EP4145859A1 - Method for operating a hearing aid - Google Patents

Abstract

The invention relates to a method (40) for operating a hearing aid (4) which has a charging connection (18) with two electrical contacts (20). A drop in an electrical voltage (44) present at the two contacts (20) is detected. An operating mode (60) of the hearing aid (4) is set as a function of the progression over time (50) of the drop. The invention also relates to a hearing aid (4) and a system (2) with a hearing aid (4) and a charging device (28).

Description

The invention relates to a method for operating a hearing aid. In addition, the invention relates to a hearing aid and a system that has a hearing aid and a charging device. The hearing device includes a charging connection with two electrical contacts.

People who suffer from hearing loss usually use a hearing aid device. In this case, ambient noise is usually detected by means of an electromechanical sound transducer. The electrical signals created on the basis of the ambient noise are amplified by means of an amplifier circuit and introduced into the person's auditory canal by means of a further electromechanical converter in the form of a receiver. In most cases, the recorded sound signals are also processed, for which purpose a signal processor in the amplifier circuit is usually used. In this case, the amplification is matched to any hearing loss of the hearing aid device wearer.

Electrical energy is required to operate the converter and the amplifier circuit. This is usually provided in the form of a battery that is arranged in a housing of the hearing aid device. This provides freedom of movement for the person using the hearing aid device, ie the hearing aid device wearer. If the battery is empty, it is necessary to replace it. For this purpose, the housing usually has a flap through which the battery is accessible.

The disadvantage here is that due to leaks, foreign particles or moisture can penetrate into the housing and thus those arranged there Can damage hearing aid components, such as the amplifier circuitry. As a result, a comparatively large seal is required. Due to the comparatively small amount of space available, construction costs and manufacturing costs are increased. Due to the comparatively small dimensions of the flap, additional aids are usually required for operation, and incorrect operation by the person cannot be ruled out.

An alternative therefore provides to use a rechargeable battery. If the battery is empty, it is only necessary to recharge it to provide further functionality, without the need for disassembly. As a result, it is possible to make the case substantially dense, and operation is simplified. For charging, the hearing aid usually has a charging connection with two electrical contacts. These interact with two counter-contacts of a charger. For example, in this case the counter-contacts are mechanically contacted directly with the contacts, with the counter-contacts being separated from the contacts after the loading process has ended. As an alternative to this, the contacts and mating contacts interact via electrical coils, so that the exchange of energy between the hearing aid device and the charging device takes place inductively. The charger itself is usually connected to a supply network by means of a plug. The electrical voltage present between the counter-contacts, which is used to charge the hearing aid, is created using the electrical voltage provided by the supply network.

When the hearing aid is charged, the user usually removes it from the charger for immediate use. In order to increase the comfort for the user, the hearing aid is switched to a working mode as soon as it is removed from the charging device. Detachment from the charging device is usually detected by a drop in the electrical voltage present at the contacts, the interaction of which with the counter-contacts is interrupted when the device is removed from the charging device. However, it is also possible for the charger plug to be disconnected from the mains supply. As a result, the electrical voltage present at the mating contacts drops, and consequently also the electrical voltage present at the contacts Tension. In this case, however, the hearing device should usually not be used, but rather it should be operated in as energy-saving a manner as possible until it is actually used. So that the hearing aid is not put into the working mode, it is also necessary to determine whether the hearing aid is still connected to the charging device when the electrical voltage present at the contacts drops. A third contact is used for this purpose, for example, or there is a sensor, such as a Hall sensor, by means of which an electric field created by means of the counter-contacts is detected. As a result, however, there are additional components, which is why manufacturing costs are increased.

The invention is based on the object of specifying a particularly suitable method for operating a hearing aid and a particularly suitable hearing aid as well as a particularly suitable system with a hearing aid and a charging device, in which case comfort is increased and/or production costs are reduced.

This object is achieved according to the invention by the features of claim 1 with regard to the method, by the features of claim 7 with regard to the hearing aid and by the features of claim 9 with regard to the system. Advantageous developments and refinements are the subject of the respective dependent claims.

The method is used to operate a hearing aid. The hearing device is, for example, a headphone or includes a headphone. However, the hearing device is particularly preferably a hearing aid device. The hearing aid device is used to support a person suffering from a hearing loss. In other words, the hearing aid device is a medical device, by means of which a partial hearing loss is compensated for, for example. The hearing aid device is, for example, a "receiver-in-the-canal" hearing aid device (RIC; ex-receiver hearing aid device), an in-the-ear hearing aid device, such as an "in-the-ear" hearing aid device, an "in-the -canal" hearing aid (ITC) or a "complete-in-canal" hearing aid (CIC), hearing glasses, a pocket hearing aid, a bone conduction hearing aid or an implant. Alternatively this is Hearing aid device A behind-the-ear hearing aid device that is worn behind an auricle.

The hearing aid is intended and set up to be worn on the human body. In other words, the hearing aid preferably comprises a holding device, by means of which attachment to the human body is possible. Alternatively or in combination with this, the hearing device is suitably shaped. If the hearing device is a hearing aid device, the hearing device is provided and set up to be arranged, for example, behind the ear or within an auditory canal. In particular, the hearing device is wireless and intended and set up to be at least partially inserted into an auditory canal.

The hearing device preferably has a hearing device housing. Substantially all other components of the hearing device are preferably arranged in the hearing device housing, at least preferably any electronics such as an amplifier circuit. For example, the hearing device housing is made in one piece or particularly preferably from several components. The hearing aid housing is suitably made from a plastic, in particular using a plastic injection molding process. Thus, a design freedom is comparatively large. Also, the weight of the hearing device housing is not excessively increased.

A microphone, for example, is arranged in the hearing aid housing, ie in particular an electromechanical sound transducer. The microphone is used to capture ambient noise and is suitable for this purpose, in particular provided and set up. In particular, the microphone is connected electrically and/or in terms of signals to any electronics, in particular the amplifier circuit, or other electrical/electronic components of the hearing aid. By means of this, the signals recorded by means of the microphone are suitably processed.

The hearing aid particularly preferably comprises a further electromechanical sound transducer, in particular a receiver, by means of which the means signals processed by any amplifier circuit. For example, the receiver is also arranged in the hearing device housing or in another housing. For example, the two housings are connected in terms of signaling by means of a line, in particular if the hearing device is an RIC hearing aid device.

The hearing device includes a charging connection, it being possible to feed electrical energy into the hearing device via the charging connection. For this purpose, the charging connection has two electrical contacts, which are also simply referred to below as contacts. When the hearing device is being charged, when electrical energy is being fed in or at least when there is an interaction with a charging device, an electrical voltage is present on the charging device. The charger serves to charge the hearing device, ie to supply the hearing device with electrical energy. The charger is suitable for this, in particular provided and set up.

In this case, the charging connection is designed mechanically, for example, and the two electrical contacts are formed, for example, by means of pogo pins, a mechanical plug or an electrically conductive plate, or at least each include these. In this case, the electrical contacts are, for example, introduced directly into any wall of the hearing device housing or are located in a receptacle which is covered, for example, by means of a flap. As an alternative to this, the two electrical contacts are contacted with an electrical coil and charging takes place wirelessly. A rectifier, such as a diode rectifier, is expediently arranged between the electrical contacts and the (electrical) coil, so that an electrical DC voltage is present at the electrical contacts if the hearing aid interacts with the charging device. In this case, a capacitor or another capacitance is particularly preferably connected between the contacts, by means of which the electrical voltage is stabilized. The electrical voltage present at the electrical contacts is therefore essentially constant given a constant interaction with the charging device.

The charger preferably has two mating contacts. If the charging takes place mechanically, for example by means of a cable, one of the counter-contacts is mechanically directly in contact with a respectively assigned contact. If the charging takes place inductively, for example, the mating contacts are electrically contacted in particular with a coil, preferably via an inverter. In this case, an electrical DC voltage is expediently applied to the mating contacts.

The hearing device preferably includes an energy store, by means of which the energy supply is provided. The energy store is expediently used to power any electronics/acoustic converters. The energy store is suitably arranged inside the possible hearing device housing. The energy store is suitably rechargeable, and preferably a rechargeable battery. In particular, the energy store is contacted with the two electrical contacts, for example directly or via any charging circuit. In this case, the charging circuit preferably includes a voltmeter, which is designed, for example, as an A/D converter or at least includes this. In particular, the charging of the energy store via the charging connection is regulated or at least controlled by means of the charging circuit. In this way it is possible to increase a number of possible charging cycles.

The method provides for a drop in an electrical voltage present at the two contacts to be detected. The voltage applied to the electrical contacts is expediently an electrical direct voltage. In this case, the electrical voltage due to the interaction with the charging device is expediently present at the two contacts. Because of the interaction, the hearing aid is charged, for example. In order to provide the interaction, as a result of which the electrical voltage present at the two contacts is present, the hearing aid, expediently the charging connection, is connected to the charging device, in particular if charging is carried out wirelessly. As an alternative to this, in particular a mating plug or the like is plugged into the charging connection, so that corresponding mating contacts are in direct mechanical contact with the contacts of the charging connection.

After the electrical voltage is applied to the two contacts, i.e. between them, it is detected that this voltage is reduced. In this case, in particular, an amplitude of the electrical voltage applied decreases, in particular if an electrical alternating voltage is applied to the two contacts. Particularly preferably, however, a DC voltage is applied to these, and the magnitude of the electrical voltage decreases as it drops.

In a further work step, the course over time of the drop in the electrical voltage is recorded and an operating mode of the hearing aid is set as a function of this. In particular, one of a number of operating modes of the hearing device is selected here, and the hearing device is then operated in accordance with the selected and set operating mode. For this purpose, particular components of the hearing aid are energized differently.

When the interaction between the charging device and the hearing device is terminated, in particular because the hearing device is removed from the charging device, this occurs comparatively abruptly, so that the electrical voltage present at the two contacts drops comparatively quickly. On the other hand, if the charger is disconnected from any supply network or at least current flow to the charger is terminated, due to the inductances and/or capacitances present in the charger, operation of the charger is still partially maintained for a short period of time, although the between the charger and amount of energy exchanged by the hearing aid decreases. As a result, the electrical voltage present at the two contacts drops in a different way. Since the operating mode of the hearing device is set as a function of the time course of the decrease, it is set as a function of how the interaction is ended. Therefore, the hearing aid is then operated differently depending on whether the hearing aid is detached from the charger or whether the charger itself is no longer energized. Because of the method, the needs of the user of the hearing device are taken into account, so that comfort is increased. However, here are no additional components such as sensors required, which is why manufacturing costs are reduced.

For example, in order to determine the course over time, the electrical voltage is recorded only at two different points in time. In this case, for example, the time interval between the two points in time is specified, and the electrical voltage is recorded at the two different points in time. Depending on the magnitude of the difference in electrical voltage at the two points in time, conclusions are drawn about the respective course over time. In an alternative to this, the values of the electrical voltage are specified, for example, and the course over time is based on the time interval between the points in time at which the electrical voltage corresponds to the specified values. Since only two measurements are carried out in both variants, or at least the course over time is determined only on the basis of two different values, complexity is reduced and consequently also the computing effort. The method is therefore comparatively economical in terms of resources, and it is possible to carry out the method even with a low-performance hearing device.

In an alternative, to determine the course over time, the electrical voltage is recorded over a comparatively long period of time and an analysis is carried out. For example, a Fourier analysis of the electrical voltage is carried out. However, a time derivative of the electrical voltage is particularly preferably created to determine the time profile. The derivation is preferably used as the course over time. For example, if the derivative has a certain maximum value, certain minimum value, and/or a certain mean value, a certain mode of operation is used, whereas if the derivative has a different minimum/maximum/mean value, a different mode of operation is used. Accuracy is increased due to the use of the derivation, and comparatively short-term fluctuations or other disturbances, for example, do not lead to a changed operation of the hearing device.

A stand-by operating mode is particularly preferably selected when the electrical voltage drops more slowly than a first limit value. In this case, for example, the difference between the electrical voltages that are detected at two different points in time that lie at a specific time interval from one another is smaller than a specific value, by means of which the first limit value is defined. As an alternative to this, the first limit value is determined using the derivative, and the derivative is expediently smaller than a further limit value. In the stand-by operating mode, for example, individual components or all components of the hearing aid are switched off, or one of the components or some of the components are operated with a comparatively low energy requirement, with the range of functions being restricted, for example. If the electrical voltage drops slowly, the connection with the charging device or at least the interaction with it still exists, so that it can be assumed that the charging device is no longer supplied with current and only any residual voltage that is present is reduced. In this case, the hearing device will probably not be used directly afterwards by the user, and the energy requirement of the hearing device is reduced due to the stand-by operating mode. Thus, if the user subsequently actually wants to use the hearing aid, it has a comparatively high charge level. If the hearing aid was already being operated in stand-by mode when charging, this is expediently left on.

Alternatively or particularly preferably in combination with this, a working mode is selected if the electrical voltage falls faster than a second limit value. For example, in this case the difference between the two electrical voltages detected at two different points in time that are at a constant time interval from one another is greater than a certain limit value, or the derivative, in particular a minimum, maximum or average, is greater than another limit. When the hearing aid is put into the working mode, some components of the hearing aid that have not been energized up to now are preferably energized. In particular, a control device or another circuit, in particular a microprocessor, is switched to the working mode from a stand-by operating mode. With the rapid sinking, the Interaction of the hearing aid with the charger ended comparatively abruptly, so it can be assumed that the hearing aid was mechanically removed from the charger. In this case, the user mostly wants to use the hearing device immediately, and due to the method, no additional operations are required for this. If the hearing aid has already been operated in the working mode, there is in particular no change in the operating mode.

The first limit value is particularly preferably selected to be equal to the second limit value, so that only one of two operating modes is selected in each case depending on the course of the decrease over time. Complexity is thus reduced and the user can understand the operation.

For example, the drop is detected when an amount of electrical energy fed into the energy store is below a specific value. However, the drop is preferably detected when the electrical voltage present at the two contacts falls below a third limit value. The third limit value is expediently comparatively high and is, for example, between 95% and 75%, between 90% or 70% or between 85% and 80% of the electrical voltage present at the electrical contacts during a charging process. Due to such a third limit value, fluctuations in the interaction of the charger with the hearing aid do not affect the charging process of the hearing aid, whereas the corresponding operating mode of the hearing aid is already selected if the hearing aid is detached from the charger relatively soon or the charger is no longer energized. Also, only the determination of the electrical voltage is required for the method, so that hardware requirements are reduced.

The hearing aid has a charging connection with two electrical contacts. For example, the charging connection is designed as an inductive charging connection or a wired one. In this case, the electrical contacts are in particular correspondingly adapted in each case, and an electrical contact is expediently connected to each of them, regardless of the respective configuration of the charging connection DC voltage when the hearing aid is charged or at least interacts with a charger. The hearing aid is operated according to a method in which a drop in an electrical voltage present at the two contacts is detected. An operating mode of the hearing device is then set as a function of the progression over time of the drop.

In particular, the hearing device includes a control unit that is suitable, in particular provided and set up, to carry out the method. The control unit is formed, for example, by means of electronics, which suitably also include a signal processor. The hearing aid expediently includes an energy store, such as a battery, which can be charged in particular by means of the charging connection. For this purpose, the energy store is electrically connected directly to the charging connection, for example, or particularly preferably by means of a charging circuit. In particular, the charging connection is part of the charging circuit.

An A/D converter is particularly preferably used to determine the course over time. The A/D converter is expediently also used to evaluate the electrical voltage present at the electrical contacts, and the start of the drop in the electrical voltage is detected in particular by means of the A/D converter. Any charging circuit is particularly preferably operated by means of the A/D converter. The A/D converter thus performs different tasks. A corresponding A/D converter is also already present in some hearing aids, so that in particular there are no additional hardware requirements. Thus, manufacturing costs are not increased.

The (digital) signals created by means of the A/D converter are particularly preferably evaluated by means of electronics in the hearing device, for example by means of a comparator. In particular, a signal processor is used for this purpose, which, for example, is used elsewhere to process the (acoustic) output signal, preferably if the hearing device is not being charged and/or if the hearing device is in the working mode.

The system includes a hearing aid with a charging port that has two electrical contacts. The system also has a charger that is used to charge the hearing device, namely the energy store. The charger is suitable for this, in particular provided and set up. During operation, electrical energy is transferred to the hearing device by means of the charging device, in particular to an energy store of the hearing device. In summary, a charging device for a hearing device is understood to mean, in particular, a charging device for a hearing device, with the charging device not being part of the hearing device. The charging device and the hearing aid are separate units/components of the system from one another and can be removed from one another. When charging, on the other hand, the charger and the hearing aid work together.

In one embodiment, to effect the interaction, each mating contact is mechanically releasably connected to a respective associated contact, and the contacts and mating contacts are constructed of an electrically conductive material. In an alternative to this, the contacts and the mating contacts are each electrically contacted with a coil, preferably via other components. In particular, the mating contacts are in contact with the assigned coil via an inverter, and the contacts are connected via a rectifier. The contacts are expediently also electrically connected to a capacitance. To produce the interaction, the two coils are brought closer to each other, and the inverter is operated in particular in such a way that an electrical AC voltage is applied to the associated coil.

The hearing aid is operated according to a method in which a drop in an electrical voltage present at the two contacts is detected. An operating mode of the hearing aid is set depending on the course of the decrease over time.

The two counter-contacts of the charging device are particularly preferably connected by means of a capacitance, by means of which the inverter, if any, is expediently fed. Preferably, in this case, the inverter is also using operated with the voltage applied to the capacitance, so that wiring is simplified. The capacitance is particularly preferably a capacitor or has at least one capacitor.

Due to the capacity, the inverter will continue to be operated for an extended period of time if there is a change in the current supply to the charger, so that the electrical voltage at the contacts will drop comparatively slowly. On the other hand, when the hearing device is removed from the charging device, the electrical voltage continues to drop comparatively quickly. Because of the capacitance, the dependency of the course of the sinking on the type of termination of the interaction between the charging device and the hearing aid is increased.

The developments and advantages explained in connection with the method can also be transferred to the hearing device/the system and to each other and vice versa.

Fig. 1

schematisch vereinfacht ein System mit einem Hörgerät und einem Ladegerät,

Fig. 2

ein Verfahren zum Betrieb des Hörgeräts, und

Fig. 3, 4

unterschiedliche zeitliche Verläufe einer an zwei elektrischen Kontakten des Hörgeräts anliegenden elektrischen Spannung.

An exemplary embodiment of the invention is explained in more detail below with reference to a drawing. Show in it:

1

schematically simplified a system with a hearing aid and a charger,

2

a method of operating the hearing aid, and

Figures 3, 4

different time curves of an electrical voltage applied to two electrical contacts of the hearing aid.

Corresponding parts are provided with the same reference symbols in all figures.

In 1 a system 2 is shown with a hearing device 4 in the form of a hearing aid device, which is provided and set up to be worn behind an ear of a user (user, hearing device wearer, wearer). In other words, it is a behind-the-ear hearing aid device. The hearing aid 4 includes a hearing aid housing 6, which consists of an injection molding process is made of a plastic. A microphone 8 is arranged inside the hearing device housing 6 . The microphone 8 is coupled in terms of signaling to electronics 10, which includes a signal processing unit (not shown in detail) with an amplifier circuit and a signal processor. The electronics 10 are formed by means of circuit elements, such as electrical and/or electronic components. The signal processor is a digital signal processor (DSP) and is connected in terms of signals to the microphone 8 via an A/D converter that is not shown in detail.

With the electronics 10, a receiver 12 is coupled in terms of signaling. During operation, the earphone 12 is used to convert an (electrical) signal provided by the electronics 10 into an output sound, ie into sound waves. These are introduced into a sound tube, not shown in detail, one end of which is attached to the hearing aid housing 6 . The other end of the sound tube is enclosed by a dome, which is arranged in the user's auditory canal in the intended state. The electronics 10 , the microphone 8 and the receiver 12 are energized by means of an energy store in the form of a battery 14 which is arranged in the hearing aid housing 6 .

The hearing aid 4 also includes a charging circuit 16 which is electrically connected to the battery 14 and which is used to charge the battery 14 . For this purpose, the charging circuit 16 includes a control unit, not shown in detail, by means of which the voltage applied to the battery 14 is adjusted. In addition, the charging circuit 16 includes a charging connection 18 which has two contacts 20 . The contacts 20 are connected to the battery 14 via the control unit, which is not shown in detail. The electrical voltage present at the contacts 20 is detected by means of an A/D converter 21 and the control unit is operated as a function of this. The two contacts 20 are electrically connected to one another by means of a capacitor 22 and led to a rectifier 24, namely a diode rectifier. This is connected to an electrical coil 26, which is also simply referred to as a coil, and fed via it.

The system 2 also includes a charging device 28 which has two mating contacts 28 . The mating contacts 28 are connected to a further rectifier 30 and fed by it. The additional rectifier 30 is in turn fed via a plug 32, which is used to electrically contact the charging device 28 with a supply network, by means of which an electrical direct voltage, for example at 230 V or 110 V, is conducted. The two mating contacts 28 are led to an inverter 34, by means of which a coil 36 of the charger 28 is fed. In addition, the two mating contacts 28 are electrically connected to one another by means of a capacitor 38 . In this case, the capacity 38 is a capacitor.

To charge the hearing aid 4, namely the battery 14, the plug 32 is electrically connected to the supply network and as a result the capacitance 36 is charged via the further rectifier 30. The inverter 34 is operated by means of the capacitance 38 and consequently an electrical AC voltage is applied to the coil 36 of the charging device 28 . This is placed in the immediate vicinity of the charging connection 18, namely the coil 26, so that an electrical AC voltage is induced in it. This is rectified by means of the rectifier 24 and smoothed by means of the capacitor 22 so that an essentially constant electrical (direct) voltage is present at the contacts 20 . This is detected by means of the A/D converter 21 and the control unit is set as a function of this, so that the battery 14 is charged.

Furthermore, the hearing aid 4 according to an in figure 2 Method 40 illustrated operated, which is at least partially executed by means of the electronics 10. In a first step 42, a drop in the electrical voltage 44 applied to the two contacts 20 is detected, the course of which over time is shown in FIG figure 3 is shown as an example. In this case, the applied electrical voltage 44 is detected by means of the A/D converter 21 and the generated (digital) signals are sent to the electronics 10, by means of which the signals are evaluated. If the electrical voltage 44 falls below a third limit value 46, which corresponds to 80% of the electrical voltage 44 that is required when charging the battery 14 or that is usually present, the fall is detected. In other words, will too the applied electrical voltage 44 is monitored during charging by means of the A/D converter 21 and the electronics 10 .

In a subsequent second work step 48, a time profile 50 of the drop in electrical voltage 44 is determined. In one embodiment, a time derivative 52 of the electrical voltage 44 is created for this purpose. In an alternative, to determine the time profile 50 , the electrical voltage 44 is recorded at two different points in time 54 after the decrease was recorded, the first of the points in time 54 coinciding with the point in time at which the electrical voltage 44 differs from the third limit value 46 . The second of the points in time 54 is in a fixed period of time 56 after the first of the two points in time 54.

In a subsequent third work step 58, an operating mode 60 of the hearing device 4 is set as a function of the progression over time 50 of the drop. If the electrical voltage 44 falls faster than a second limit value 62, a working mode is used as the operating mode 60. The second limit value 62 is exceeded here if the user manually moves the hearing device 4 away from the charging device 28 . In this case, the user usually wants to use the hearing device 4 afterwards. When switching to the working mode, the electronics 10, namely the signal processing unit, the amplifier circuit and the signal processor, are switched to an operating mode in which there is an increased energy requirement. Any settings stored in software or a memory are also loaded, so that the hearing device 4 is ready for use when the user puts it on the body.

When the hearing aid 4 is removed from the charging device 28, the coil 36 of the charging device 28 is first applied to the electrical AC voltage by means of the inverter 34, so that the electrical field is created around it. However, less electrical voltage is induced in the coil 26 of the hearing aid 4 due to the increasing distance. As a result, the electrical voltage 44 present at the contacts 20 drops to 0 V. Since the hearing aid 4 is removed from the charging device 28 comparatively abruptly is, the interaction between them is also terminated comparatively abruptly. In other words, the energy transfer between the charging device 28 and the hearing device 4 is terminated abruptly.

In one variant, a specific value for the derivation 52 is used as the second limit value 62; figure 3 example shown is exceeded by derivative 52. In other words, second limit value 62 is exceeded when derivative 52 is greater than second limit value 62 and electrical voltage 44 thus drops to 0 V comparatively quickly. If the time curve 50 is determined using the electrical voltage 44 detected at the two points in time 54, the second limit value 62 is exceeded if the difference between the two electrical voltages 44 detected is greater than a specific value corresponding thereto.

If, on the other hand, the plug 32 is removed from the supply network and the position of the two tracks 26, 36 relative to one another is not changed, the capacitor 38 is no longer fed via the further rectifier 30. However, due to the electrical voltage still present at the capacitor 38 and the electrical energy thus stored, the inverter 34 continues to be operated for a longer period of time. As a result, energy continues to be transferred from the charging device 28 to the hearing aid 4, but the electrical voltage induced in the coil 26 slowly decreases, so that the electrical voltage 44 present at the contacts 20 also falls comparatively slowly.

As a result, as in figure 4 shown, the derivative 52 below the second limit value 62, which is chosen to be equal to a first limit value 64. In other words, the two limit values 62, 64 are the same. The difference in the electrical voltage 44 detected at the points in time is also greater than the corresponding specific value. In this case, a stand-by operating mode is selected as the operating mode 60 . In summary, the stand-by operating mode is selected when the electrical voltage 44 falls more slowly than the first limit value 64 . In the stand-by operating mode, the electronics 10, if this is still is not the case, operated in an operating mode in which an energy requirement is reduced. For this purpose, for example, the amplifier circuit, the signal processing circuit and/or the signal processor are switched off completely. The control unit is also switched off. As a result, the energy requirement of the hearing aid 4 is reduced and it can be stored over a comparatively long period of time. If the user wants to use the hearing aid 4, it is necessary to put it into the working mode, which is done by means of a corresponding input, in particular by actuating a switch.

The invention is not limited to the embodiment described above. On the contrary, other variants of the invention can also be derived from this by a person skilled in the art without departing from the subject matter of the invention. In particular, all of the individual features described in connection with the exemplary embodiment can also be combined with one another in other ways without departing from the subject matter of the invention.

Reference List

2

system

4

hearing aid

6

hearing aid housing

8th

microphone

10

electronics

12

listener

14

battery

16

charging circuit

18

charging port

20

Contact

21

A/D converter

22

capacitor

24

rectifier

26

Kitchen sink

28

mating contact

30

another rectifier

32

Plug

34

inverter

36

Charger coil

38

capacity

40

Proceedings

42

first step

44

electrical voltage

46

third limit

48

second step

50

time course

52

derivation

54

time

56

Period of time

58

third step

60

operation mode

62

second limit

64

first limit

Claims (9)

Method (40) for operating a hearing aid (4), which has a charging connection (18) with two electrical contacts (20), in which - A drop in an electrical voltage (44) present at the two contacts (20) is detected, and - An operating mode (60) of the hearing aid (4) is set as a function of the progression over time (50) of the drop. Method (40) according to claim 1,
characterized,
that the electrical voltage (44) is detected only at two different points in time (54) to determine the time profile (50). Method (40) according to claim 1,
characterized,
that a time derivative (52) of the electrical voltage (44) is created to determine the time profile (50). Method (40) according to any one of claims 1 to 3,
characterized,
that a stand-by operating mode is selected when the electrical voltage (44) drops more slowly than a first limit value (64). Method (40) according to any one of claims 1 to 4,
characterized,
that a working mode is selected when the electrical voltage (44) drops faster than a second limit value (62). Method (40) according to any one of claims 1 to 5,
characterized,
that the drop is detected when the electrical voltage (44) present at the two contacts (20) falls below a third limit value (46). Hearing aid (4), which has a charging connection (16) with two electrical contacts (20), and which is operated according to a method (40) according to any one of claims 1 to 6. Hearing aid (4) according to claim 7,
marked by
an A/D converter (21) for determining the time course (50) of the fall. System (2) with a charging device (28) which has two electrical counter-contacts (28) which are electrically connected by means of a capacitor (36), and with a hearing aid (4) according to claim 7 or 8.

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