EP3461147B1 - Method for operating a hearing device - Google Patents

Description

The invention relates to a method for operating a hearing aid, a first input signal being generated from a sound signal by a first input transducer, a second input signal being generated from the sound signal by a second input transducer. Directional signal is formed, and an output signal is generated from the amplification directional signal.

In a hearing aid, a sound signal from the environment is converted into corresponding electrical signals by one or more input transducers, amplified depending on the frequency band, among other things, to correct a hearing loss of the hearing aid user, and the signal amplified in this way is converted into an output sound signal by an output transducer, which is sent to the hearing of the user. Two basic tasks of the hearing aid are to present the user with a sound image that is tailored to his or her individual requirements caused by the hearing loss, and in which potential useful signals are masked as little as possible by noise, and thus the most favorable signal possible. to noise ratio (SNR) is present.

For a hearing aid with at least two input transducers, this can be achieved by applying directional microphones to the corresponding input signals, if necessary by applying a frequency band. For this purpose, it is assumed that useful signals such as speech or music usually arrive at the user from a clearly defined direction, whereas many types of noise or interference come from a comparatively wide angle range originate, and thus no clear direction for a sound source can be assigned.

In most implementations of directional microphones in hearing aids, it is moreover assumed that a user instinctively directs his line of sight towards the source of a useful signal, so that the directional microphone has to be aligned essentially in the frontal direction of the user in order to suppress interference. In addition to the desired suppression of background noise, however, this sometimes leads to an unnatural perception of the environment. Sound events that occur away from the preferred direction of the directional microphone are masked out by the noise suppression, regardless of whether they are required for a realistic reproduction of the surrounding situation or not. A localization of such sound events is therefore often not possible in a satisfactory manner for the user of the hearing aid, which can impair his overall perception of the surroundings.

In addition, existing algorithms of the directional microphone do not take sufficient account of the individual anatomical conditions and the resulting restrictions that result from this, for example, to the directional field of a real ear. For example, due to the shape of the pinna, a human ear has a significantly lower sensitivity to sound signals towards the rear, while the shape of the concha and the auditory canal mean that the direction of maximum hearing sensitivity in the broadest sense is directed obliquely forward, the exact maximum depending on the individual anatomy varies. For a hearing experience that is as realistic as possible, such circumstances must be taken into account. The possibility of forming a directional microphone from two omnidirectional signals, which are each generated at one ear of the user, is also not able to adequately reproduce the anatomical conditions and the restrictions resulting therefrom with binaural hearing aid systems.

the US 2012/189147 A1 teaches, by means of two microphone signals of a hearing aid, first of all a first directional signal directed at a speaker and a second To form directional signal, which has a total attenuation in the direction of the speaker. On the basis of the signal level of the two directional signals, a distance between the speaker is determined, by means of which a gain factor for the first directional signal is determined.

the US 2014/198934 A1 calls a hearing aid system with a hearing aid and an external remote control, by means of which a wearer of the hearing aid can indicate the directions of useful signal and background noise sources so that signal processing in the hearing aid to improve a signal-to-noise ratio of the useful signals can take place on the basis of this input.

The invention is therefore based on the object of specifying a method for operating a hearing aid which allows the most realistic spatial hearing sensation possible, while at least offering the possibility of taking into account user-specific anatomical features for the spatial hearing sensation.

The stated object is achieved according to the invention by a method for operating a hearing aid, a first input signal being generated from a sound signal by a first input transducer, a second input signal being generated from a sound signal by a second input transducer, a first angle and an angular range being specified be, with frequency band based on the first input signal, the second input signal and the first angle, an attenuation directional signal is formed which has a relative attenuation at least for a second angle located in the angular range around the first angle, and thereby an overlay parameter is determined, based on of the first input signal and the second input signal as well as the superimposition parameter and / or the second angle, a directional gain signal is formed which has a relative gain for the second angle, wherein from the directional attenuation signal and an angle-emphasized directional signal is generated from the amplification directional signal, and an output signal based on the angle-emphasized directional signal is produced. Advantageous embodiments, some of which are seen in isolation, are the subject matter of the subclaims and the following description.

The first input signal and the second input signal preferably each have an omnidirectional directional characteristic. The formation of the attenuation directional signal on the basis of the first input signal and the second input signal takes place in such a way that a plurality of intermediate signals, each with a non-trivial directional characteristic, are initially formed from the first input signal and the second input signal, and then from these intermediate signals depending on the first Angle the attenuation directional signal is formed, for example by linear superposition. The same intermediate signals are also used for generating the directional gain signal (depending on the superposition parameter and / or the second angle).

As an alternative to this, it is also conceivable to form the attenuation directional signal directly by superimposing the first input signal on the second input signal with a time delay. The same is also possible for the directional amplification signal.

The specification of the first angle and the angular range can also take place implicitly, that is to say for example by means of parameters, provided that the corresponding parameters clearly define the first angle or the angular range. For example, if the attenuation directional signal is to be formed by superimposing intermediate signals, the first angle can be implicitly specified by a preliminary overlay parameter a0, which corresponds to a minimum sensitivity for the attenuation directional signal at the first angle. The final overlay parameter a, which corresponds in particular to a sensitivity minimum at the second angle, can then take place through a variation, for example in the form of a minimization of the signal level, of the overlay parameter over a range Δa which exactly corresponds to the angle range.

A relative attenuation for the attenuation directional signal at the second angle is to be understood in particular to mean that at this angle the sensitivity assumes a significantly lower value than the global maximum of the directional characteristic, and in particular has a local minimum. The condition of the local minimum can, however, also be relaxed to the effect that it can be found at least in the angular range around the first angle, provided that the sensitivity increases monotonically from the minimum over the entire angular range and takes on significantly lower values than the global maximum. The relative amplification of the amplification directional signal at the second angle is to be understood here in particular as a sensitivity which is considerably increased compared to the global minimum value, and in particular as an absence of local minimums of the sensitivity in the immediate vicinity of the second angle, for example over the specified angular range away. The specified angular range can in particular include a widening of up to +/- 15 °, preferably up to +/- 10 °. The relative attenuation in the attenuation directional signal can then be understood in this context in particular to mean that the attenuation directional signal at the second angle has a significantly lower sensitivity over a solid angle range which is considerably larger than the specified angle range, for example in a quadrant as the maximum value in the quadrant in which the second angle is located. The relative amplification by the amplification directional signal can then be understood in this context to mean that the amplification directional signal at the second angle has a significantly greater sensitivity than the minimum value of the sensitivity for the amplification directional signal in the quadrant.

The angle-emphasized directional signal can now be constructed in such a way that it itself has a relative gain as a result of the contributions of the amplification directional signal in the direction of the second angle. Here, the attenuation directional signal or its contributions in the angle-emphasized directional signal provides an additional degree of freedom in order to be able to set a strength of the directional effect of the angle-emphasized directional signal with respect to the second angle. As a result of the relative attenuation for the attenuation directional signal in the direction of the second angle, which is essential relative to the global maxima of the sensitivity of the attenuation directional signal and, in the ideal case, leads to complete suppression in the direction of the second angle, the proportion of sound signals whose source is remote can be set via the proportion of the attenuation directional signal in the angle-emphasized directional signal of the second angle is without this setting resulting in a significant change in the second angle, which would require a renewed adjustment of the amplification directional signal.

The method steps mentioned are preferably to be carried out in each case in frequency bands and the angle-emphasized directional signal is preferably to be adapted in frequency bands via an output level to the individual requirements of the hearing aid user. Such an adaptation can, however, also take place after an additional, possibly directional noise suppression and / or after a renewed addition of omnidirectional signal contributions in frequency bands.

According to the invention, the attenuation directional signal and the amplification directional signal are each formed from the first input signal and the second input signal by a time-delayed superposition or from a linear superposition of intermediate signals, which are each derived from the first input signal and the second input signal -Directional signal the signal level is minimized over the angular range by the first angle, and thereby the second angle is determined. This means in particular that the first input signal and the second input signal are directly or, in the case of a formation from intermediate signals derived therefrom, indirectly each entered linearly in the attenuation directional signal. A minimization of the signal level for the formation of the attenuation directional signal is understood here to mean that the first input signal and the second input signal or the intermediate signals derived therefrom are correspondingly convexly superimposed, and the superimposition parameter with regard to the signal level is minimized, the minimization under the Boundary condition takes place that the resulting second angle for a local minimum of the sensitivity within of the specified angular range has to lie around the first angle. The signal resulting from this minimization is now taken as the attenuation directional signal, and the angle corresponding to the local minimum sensitivity for this signal is used as the second angle and the resulting superimposition parameter for the amplification directional signal and / or further signal processing.

The formation of the attenuation directional signal on the basis of such a minimization has the advantage that the signal components which are included in the angle-emphasized directional signal to reinforce the corresponding directional effect make particularly small contributions to the overall level of the angle-emphasized directional signal, and thus the additional degree of freedom for the directional effect as a whole Sound image of the surrounding sound less impaired.

In a further advantageous embodiment, a first directional signal and a second directional signal are formed as intermediate signals on the basis of the first input signal and the second input signal. The first directional signal and the second directional signal are preferably each formed from a time-delayed superposition of the first input signal and the second input signal. Particularly preferred is the respective time delay given by the sound path from the first input transducer to the second input transducer or vice versa, so that the first directional signal has a cardioid-shaped directional characteristic with respect to the axis defined by the first input transducer and the second input transducer, and the second directional signal accordingly an anti-cardioid polar pattern.

Appropriately, the attenuation directional signal is formed based on the first directional signal and the second directional signal as a function of the first angle and the angular range, and / or the amplification directional signal is based on the first directional signal and the second directional signal as a function of the superimposition parameter and / or the second Formed angle.

The use of the mentioned directional signals as intermediate signals has the advantage that to generate the attenuation directional signal as well as the amplification directional signal, and in particular to estimate the corresponding angle-dependent attenuation or amplification, no variations of the time parameters have to take place, but rather a variation is carried out on the basis of an overlay parameter can be. As a result, no delays with variations, which in individual cases could be below a sampling period, have to be implemented, but only algebraic operations.

A notch filter directional signal is particularly preferably formed as the attenuation directional signal. This is to be understood as a signal whose directional characteristic has a sensitivity in at least one direction which is reduced by at least six dB, preferably by several tens of dB, compared to the global maximum value of the sensitivity, the shape of the directional characteristic at the minimum value corresponding to the sensitivity of a notch. The minimum, that is to say the "notch", is preferably located at the second angle ϑ2. With a notch filter as an attenuation directional signal, the following angle-dependent method steps can be controlled particularly easily, since the signal contributions of the attenuation directional signal can be neglected at the second angle.

gebildet werden, wobei S das winkelbetonte Richtsignal, L das Verstärkungs-Richtsignal, N das Abschwächungs-Richtsignal und c ein Linearfaktor ist. Je größer hierbei der Betrag von c ist, desto stärker ist hierbei die Richtwirkung des winkelbetonten Signals.The angle-emphasized directional signal is preferably formed by a superposition, that is to say in particular by a linear superposition, of the attenuation directional signal and the amplification directional signal. In particular, the angular directional signal can be achieved by superimposing the shape $$\mathrm{S.}=\mathrm{L.}+\mathrm{c}\cdot \mathrm{N}$$

be formed, where S is the angle-emphasized directional signal, L is the amplification directional signal, N is the attenuation directional signal and c is a linear factor. The greater the amount of c, the stronger the directivity of the angular signal.

The signal level is expediently minimized in order to generate the angle-emphasized directional signal. In this way it can be achieved that the contributions of the attenuation directional signal, which represent the spatial directions apart from the desired preferred direction of the second angle, are included in the angle-emphasized directional signal to the smallest possible extent.

It also proves to be advantageous if directional noise suppression is carried out to generate the output signal, for which purpose the angle-emphasized directional signal is given as a useful signal and the attenuation directional signal is given as an interference signal. Directional noise suppression is basically an algorithm used in many hearing aids to improve the SNR. In this case, a directional useful signal is assumed and an amplifying directional signal is aimed at this direction. The other spatial directions are weakened because it is assumed that the background noise component is higher in these spatial directions. Within the scope of the present method, the amplification or attenuation directional signal that is present in any case can now be used for amplification or for weakening. This is particularly advantageous if the attenuation directional signal has already been generated by minimizing the total signal level over the specified angular range, because in this case it can be assumed that the useful signal component in the attenuation directional signal is minimal, while the useful signal Share in the most complementary amplification directional signal is particularly high. The directional signals generated as part of the method are advantageously used in a further signal processing process which is frequently used in hearing aids.

It also proves to be advantageous if an omnidirectional signal is added in a frequency-dependent manner in order to generate the output signal. The admixing can in particular consist of a simple linear combination with frequency-dependent linear factors. The spatial hearing perception of a person shows a considerable frequency dependence. By adding an omnidirectional signal in a frequency band, this frequency dependency can be taken into account in a particularly simple manner, with bands, in which there is usually a lower angular dependence of the hearing sensitivity, can be correctly mapped.

The invention also mentions a hearing aid with a first input transducer for generating a first input signal, a second input transducer for generating a second input signal, a signal processing unit and an output transducer for generating an output sound signal from an output signal, the signal processing unit being set up to use the first input signal and of the second input signal, the output signal by the method described above. The advantages mentioned for the method and its developments can be applied to the hearing aid in the same way. In a further advantageous embodiment, the invention also mentions a bilateral hearing aid system with two such hearing aids, and in particular a binaural hearing aid system in which the two hearing aids of the hearing aid system each transmit signal components to one another to improve the spatial hearing impression.

Fig. 1

in einem Blockschaltbild ein Verfahren zum Betrieb eines Hörgerätes für ein möglichst realistisches Hörempfinden.

An exemplary embodiment of the invention is explained in more detail below with reference to a drawing. The following are shown schematically in each case:

Fig. 1

in a block diagram, a method for operating a hearing aid for the most realistic hearing possible.

In Figure 1 a method 2 for operating a hearing aid 4 is shown schematically in a block diagram. The hearing aid 4 has a first input transducer 6 and a second input transducer 8, which generate a first input signal 12 and a second input signal 14 from a sound signal 10 from the surroundings. The first input transducer 6 and the second input transducer 8 are each designed as omnidirectional microphones in the present case. In a preprocessing step 16, a first directional signal 18 and a second directional signal 20 are now generated as intermediate signals from the first input signal 12 and the second input signal 14. Here, the first directional signal 18 has a directional characteristic 22 which is given by a cardioid, its preferred direction 24 runs along the axis 25, which is formed by the two input transducers 6, 8. The second directional signal 20 has a directional characteristic 26 which is complementary to the first directional signal 18, that is to say which, with regard to the axis 25, along the first input transducer 6 and the second input transducer 8 is formed by an anti-cardioid.

wobei N das Abschwächungs-Richtsignal 28 und R1 und R2 das erste bzw. zweite Richtsignal 18, 20 bezeichnen. Der entsprechende Überlagerungsparameter a für die Superposition wird schlussendlich so bestimmt, dass der resultierende Signalpegel des Abschwächungs-Richtsignals 28 über den Winkelbereich Δϑ hinweg minimal ist. Die Richtung minimaler Empfindlichkeit für das Kerbfilter 30 liegt somit nicht zwingend in Richtung des ersten Winkels ϑ1, sondern in Richtung eines zweiten Winkels ϑ2, welcher im Winkelbereich Δϑ um den ersten Winkel ϑ1 gelegen ist. Im Fall, dass der zweite Winkel ϑ2 in der vorderen Hemisphäre des Benutzers des Hörgerätes 4 liegt, sind zudem für die Überlagerung das erste Richtsignal und das zweite Richtsignal zu vertauschen, also $$\begin{array}{cc}\mathrm{N}=\mathrm{R}2-\mathrm{a}\cdot \mathrm{R}1& \mathrm{für}\mathrm{\hspace{0.17em}}\mathrm{\vartheta }2>90°\end{array}.$$

An attenuation directional signal 28 is now formed from the first directional signal 18 and the second directional signal 20. For this purpose, a first angle ϑ1 is first specified externally, it being possible for the specification to be static or dynamic. A static specification can be made here, for example, by storing, among other things, anatomically determined angle values in a database, while a dynamic specification can also include the current hearing situation. The attenuation directional signal 28 is now first implemented as a notch filter 30 in the direction of the predetermined first angle ϑ1. The notch filter 30 is obtained from a linear superposition of the first directional signal 18 with the second directional signal 20. For this purpose, an angular range Δϑ is also specified, in which the direction of minimum sensitivity of the notch filter 30 can vary by the first angle ϑ1. The attenuation directional signal 28 is thus given as $$\begin{array}{cc}\mathrm{N}=\mathrm{R.}1-\mathrm{a}\cdot \mathrm{R.}2& \left(\mathrm{for}\mathrm{}\mathrm{<figure-callout\; id="2"\; label="\theta "\; filenames="imgf0001.png"\; state="\{\{state\}\}">\vartheta </figure-callout>}2>90°\right)\end{array},$$

where N denotes the attenuation directional signal 28 and R1 and R2 denote the first and second directional signals 18, 20, respectively. The corresponding superimposition parameter a for the superposition is ultimately determined in such a way that the resulting signal level of the attenuation directional signal 28 is minimal over the angular range Δϑ. The direction of minimum sensitivity for the notch filter 30 is therefore not necessarily in the direction of the first angle ϑ1, but in the direction of a second angle ϑ2, which is located in the angular range Δϑ around the first angle ϑ1. In the event that the second angle ϑ2 lies in the front hemisphere of the user of the hearing aid 4, the first directional signal and the second directional signal must also be interchanged for the superposition, that is to say $$\begin{array}{cc}\mathrm{N}=\mathrm{R.}2-\mathrm{a}\cdot \mathrm{R.}1& \mathrm{for}\mathrm{}\mathrm{<figure-callout\; id="2"\; label="\theta "\; filenames="imgf0001.png"\; state="\{\{state\}\}">\vartheta </figure-callout>}2>90°\end{array}.$$

A directional amplification signal 34 is now formed from the first directional signal 18 and the second directional signal 20 on the basis of the superimposition parameter a or on the basis of the angle ϑ2 established by this. The amplification directional signal 34 has a directional characteristic 36, the sensitivity of which preferably has a local maximum at the second angle ϑ2, or a local maximum can be found in the angular range Δϑ around the first angle ϑ1. The angular range Δϑ can be formed here, for example, by an interval of 20 °, that is ϑ1 +/- 10 °.

erfolgen, wobei L das Verstärkungs-Richtsignal 34 bezeichnet und b ein Überlagerungsparameter ist, welcher in Abhängigkeit vom Überlagerungsparameter a des Abschwächungs-Richtsignals 28 zu wählen ist. Im Fall, dass der zweite Winkel ϑ2 in der hinteren Hemisphäre des Benutzers des Hörgerätes 4 liegt, ist b gegeben durch -a. Liegt der zweite Winkel ϑ2 in der frontalen Hemisphäre des Benutzers, so ist b = a-2. Hierdurch wird die Richtcharakteristik 36 des Verstärkungs-Richtsignals 34 variiert zwischen einem Kardioid bzw. Antikardioid und einer omnidirektionalen Charakteristik. Das Verstärkungs-Richtsignal 34 wird nun noch einer Amplitudenkompensation 38 unterzogen, welche den für identische omnidirektionale Eingangssignale unterschiedlichen à-priori-Ausgangspegeln von kardiod-förmigen und omnidirektionalen Richtcharakteristiken Rechnung trägt.The amplification directional signal 34 is formed in particular in the direction of the second angle ϑ2 as a type of complementary directional signal to the attenuation directional signal 28. While the attenuation directional signal 28 as a notch filter 30 should have the lowest possible sensitivity in the direction of the second angle ϑ2, the amplification directional signal 34 in the direction of the second angle ϑ2 has the smallest possible attenuation relative to the maximum sensitivity. This can be done, for example, by a linear superposition of the first directional signal 18 with the second directional signal 20 of the shape $$\mathrm{L.}=\mathrm{R.}1-\mathrm{b}\cdot \mathrm{R.}2$$

take place, where L denotes the amplification directional signal 34 and b is an overlay parameter which is to be selected as a function of the overlay parameter a of the attenuation directional signal 28. In the event that the second angle ϑ2 lies in the rear hemisphere of the user of the hearing aid 4, b is given by -a. If the second angle ϑ2 is in the frontal hemisphere of the user, then b = a-2. As a result, the directional characteristic 36 of the amplification directional signal 34 varies between a cardioid or anti-cardioid and an omnidirectional characteristic. The amplification directional signal 34 is now subjected to amplitude compensation 38, which takes into account the different a priori output levels of cardiodic and omnidirectional directional characteristics for identical omnidirectional input signals.

wobei S das winkelbetonte Richtsignal 40 bezeichnet und c einen Überlagerungsparameter, welcher mit zunehmendem Betrag zu einer Verstärkung der Richtwirkung hinsichtlich des zweiten Winkels ϑ2 führt. Der Überlagerungsparameter c kann hierbei aus einer Minimierung des Gesamtausgangspegels des winkelbetonten Richtsignals 40 gewonnen werden.From the attenuation directional signal 28 and the amplification directional signal 34, an angular directional signal 40 is now formed by means of linear superposition. This is of the form $$\mathrm{S.}=\mathrm{L.}+\mathrm{c}\cdot \mathrm{N}$$

where S denotes the angular directional signal 40 and c denotes an overlay parameter which, with increasing magnitude, leads to an intensification of the directivity with regard to the second angle ϑ2. The superimposition parameter c can be obtained from a minimization of the overall output level of the angle-stressed directional signal 40.

The angle-emphasized directional signal 40 is now constructed in such a way that, due to the component of the amplification directional signal 34 in the direction of the second angle ϑ2, there is a particularly high sensitivity, while the minimization processes, depending on the real sound events, cause interference from other directions to be caused by the attenuation directional signal 28 can be suppressed without this significantly affecting the contributions of the amplification directional signal 32. The construction of the attenuation directional signal 28 by minimizing the total output level over the angular range Δϑ by the specified first angle ϑ1 also leads to a particularly good adaptation of the attenuation directional signal to the currently present sound events, within the framework of the specification of the first angle ϑ1 as the desired one Preferred direction.

The angle-emphasized directional signal 40 can now also be subjected to directional noise suppression 42, the angle-emphasized directional signal 40 itself being interpreted as the useful signal 44 and the attenuation directional signal 28 being interpreted as the background noise component 46. Signal components of an omnidirectional signal, for example the first input signal 12, are now added to the signal 48 resulting from the directional noise suppression 42, and so the output signal 50 is generated, which is converted into an output sound signal by an output transducer 52 of the hearing aid 4 54 is converted, which is supplied to the hearing of the user of the hearing aid 4. Due to the portion of the angle-emphasized directional signal 40 in the output signal 50, the output sound signal 54 reproduces the acoustic environment of the hearing aid 4 in a particularly realistic manner, since angle-dependent or space-dependent attenuations are modeled on those caused by a real outer ear. The directivity or attenuation of real hearing can be controlled by frequency band via the portion of the omnidirectional first input signal 12 in the output signal 50. In addition, the signal level of the output signal can be lowered or raised individually in a user-specific manner in individual frequency bands.

Although the invention has been illustrated and described in more detail by the preferred exemplary embodiment, the invention is not restricted by this exemplary embodiment. Other variations can be derived therefrom by the person skilled in the art without departing from the scope of protection of the invention.

List of reference symbols

2

proceedings

4th

Hearing aid

6th

first input transducer

8th

second input transducer

10

Sound signal of the environment

12th

first input signal

14th

second input signal

16

Preprocessing step

18th

first directional signal

20th

second directional signal

22nd

Directional characteristic

24

Preferred direction

25th

axis

26th

Directional characteristic

28

Attenuation directional signal

30th

Notch filter

34

Gain directional signal

36

Directional characteristic

38

Amplitude compensation

40

Angular directional signal

42

directional noise reduction

44

Useful signal

46

Noise component

48

resulting signal

50

Output signal

52

Output converter

54

Output sound signal

ϑ1

first angle

ϑ2

second angle

Δϑ

Angular range

Claims (10)

1. A method (2) for operating a hearing aid (4),

   wherein a first input signal (12) is generated from a sound signal (10) by a first input transducer (6),

   wherein a second input signal (14) is generated from the sound signal (10) by a second input transducer (8),

   wherein a first angle (ϑ1) and an angle range (Δϑ) are provided, wherein, in a frequency band-wise manner,

   - a directional attenuation signal (28) is formed on the basis of the first input signal (12), the second input signal (14) and the first angle (ϑ1), said directional attenuation signal (28) having a relative attenuation at least for a second angle (ϑ2) located in the angular range (Δϑ) around the first angle (ϑ1), and thereby determining a superposition parameter,

   - a directional amplification signal (34) is formed on the basis of the first input signal (12) and the second input signal (14), as well as on the basis of the superposition parameter and/or the second angle (ϑ2), said directional amplification signal (34) having a relative amplification for the second angle (ϑ2),

   - an angle-enhanced directional signal (40) is generated from the directional attenuation signal (28) and the directional amplification signal (34), and

   - an output signal (50) is generated on the basis of the angle-enhanced directional signal (40),

   wherein the directional attenuation signal (28) and the directional amplification signal (34) are respectively formed from the first input signal (12) and the second input signal (14) by a time-delayed superposition or from a linear superposition of intermediate signals (18, 20), each of which are respectively derived from the first input signal (12) and from the second input signal (14),

   wherein for forming the directional attenuation signal (28), the signal level is minimized over the angular range (Δϑ) around the first angle (ϑ1), thereby determining the second angle (ϑ2).
2. The method (2) according to claim 1,
   wherein, on the basis of the first input signal (12) and the second input signal (14), a first directional signal (18) and a second directional signal (20) are formed as intermediate signals.
3. The method (2) according to claim 2,

   wherein the directional attenuation signal (28) is formed on the basis of the first directional signal (18) and the second directional signal (20) as a function of the first angle (ϑ1) and the angular range (Δϑ), and/or.

   wherein the directional amplification signal (34) is formed on the basis of the first directional signal (18) and the second directional signal (20) in dependence of the superposition parameter and/or the second angle (ϑ2).
4. The method (2) according to one of the preceding claims,
   wherein a directional notch filter signal (30) is formed as the directional attenuation signal (28).
5. The method (2) according to one of the preceding claims,
   wherein the angle-enhanced directional signal (40) is formed by a superposition of the directional attenuation signal (28) and the directional amplification signal (34).
6. The method (2) according to claim 5,
   wherein the signal level is minimized for the generation of the angle-enhanced directional signal (40).
7. The method (2) according to one of the preceding claims,

   wherein for the generation of the output signal (50), a directional noise suppression (42) is performed, and

   wherein, to this end, the angle-enhanced directional signal (40) is provided as a useful signal (44) and the directional attenuation signal (28) is provided as an interference signal (46).
8. The method (2) according to one of the preceding claims,
   wherein for the generation of the output signal (50), an omni-directional signal (12, 14) is added in a frequency band-wise manner.
9. A hearing aid (4) with a first input transducer (6) for generating a first input signal (12), a second input transducer (8) for generating a second input signal (14), a signal processing unit, and an output transducer (54) for generating an output sound signal (54) from an output signal (50), wherein the signal processing unit is configured to generate the output signal (50) on the basis of the first input signal (12) and the second input signal (14) by means of a method (2) according to one of the preceding claims.
10. A binaural hearing system comprising two hearing aids (4) according to claim 9.

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