KR20010021877A - Method for electronically selecting the dependency of an output signal from the spatial angle of acoustic signal impingement and hearing aid apparatus - Google Patents

Abstract

For beam forming acoustical signals the phase difference of the output signals of two acoustical/electrical transducers is determined (27) and is multiplied by a factor (30). One of the two output signals of the at least two transducers is phase shifted by an amount according to the multiplication result. This phase shifted signal and the signal of the second transducer are led to a signal processing unit, wherein beam forming on these at least two signals is performed. Thereby, it becomes possible to perform beam forming as if the transducers were mutually distant by more than they physically are. <IMAGE>

Description

FIELD OF ELECTRONICALLY SELECTING THE DEPENDENCY OF AN OUTPUT SIGNAL FROM THE SPATIAL ANGLE OF ACOUSTIC SIGNAL IMPINGEMENT AND HEARING AID APPARATUS}

1 is the most general diagram of a known technique for "beam forming" on an acoustic signal. According to this, at least two multidirectional acoustic / electrical converters 2a, 2b are provided, all of which essentially convert the acoustic signals independent of their collision direction [theta], and thus the first electrical output signal and the second. The electrical output signals A ₁ , A ₂ are not substantially weighted with respect to the collision direction θ. The output signals A ₁ and A ₂ are supplied to the electronic transducer unit 3 which generates the output signal _Ar from the input signals A ₁ and A ₂ . As shown in the block of the unit 3, the signals A ₁ , A ₂ are processed to yield a resultant signal A _r that depicts the signal A ₁ or the signal A ₂ . However, this signal A ₁ , A ₂ is additionally weighted by the spatial amplification function F ₁ (θ). Thus, the acoustic signal can be selectively amplified depending on the impinging spatial angle [theta], ie depending on the spatial angle at which the transducer devices 2a, 2b "see" the acoustic source. Thus, this known method is strictly related to the physical location and inherent "lobe" of the transducer provided.

One method of performing signal processing in the transducer unit 3 can be embodied with reference to FIG. 2. According to FIG. 2, all such methods are due to the predetermined mutual physical distance P _p of the two transducers 2a, 2b, so that the delay time dt between the reception of the acoustic signal at each transducer 2a, 2b. Is based on the fact that

Considering the single frequency (ω) acoustic signal received at the transducer 2a, this transducer will produce the following output signal.

Here, the second converter 2b generates an output signal according to equation (2).

Here, dt is determined by equation (3).

Where c is the speed of sound.

For example, A ₁ is time delayed by a size determined by Equation 4 below,

The resultant signal A _r is formed from the difference of the time delayed signal A ₁ ′ (third signal), that is, from equations (5) and (2).

As a result, when considered at the frequency ω, a spatially cardioid weighted output signal A _r is output, as shown in the block of the transducer unit 3.

Here, the signal A _r becomes zero at θ = 90 ° and at θ = −90 °, as shown in Equation 7 below.

Such processing of the output signal of two omnidirectional order converters leads to a first order cardioid weighing function F ₁ (θ) as shown in FIG. 3. A higher order m weighting function F _m (θ) can be realized by selecting transducers respectively for higher order acoustic / electrical conversion characteristics, ie “lobes” and / or using two or more transducers.

In FIG. 4, the amplitude A _rmax resulting from the first-order cardiac weighted function as a function of frequency f = ω / 2π is shown. In addition, the angular function for the second-order cardiac weighting function F ₂ (θ) is shown. According to this, the selected physical distance P _p between the two transducers 2a, 2b shown in FIG. 1 is 12 mm.

As can be clearly seen at the frequency f _r according to Equation 8 below, the maximum amplitude in the first order cardoid is +6 dB and in the second cardiac pattern is +12 dB. P _p = 12 mm, F _r = 7 kHz.

From Fig. 4 one can see significant roll-offs for high and low frequencies as compared to f _r . That is, a significant reduction in amplification is recognized.

Such or similar types of beam forming techniques such as US Pat. No. 4,333,170 (sound source detection), European Patent Application No. 0 381 498 (directional microphone) or Norio Koike et al. Verification of the Possibility of Separation of Sound Source Direction via a Pair of Pressure Microphone ", Electronics and Communication in Japan, Part 3, Vol. 77, No. 5, 1994, pages 68-75.

Regardless of the prior art used to form such beams using at least two transducers, the distance P _p is an important entity as shown in Equation 8 and directly determines the resulting amplification / angle dependency. .

There is no particular difficulty in applying Equation 8 if such techniques are used for narrowband signal detection or do not encounter serious limitations in installing at least two transducers with a wide physical distance P _p between them.

Nevertheless, the fact that f _r is inversely proportional to the transducer's physical distance P _p , especially for hearing aid applications, means that the audible frequency band up to about 4 kHz for speech recognition of the hearing aid is as short as possible. Due to the fact that they must be detected by at least two transducers that must be mounted at a mutual distance of P _p , a serious drawback. These two requirements are in conflict. For lower f _r to be realized a wider distance P _p is required.

The present invention relates to a technique for receiving an acoustic signal by at least two acoustic / electrical converters, for example by a multidirectional microphone, wherein each output signal of such a transducer is an electronic transducer unit. and electrical calculations to produce an output signal representing the acoustic signal to which the spatial characteristics of amplification are weighted. Thus, the output signal depicts a received acoustic signal with a spatial amplification characteristic, such as the reception of the acoustic signal is, for example, the reception of the acoustic signal by an antenna with an appropriate receiving lobe or beam. . Accordingly, the present invention relates to a receive " lobe " which is electrically preset, i. E. Can be electrically adjusted and tailored.

Other objects of the present invention will become more apparent by the following description taken in conjunction with the drawings.

1 is a block diagram illustrating two transducer acoustic receivers having a directional beam formed according to the prior art;

FIG. 2 is a block diagram illustrating an example of a conventional beam forming technique applied to the apparatus of FIG. 1. FIG.

3 shows in two dimensions the amplification characteristics as a function of the incident angle of incidence of a three dimensional cardiac beam, ie an acoustic signal;

4 shows the frequency dependence of the maximum amplification according to FIG. 3 for the first-order cardiac function and the second-order cardiac function.

5 shows a pointer from the technique according to the prior art, FIG.

FIG. 6 is a pointer diagram according to the method of the present invention, based on FIG. 5 (prior art), but performed by the apparatus of the present invention.

7 is a block diagram schematically illustrating a first embodiment of a device of the invention, in particular a hearing aid in which the method of the invention is implemented;

8 schematically illustrates a preferred embodiment of the method and apparatus of the present invention.

9 is a schematic block diagram of an apparatus of the present invention operating in accordance with the method of the present invention in a general form.

10 is a block diagram illustrating general signal flow and functional blocks of an apparatus of the present invention operating in accordance with the method of the present invention.

FIG. 11 shows measured directivity characteristics resulting from the method and apparatus of the invention according to FIG. 8. FIG.

12 shows a second directivity characteristic resulting from the method and apparatus of the invention according to FIG. 8, represented according to FIG. 11.

Thus, a first object of the present invention is to provide a solution to the drawback with respect to the distance P _p -dependence of known acoustical "beam formation".

A first object of the invention can be achieved by providing a method for electronically selecting the dependence of the electrical output signal of the electronic transducer unit on the spatial direction in which the acoustic signal impinges at least the first and second acoustic / electrical transducers. . The transducers are each connected to an input of the transducer unit, thus inputting a first electronic signal and a second electronic signal to the unit. The method is

Generating at least one third electrical signal that depends on the mutual pasing of the first electronic signal and the second electronic signal, wherein the pacing is multiplied by a constant or frequency-dependent factor, and furthermore, the third The electrical signal is dependent on a fourth electrical signal that depends on at least one of the first electrical signal and the second electrical signal;

Generating an output signal of the transducer unit that is dependent on the third signal and further dependent on a fifth electrical signal that depends on at least one of the first electrical signal and the second electrical signal.

Thus, it becomes possible to select the dependency regardless of the actual physical mutual distance between the two transducers. It is thus possible to pre-select, tune and adjust the same, resulting in a dependency as if at least two transducers are in a completely different physical location than they are actually located.

In a first preferred way of realizing the method of the invention, the fourth electrical signal is selected to have a linear dependence on only one of the first electrical signal and the second electrical signal and thus such first electrical signal or second electrical signal. The fourth electrical signal is preferably directly formed by the signal.

Nevertheless, in the present more preferred manner of realizing the method of the present invention, the fourth electrical signal depends on both the first and second electrical signals. In a preferred form, the fourth electrical signal has a predetermined or adjustable " lobe " characteristic, i.e. dependence on the spatial collision direction. Thus, in the preferred formation of a "lobe", the realization of the fourth electrical signal is achieved by delaying one of the first and second electrical signals and adding the delayed signal with another non-delayed signal in the first and second electrical signals. . Accordingly, the fourth electrical signal essentially has an amplification for the impinging angle dependency, and thus defines "lobe" as an example according to the dependency described above with reference to FIGS.

In a further preferred form of realizing the method of the present invention, the first and the first, in combination with other methods of generating the above-described fourth signal, in particular the method of generating the fourth signal with the "lobe" characteristic, It is proposed to generate a fifth signal having a direct or linear dependence on at least one of the two electrical signals, thus using one of the first and second electrical signals as the fifth signal.

Thus, by itself or in combination with other methods of generating the above-described fourth signal, in particular the method of generating the fourth signal with "lobe" dependence, the first, with "lobe" dependency from the collision angle in space, It is proposed to produce a fifth electrical signal implemented in the first form by delaying one of the first and second electrical signals and adding the delayed signal with the other undelayed signals in the first and second electrical signals. Thus, it becomes clear that the fourth electrical signal generated to define the "lobe" characteristic can be used directly as the fifth electrical signal, having the same "lobe" characteristic.

It is proposed to produce a first electrical signal and a second electrical signal in each spectral representation, in combination with any of the apparently preferred further embodiments of the invention and in any of the preferred embodiments so far described and continued. Thereby generating at least one third electrical signal which is dependent on the mutual pacing of each spectral component of the first and second signals multiplied by a constant frequency independent factor or a frequency dependent factor.

In another preferred mode of operation, the frequency dependent multiplication factor is chosen inversely proportional to frequency in at least a first approximation.

Particular attention is given to hearing aids most suitable for the method of the invention, which can be explicitly applied in various places, suggesting that the actual physical distance of the first and second transducers up to 20 mm is proposed, thus at least virtually dependent on the pacing multiplication factor. The distance was chosen farther than the physical distance between the two transducers. In other words, the dependence of the output signal of the transducer unit on the spatial angle is as if the transducers were installed at mutually remarkable distances from each other. Such a technique has many advantages for any space-constrained application, especially for hearing aids, needless to say otherwise.

The acoustic / electric transducer device according to the invention for realizing the above-mentioned object and in particular for the hearing aid in which the required receiving lobe can be tailored and adjusted as necessary, irrespective of the physical position of at least two acoustic / electrical transducers, At least two acoustic / electrical converters spaced apart from each other at a predetermined physical distance. The distance between the transducers thus makes at least two transducers, respectively, a first electrical output signal and a second electrical output signal, which are operatively connected to the electronic transducer unit. The unit generates an output signal that depends on the first and second output signals of the converter by an amplification function. The amplification function depends on the spatial angle at which the transducer receives the acoustic signal.

The acoustic / electric transducer device includes a phase difference detection unit, a phase processing unit and a beam-former processing unit,

The phase difference detecting unit has its input terminal operatively connected to the output terminal of the converter and generates a phase difference dependent signal at its output terminal,

The phase processing unit has its first input end operatively connected with the phase difference detection unit, its at least one second input end is operatively connected with a factor-value-selecting source, and has its own third An input stage is operatively connected with at least one of the input stages of the at least two converters, and generates an output signal at its output stage in accordance with a signal at the third input stage, the phase of which is at least one of the first input stage and the at least one first stage; 2 is adjusted according to the signal at the input,

The beam-former processing unit has at least two inputs, one input being operatively connected with the output of the phase processing unit and a second input being operatively connected with at least one of the outputs of the at least two transducers.

Equation 9 can be realized under all features of the present invention.

This can be applied in particularly narrow spaces, especially in hearing aids.

Thus, the concept of the virtual distance P _v of the transducer, ie the distance between the transducers, which had to be physically realized to have an angle dependency in accordance with the invention, is introduced.

According to this and Equation 8, f _r can move to a lower frequency. The value of f _r can be an audible frequency band (<4 kHz) for speech recognition, with the distance of the microphone being significantly less than previously possible.

Multiplying the phase difference by a constant factor does not affect the roll-off shown in FIG. This roll-off is significantly improved, leading to an extended frequency band B _r according to FIG. 4 if the predetermined frequency function is chosen as a first order approximation function that is at least inversely proportional to the frequency of the acoustic signal, as described above. .

For the first order cardoid according to FIGS. 3 and 4, for example, by appropriately selecting the frequency dependent function multiplied by the phase difference, a flat frequency characteristic can be reached between 0.5 kHz and 4 kHz, and thus Thus, the roll-off of amplification at higher or lower frequencies is well defined, resulting in a significantly extended frequency band (B _r ).

As mentioned above, FIGS. 1 to 4 relate to known beam forming techniques which are separated by a physical distance P _p from each other and based on at least two acoustic / electrical transducers.

In FIG. 5, a pointer diagram according to equation (6) is shown.

The basic idea of the present invention will be described taking a simplified single frequency ω as an example. A pointer diagram realized according to the invention is shown in FIG. 6. The phase difference ω · dt between the signal A ₂ and the signal A ₁ according to FIG. 6 is expressed by Equation 10.

This phase difference is determined and multiplied by a value that depends on the frequency, that is, each value of the function M (ω). Also the constant M _o will not be one.

The two signals (A _1, A ₂₎ are in accordance with each point in FIG. 6 a signal of, for example, by shifting the phase of A ₂ in accordance with the pointer by M _ω · Δφ or M _o · Δφ of A _2, the phase shift A _2V is obtained. If dt is greater than M _ω or M _o , then a "virtual transducer" is positioned from the transducer 1a with a virtual distance P _v obtained from Equation 11 or 12 below. This pointer would also have occurred.

or

For simplicity, considering only a single frequency, we can assume M _o = M _ω .

If we put the hypothetical τ _v as in the equation below,

According to the present invention, the following can be obtained.

According to Equation 8, the following may be further obtained.

From this, it can be seen that for a given P _p leading to too high frequency f _r , f _rv is reduced by the factor M _ω > 1. FIG. 7 is a simplified view of a first embodiment of the device of the present invention, in particular of the hearing aid of the present invention implementing the method of the present invention. According to this, the output signal of the acoustic / electric transducers 2a, 2b is supplied to the respective analog-to-digital converters 20a, 20b, and the output therefrom is a time domain which is a Fast-Fourier Transform unit. It becomes the input of a time domain to frequency domain converter (TFC). The spectral phase difference detection unit 27 spectrally detects the phase difference Δφ _n for all n spectral frequency components multiplied by the set of constants C _n . If M is a function of _ω (M _ω ), c _n may be different for different frequencies, meaning a frequency dependent function or a frequency dependent factor. On the other hand, if the phase difference Δφ _n is multiplied by the same constant (c ₀ = c _n ≠ 1), it is equivalent to using the constant (M _o ).

This multiplication according to equation 3v is performed in the spectral multiplication unit 28. The signal A ₁ in its spectral representation is shifted in phase on the spectrum in a spectral phase shifter unit 29 by the multiplied spectral phase difference signal output by the multiplication unit 28. do.

According to FIG. 7, the signal A ₁ in its spectral representation and the signal whose phase in the spectrum is shifted according to the invention [ ] Is a spectral computing unit with a signal A ₂ in its spectral representation, as if the transducer 2a had a distance P _v = M _ω P _p from the transducer 2b. (23) is calculated.

The resulting spectrum is again transformed by a frequency domain-time domain converter (FTC), such as an inverse-Fast-Fourier-Transform unit 24 to derive the signal A _{r #} .

Accordingly, a beam forming technique other than the technique described with reference to FIGS. 1 to 4, that is, the time delay technique, which is converted in the frequency domain, may be used in the unit 23.

Nevertheless, time delay techniques are preferred.

In FIG. 4, it is illustrated that by introducing a "virtual" converter with a virtually extended mutual distance according to the invention, it is possible to shift the high gain frequency f _r to a lower frequency, which is particularly advantageous for hearing aids. Lose. As described, this can also be achieved by multiplying the phase difference by the constant M ₀ instead of the frequency dependent function M _ω .

In a preferred embodiment of the present invention, the frequency dependent function M _ω is selected as in equation 15 in at least a first order approximation.

Thus, unlike FIG. 4, there is no roll-off, and the gain in the target direction becomes constant in the required frequency range. By appropriate selection of the function M _ω , it is possible to have a flat characteristic within a predetermined frequency range, such as 0.5 kHz to 4 kHz, and to have a defined roll-off at higher or lower frequencies. With appropriate selection of the function M _ω , virtually any form of beam formation is possible.

In order to derive a higher order cardiac weighting function, the non-phase-shifted signal A ₁ is additionally used (shown in broken lines in FIG. 7) as the input signal to be input to the unit 23. It is of course also possible to "simulate" three converters.

FIG. 8 illustrates a preferred embodiment of the present device of the present invention in a functional block / signal flow scheme similar to FIG. 7. Of the already described blocks and signals of FIG. 7, those in FIG. 8 are given the same reference numerals.

The phase spectrum Δφ ' _{1... N} outside of the multiplication unit 28 is the preselected dependency on the collision angle θ, such as the primary cardiac dependence or the higher order cardiac dependence, in the addition unit 29'. Is also added as a spectral form to the signal [ _{Akr, 1 ... n} (ω, θ)].

2 to 4, the output signals A ₁ (ω) and A ₂ (ω) are realized in order to realize the signals A _{kr, 1... N} (ω _{1 ... n} , θ). ) Is directed to the beam-former unit 32, which may be integrated into the beam-former unit 23 ′, for example made according to the beam-former of FIG. 2. Instead of the beam-former 32 of FIG. 8, other types of beam-formers may be implemented which produce different results than the primary cardiac characteristics.

The spectrum A _{kr, 1 ... n} (ω _{1 ... n} , θ) is phase-shifted by the phase addition unit 29 'by Δφ' _{1 ... n} to output the unit 29 '. Signal, which has a spectrum [A _{kv, 1... N} (ω _{1 ... n} , Δφ ' _{1 ... n} , θ) as shown in FIG. 8. In addition to the output signal of the adding unit 29 ', the signals _{Akr, 1 ... n} (ω _{1 ... n} , θ) also reach the beam-former unit 23', which signals (33) It is preferably added back as shown in.

At the output of the beam-former unit 32 a signal with the actual cardiac dependence on the impact angle θ is generated, and at the output of the unit 29 ', thus after phase shift, the dependency function on the impact angle θ Is realized according to the virtually located transducer. During the addition, like unit 33 in beam-former unit 23 ', the dependence of the output signal A _r on the collision angle [theta] appears, if the actual cardiac dependence at the output of unit 32 If the primary heart type, then the dependence of the output signal A _r follows the secondary heart type.

Thus, as in FIG. 9, more generally expressed, the phase difference spectrum at the output of the unit 27 is passed to the phase shifter unit 35 _where it is modulated by c ₁ by c _n .

The generalized phase shifter 35 may directly receive one of the output signal of one of the two transducers 2a, 2b and / or the signal resulting from beam shaping from the output signal of the phase shifted transducer. In FIG. 9, this is represented as a signal path fed back from the beam-former 37 to the phase shifter 35. Referring to FIG. 8, this feedback coincides with the signal path between the beam-former 32 and the adding unit 29 ′. According to FIG. 9, the beam forming unit 32 of FIG. 8 is integrated into the integrated beam-former unit 37. The beam-former 37 in the general form shown in FIG. 9 receives at least one of the output signal of the transducers 2a, 2b and the output signal of the generalized phase shifter 35.

1) two or more real transducers may be used, or 2) from one real transducer signal or one or more real transducer signals, using one function (M _ω ) or one of c ₀ or c _1. It will be apparent to one skilled in the art that one or more "virtual transducer" signals can each be generated.

Several physical transformers and virtual transformers, their properties, and the virtual "relocation" of these transformers can be selected to selectively fit the spatial weighting function.

Under the main object, the present invention allows virtually any beam formation required, using at least two transducers separated by a predetermined small distance, by electronically providing a virtual position between the transducers of the physically installed transducers. Let's do it.

Thus, the roll-off is markedly reduced by such a virtual transducer, which is in particular established by realizing the virtual distance of the transducer which is not dependent on frequency, in particular in inverse proportion. By selecting a virtual distance dependent on the frequency M _{ω of the} transducer, a virtual arrangement of the frequency selective transducer is achieved. For hearing aids, the actual distance between at least two transducers, ie the microphones, is selected up to 20 mm, preferably less than.

FIG. 10 is a diagram illustrating, in the most general form, the main flow and device structure in accordance with the present invention and commonly applied to all embodiments of the present invention described above.

The first and second electrical signals S ₁ , S ₂ , which are derived from the output signals of at least two acoustic / electrical converters 2a, 2b, are inputs of the transducer unit 3. In the unit 3, a phase difference detecting unit such as the unit 27 of FIGS. 7, 8, or 9 is provided. The phase difference detection unit 27 has respective input ends operatively connected to the input end of the unit 3 and thus connected to the output ends of the transducers 2a and 2b. The output end of the phase difference detection unit 27 is operatively connected to the input end of the phase processing unit 40 shown by broken lines in FIG. The phase processing unit 40 has a second input, which is connected to a factor value-selecting source 42 and generates a constant factor or a frequency dependent factor h. The third input of the phase processing unit, as schematically shown, is operatively connected to the output of at least two transducers 2a, 2b with a "logical" or "exclusive OR" dependency by coupling unit 44. . The phase processing unit 40 is according to the signal S ₄ supplied to the third input of the processing unit 40 and to the first input (from 27) and the second input (from 42) of the phase processing unit. The output signal S ₃ is generated in accordance with the supplied signal.

The signal at the first input of the phase processing unit is operatively connected with the output of the phase difference detection unit, which is multiplied by a constant or frequency dependent factor by the unit 28. In the signal combining unit 46, the output signal of the processing unit, that is, the signal S ₃ , is generated in dependence on the mutual pacing of the output signal of the converter so that the constant or frequency dependent factor is multiplied and the third of the processing unit 40. depends on the signal (S ₄₎ which is supplied to an input terminal, a signal (S ₄₎ is dependent on at least one of the output signal of the transducer (2a, 2b). In unit 46, a dependency F ₁ of signal S ₃ occurs, depending on the signal S ₄ and the phase signal multiplied in unit 28.

The signal S ₃ according to A ₁ (ω) in FIG. 7 or according to A _{kr, 1 ... n} (ω _{1 ... n} , θ) in FIGS. 8 and 9 is the unit of FIGS. 7 to 9. (23), the input of the beam-former processing unit 48 corresponding to the unit 23 'or unit 37. The beam-former processing unit has a second input, which is supplied with a signal S ₅ which depends on at least one of the output signals of the transducers 2a, 2b. Thus, signal S ₅ is operatively coupled to beam-former processing unit 48 in a "exclusive AND" or "logical" combination, as schematically illustrated by block 50.

FIG. 11 shows the “lobe” or directivity characteristic (in dB) measured in the device of the invention according to FIG. 8 at a single frequency (1 kHz) of an acoustic signal impinging two acoustic / electrical transducers. . The specifications of this device are as follows.

Transducers (2a, 2b): omni-directional microphone, KNOWLES EK 7263

Physical distance (P _p ): 12 mm

τ: 35 μsec

c: 2 at 1 kHz and 4 kHz

The resulting directivity index is defined as 8.83 in "SPEECH COMMUNICATION 20 (1996), 229 to 240, Microphone array systems for hands-free telecommunications, Gary W. Elco".

FIG. 12 shows the results for an acoustic collision signal of a single frequency of 4 kHz in the device of the invention used for the measurement according to FIG. 11. The directivity index is 7.98.

The treatment according to FIG. 8 results in a directivity characteristic along the secondary heart type. To realize this, conventionally, four acoustic / electrical transducers such as transducers 2a and 2b had to be used, and the physical distance between each transducer was 24 mm. Therefore, the result of the directivity of the method and apparatus of the present invention employing only two acoustic / electrical converters and only 12 mm apart from each other is as follows, using four acoustic / electrical converters and a distance of 24 mm from each other. The result is no different.

Claims (22)

For a spatial direction in which an acoustic signal operatively connected to the input of the transducer unit and thereby impinging at least two first acoustic / electrical transducers and a second acoustic / electrical transducer for inputting the first electrical signal and the second electrical signal; A method of electronically selecting a dependency of an electrical output signal of said electronic transducer unit, At least depending on the mutual pacing of the first and second electrical signals multiplied by a constant or frequency dependent factor, and further dependent on a fourth electrical signal depending on at least one of the first and second electrical signals. Generating one third electrical signal, Generating the output signal of the transducer unit that is dependent on the third electrical signal and also dependent on a fifth electrical signal that depends on at least one of the first electrical signal and the second electrical signal. The method of claim 1, wherein the fourth electrical signal is generated as a signal dependent on the first electronic signal and the second electronic signal. The method of claim 1, wherein the fourth electrical signal is dependent on the first electronic signal and the second electronic signal. The method of claim 1, wherein said fourth electrical signal is generated as a signal having a dependency on said spatial direction, such as cardiac dependence, predetermined or adjustable. The method of claim 1, wherein the fourth electrical signal is generated by delaying one of the first electrical signal and the second electrical signal and adding the delayed signal to another signal of the first electrical signal and the second electrical signal. 5. The method of claim 1, wherein the fifth signal is dependent on one of the first electrical signal and the second electrical signal. 6. 5. The method of claim 1, wherein the fifth electrical signal is dependent on both the first electrical signal and the second electrical signal. 6. The method of claim 1, wherein the fifth electrical signal is generated as a signal having a predetermined or adjustable dependency, such as cardiac dependence. 9. 9. The method according to any one of claims 1 to 5, 7, or 8, wherein one of the first signal and the second signal is delayed and added to another signal of the first signal and the second signal. 5 How to generate an electrical signal. 10. The method of any one of the preceding claims, wherein the fourth electrical signal is generated by generating the fifth electrical signal. 11. The method of any one of claims 1 to 10, wherein the first electrical signal and the second electrical signal are generated in respective spectral formats, and the mutual pacing of the respective spectral components of the first and second signals. And generate the at least one third electrical signal that is multiplied by the factor and is dependent on the fourth electrical signal. 12. The method of any one of the preceding claims, wherein the factor is selected in inverse proportion to frequency. An acoustic / electric transducer device comprising at least two acoustic / electrical transducers at a predetermined physical distance, the at least two transducers respectively generating a first output signal and a second output signal, the output end of the transducer being an electronic transformer. Operatively connected to a producer unit, the unit generates an output signal that depends on the first and second output signals of the transducer, by means of an amplification function dependent on the spatial angle at which the transducer receives the acoustic signal. As being, A phase difference detection unit having its input terminal operatively connected to the output terminal of the converter and generating a phase difference-dependent signal at its output terminal; Its first input is operatively connected to an output of the phase difference detection unit, at least one of its second inputs is operatively connected to a factor value selection source, and its third input is at least of the outputs of the at least two converters. A phase processing unit operatively connected to one, the phase processing unit generating an output signal having a pacing according to signals at the first input terminal and at least one second input terminal in accordance with a signal at the third input terminal; And a beam-former having at least two inputs, a first input being operatively connected to an output of the phase processing unit, and a second input being operatively connected to at least one of the outputs of the at least two transducers. 14. The apparatus of claim 13, wherein the factor value selection source generates a constant or frequency dependent signal value. 15. The apparatus of claim 13 or 14, wherein the third input of the phase processing unit is operatively connected to one output of the at least two transducers. 16. The apparatus of any one of claims 13 to 15, wherein the third input of the phase processing unit is connected to an output of a beam-former unit, and the input of the beam-former unit is operably connected to the output of the at least two transducers. The device to be connected. 17. The apparatus of claim 16, wherein the beam-forming unit includes an additional adding unit, wherein one input of the adding unit is operatively connected to an output of one of the at least two transducers, and the other input is via a time-delay unit. Device connected to the output of the other of the at least two transducers. 18. The apparatus of any one of claims 13 to 17, wherein the second input of the beam-former processing unit is operatively connected to one of the at least two transducers. 19. The apparatus of any one of claims 13 to 18, wherein the second input end of the beam-former processing unit is operatively connected to an output end of an adding unit, wherein the first input end of the adding unit is at least via the time-delay unit. And a second input of the addition unit is operatively connected to an output of the other of the at least two converters. 20. The apparatus according to any one of claims 13 to 19, wherein the output stages of the at least two transducers are operatively connected to the input stages of an additional adding unit, one of which goes through a time-delay unit and the further adding unit. And an output terminal of is operatively connected to a third input terminal of the phase processing unit and a second input terminal of the beam-former processing unit. 20. The apparatus of any one of claims 13 to 19, wherein the outputs of the at least two converters are respective analog-to-digital converters, time domain to frequency domain transform units, and the phase difference detection unit. The apparatus is generated via the phase processing unit and the beam-former processing unit operating in the frequency domain, and the output of the transducer unit is generated through a frequency domain to time domain conversion unit. . 22. The device according to any one of claims 13 to 21, wherein said at least two transducers have a physical distance of no more than 20 mm from each other.