearing aid 10 shown in fig4 may be a multi - channel hearing aid in which the ite microphone audio signal 28 and the monaural audio signal to be processed are divided into a plurality of frequency channels , and wherein the signals are processed individually in each of the frequency channels . for a multi - channel hearing aid 10 , fig4 may illustrate the circuitry and signal processing in a single frequency channel . the circuitry and signal processing may be duplicated in a plurality of the frequency channels , e . g . in all of the frequency channels . for example , the signal processing illustrated in fig4 may be performed in a selected frequency band , e . g . selected during fitting of the hearing aid to a specific user at a dispenser &# 39 ; s office . the selected frequency band may comprise one or more of the frequency channels , or all of the frequency channels . the selected frequency band may be fragmented , i . e . the selected frequency band need not comprise consecutive frequency channels . the plurality of frequency channels may include warped frequency channels , for example all of the frequency channels may be warped frequency channels . an arbitrary number n of ite microphones may substitute the ite microphone 26 , and a combination of output signals from the n ite microphones may be combined in a ite signal combiner to form the , optionally pre - processed , output signal 32 , e . g . as a weighted sum . the weights may be frequency dependent . an electronic input for provision of a monaural audio signal received at the input and representing sound output by a sound source located in a position with relation to a user of the hearing aid , an ite microphone housing accommodating at least one ite microphone and configured to be positioned in the outer ear of the user for fastening and retaining the at least one ite microphone in its operating position , a filter for filtering the monaural audio signal and configured to output a signal selected from the group of signals consisting of : the monaural audio signal phase shifted with a phase shift based on an output signal of the at least one ite microphone , the monaural audio signal multiplied with a gain based on an output signal of the at least one ite microphone , and the monaural audio signal multiplied with a gain and phase shifted with a phase shift , wherein the gain and phase shift are based on an output signal of the at least one ite microphone , a processor configured to generate a hearing loss compensated output signal based the output signal of the filter , and a receiver for conversion of the hearing loss compensated output signal into an acoustic signal for transmission towards an eardrum of a user of the hearing aid , and optionally wherein a transfer function of the filter is substantially equal to one of the left ear part and the right ear part of a head related transfer function , and optionally a processor that is configured to calculate a cross - correlation between the monaural audio signal and the output signal of the at least one ite microphone and to determine the phase shift based on the calculated cross - correlation , and optionally wherein the filter is an adaptive digital filter with filter coefficients that are adapted so that a difference between the output of the at least one ite microphone and the output of the filter , is minimized , and optionally min g ⁡ ( f , t ) ⁢   ⁢ w ⁡ ( f ) ⁢ ( s i ⁢ ⁢ e ⁢ ⁢ c ⁡ ( f , t ) - g ⁡ ( f , t ) ⁢ s ⁡ ( f , t ) ) ⁢   ?? , s iec ( f , t ) is the short time spectrum at time t of the output signal of the at least one ite microphone , and s is the short time spectra at time t of the monaural audio signal , wherein the hearing aid further comprises a processor that is configured for determination of signal magnitudes of an output signal of the at least one ite microphone at a plurality of frequencies , and determination of signal magnitudes of the monaural audio signal at the plurality of frequencies , and determining gain values of the filter at respective frequencies of the plurality of frequencies based on the determined signal magnitudes of an output signal of the at least one ite microphone and the determined signal magnitudes of the monaural audio signal , and optionally wherein the monaural audio signal is divided into a plurality of frequency channels , and wherein the filter is configured for individually processing the monaural audio signal in selected frequency channels . a binaural hearing aid system is also provided , comprising a hearing aid as disclosed above . a method is also provided of processing a monaural signal in a hearing aid having an ite microphone housing accommodating at least one ite microphone and configured to be positioned in the outer ear of the user for fastening and retaining the at least one ite microphone in its operating position , the method comprising filtering the monaural audio signal into a signal selected from the group of signals consisting of : the monaural audio signal phase shifted with a phase shift based on an output signal of the at least one ite microphone , the monaural audio signal multiplied with a gain based on an output signal of the at least one ite microphone , and the monaural audio signal multiplied with a gain and phase shifted with a phase shift , wherein the gain and phase shift are based on an output signal of the at least one ite microphone , generating a hearing loss compensated output signal based the filtered monaural signal , and converting the hearing loss compensated output signal into an acoustic signal for transmission towards an eardrum of a user of the hearing aid . although particular embodiments have been shown and described , it will be understood that it is not intended to limit the claimed inventions to the preferred embodiments , and it will be obvious to those skilled in the art that various changes and modifications may be made without department from the spirit and scope of the claimed inventions . the specification and drawings are , accordingly , to be regarded in an illustrative rather than restrictive sense . the claimed inventions are intended to cover alternatives , modifications , and equivalents .