Method for operating a hearing aid

Abstract

The invention relates to a method (40) for operating a hearing aid (4) having a charging contact (18) with two electrical contacts (20). Here, a drop in the voltage (44) present at the two contacts (20) is detected. Depending on the time course (50) of the drop, an operating mode (60) of the hearing aid (4) is set. The invention also relates to a hearing aid (4) and to a system (2) having a hearing aid (4) and a charging device (28).

Description

TECHNICAL FIELD

[0001] The invention relates to a method for operating a hearing aid. Furthermore, the invention relates to a hearing aid and a system having a hearing aid and a charging device. The hearing aid comprises a charging connection having two electrical contacts. BACKGROUND

[0002] People with reduced hearing capacity usually use a hearing aid. Here, environmental sound is usually detected by means of an electromechanical sound transducer. The electrical signal created from the environmental sound is amplified by means of an amplifier circuit and introduced into the ear canal of the person by means of a further electromechanical transducer in the form of an earpiece. Furthermore, the detected sound signal is usually processed for which a signal processor of the amplifier circuit is usually used. Here, the amplification is coordinated with the possible hearing loss of the hearing aid wearer.

[0003] For the operation of the transducer and the amplifier circuit, electrical energy is required. The electrical energy is usually provided in the form of a battery which is arranged in the housing of the hearing aid. Thus, the person using the hearing aid, i.e. the hearing aid wearer, is provided with freedom of movement. If the battery is empty, it has to be replaced. For this purpose, the housing usually has a cover plate by means of which the battery can be reached.

[0004] A disadvantage here is that due to the lack of sealing, foreign particles or moisture can penetrate into the housing and thus possibly damage the components of the hearing aid arranged there, for example the amplifier circuit. Therefore, a comparatively comprehensive sealing is required. Here, due to the comparatively small space provided, the design and production costs are increased. Due to the comparatively small size of the cover plate, further aids are usually required for the operation and a human error cannot be ruled out.

[0005] Therefore, an alternative provides for the use of rechargeable batteries. If the battery is empty, it only has to be recharged to provide further capacity for action, without having to be removed. Thus, it is possible to design the housing essentially sealingly and the operation is simplified. For the charging, the hearing aid usually has a charging connection with two electrical contacts. These two electrical contacts interact with two mating contacts of the charging device. Here, for example, the mating contacts are in direct mechanical contact with the contacts, wherein the mating contacts are separated from the contacts after the end of the charging. As an alternative thereto, the contacts and the mating contacts interact with one another by means of electrical coils, whereby the energy exchange between the hearing aid and the charging device takes place inductively. The charging device itself is usually connected to the power supply network by means of a plug. From the voltage provided by means of the power supply network, a voltage is generated which exists between the mating contacts and which is used to charge the hearing aid.

[0006] When the hearing aid has been charged, the user usually takes it out of the charging device to be used immediately. In order to increase the comfort of the user, the hearing aid is already placed in the operating mode when it is separated from the charging device. The separation from the charging device is usually detected according to a drop in the voltage present at the contacts, which is interrupted in the interaction of the mating contacts when removed from the charging device. However, it is also possible that the plug of the charging device is separated from the power supply network. As a result, the voltage present at the mating contacts drops and thus also the voltage present at the contacts. In this case, however, the hearing aid should usually not be used, but should be operated in a way that is as energy-saving as possible until it is actually used. In order to prevent the hearing aid from being placed in the operating mode, it is necessary to additionally determine whether the hearing aid is still connected to the charging device in the event of a drop in the voltage present at the contacts. For this purpose, a third contact is used, for example, or a sensor, such as a Hall sensor, is present, by means of which the electric field generated by the mating contacts is detected. However, additional components are thus present, which is why the production costs increase. SUMMARY

[0007] The technical problem addressed by the present application is to provide a particularly suitable method for operating a hearing aid and a particularly suitable hearing aid and a particularly suitable system having a hearing aid and a charging device, wherein, inter alia, the comfort is increased and / or the production costs are reduced.

[0008] The above-mentioned technical problem is solved according to the present application by the features of the application with respect to the method, by the features of the application with respect to the hearing aid and by the features of the application with respect to the system. Advantageous further developments and design solutions are the subject matter of the respective embodiments.

[0009] The method is for operating a hearing aid. The hearing aid is, for example, an earpiece or comprises an earpiece. However, the hearing aid is particularly preferably a hearing assistance device. The hearing assistance device is used to support a person with reduced hearing ability. In other words, the hearing assistance device is a medical device by means of which, for example, a partial hearing loss is compensated. The hearing assistance device is, for example, a "Receiver-in-the-canal" hearing assistance device (RIC; external earpiece hearing assistance device), an in-the-ear hearing assistance device (for example, an "in-the-ear" hearing assistance device), an "in-the-canal" hearing assistance device (ITC) or a "complete-in-canal" hearing assistance device (CIC), a glasses hearing aid, a pocket hearing assistance device, a bone conduction hearing assistance device or an implant. Alternatively, the hearing assistance device is a behind-the-ear hearing assistance device ("Behind-the-Ear" hearing assistance device) which is worn behind the pinna.

[0010] The hearing aid is arranged and designed to be worn on the human body. In other words, the hearing aid preferably comprises a holding device by means of which it can be fixed at the human body. Alternatively or in combination therewith, the hearing aid is suitably shaped. If the hearing aid is a hearing assistance device, the hearing aid is arranged and designed to be arranged, for example, behind the ear or in the ear canal. The hearing aid is in particular wireless and is arranged and designed to be introduced at least partially into the ear canal.

[0011] The hearing aid preferably has a hearing aid housing. In the hearing aid housing, preferably substantially all other components of the hearing aid are arranged, at least preferably possible electronics such as an amplifier circuit. The hearing aid housing is made, for example, in one piece or particularly preferably from a plurality of component parts. The hearing aid housing is suitably made from plastic, in particular in a plastic injection molding process. Thus, the degree of freedom of design is relatively large. The weight of the hearing aid housing is also not excessively increased.

[0012] In the hearing aid housing, for example, a microphone, i.e. in particular an electromechanical sound transducer, is arranged. The microphone serves to detect environmental sound and is suitable, in particular arranged and designed, for this purpose. The microphone is in particular electrically and / or in a signal-technical manner connected with possible electronics, in particular an amplifier circuit, or with other electrical / electronic components of the hearing aid. The signals detected by means of the microphone are suitably processed by means of the electronics.

[0013] The hearing aid particularly preferably comprises a further electromechanical sound transducer, in particular an earpiece, by means of which the signals processed by means of the possible amplifier circuit are output. The earpiece is also arranged, for example, in the hearing aid housing or in a further housing. Here, the two housings are connected in a signal-technical manner, for example, by means of a line, in particular if the hearing aid is an RIC hearing assistance device.

[0014] The hearing aid comprises a charging connection, wherein electrical energy can be fed into the hearing aid by means of the charging connection. To this end, the charging connection has two electrical contacts, which are also referred to in the following simply as contacts. In the case of a charging of the hearing aid, there is a voltage at the charging device when electrical energy is fed or at least when interaction with the charging device takes place. The charging device serves for charging the hearing aid, i.e. for providing the hearing aid with electrical energy. The charging device is suitable, in particular arranged and designed, for this purpose.

[0015] The charging contacts are designed, for example, mechanically, and the two electrical contacts are formed, for example, by means of Pogo-Pins, mechanical plugs or conductive plates, or at least comprise Pogo-Pins, mechanical plugs or conductive plates, respectively. The electrical contacts are introduced, for example, directly into possible walls of the hearing aid housing or are located in receptacles covered, for example, by means of a cover plate. As an alternative thereto, the two electrical contacts are in contact with an electrical coil, and the charging takes place in a wireless manner. Suitably, a rectifier, for example a diode rectifier, is arranged between the electrical contacts and the (electrical) coil, so that a direct voltage is present at the electrical contacts if the hearing aid interacts with the charging device. A capacitor or other capacitance is particularly preferably connected between the contacts, by means of which the voltage is stabilized. Thus, the voltage present at the electrical contacts is essentially constant in the case of constant interaction with the charging device.

[0016] The charging device preferably has two mating contacts. If the charging takes place mechanically, for example by means of a cable, either of the mating contacts is in direct mechanical abutment at the respectively associated contact, respectively. If the charging takes place, for example, in an inductive manner, the mating contacts are in particular in electrical contact with the coil, preferably via an inverter. Suitably, a direct voltage is present at the mating contacts.

[0017] The hearing aid preferably comprises an energy store, by means of which the energy supply is provided. The energy store is suitably used to energize possible electronics / sound transducers. The energy store is suitably arranged within a possible hearing aid housing. The energy store is suitably rechargeable and is preferably a rechargeable battery. The energy store is in contact, in particular directly or via a possible charging circuit, with the two electrical contacts. The charging circuit preferably comprises a voltmeter, which is designed, for example, as an analog-digital converter or at least comprises an analog-digital converter. The charging of the energy store by means of the charging contacts is regulated or at least controlled, in particular by means of the charging circuit. In this way, the number of possible charging cycles can be increased.

[0018] The method provides that a drop in the voltage present at the two contacts is detected. The voltage present at the electrical contacts is suitably a direct voltage. Suitably, a voltage is present at the two contacts as a result of the interaction with the charging device. As a result of the interaction, the charging of the hearing aid, for example, takes place here. In order to provide the interaction, as a result of which the voltage is present which is applied to the two contacts, the hearing aid (suitably the charging contacts) is abutted against the charging device, in particular if the charging takes place in a wireless manner. As an alternative thereto, in particular a mating plug or the like is inserted into the charging contacts, so that the corresponding mating contacts are in direct mechanical abutment at the contacts of the charging contacts.

[0019] After the voltage is present at the two contacts, i.e. between the two contacts, a voltage drop is detected. Here, in particular the amplitude of the voltage present is reduced, in particular if an alternating voltage is present at the two contacts. However, particularly preferably, a direct voltage is present at the two contacts and the magnitude of the voltage decreases with the drop.

[0020] In a further working step, the time course of the voltage drop is detected and on the basis of this the operating mode of the hearing aid is set. Here, in particular one of a plurality of operating modes of the hearing aid is selected, after which the hearing aid is operated in accordance with the selected and set operating mode. For this purpose, in particular certain components of the hearing aid are energized in different ways.

[0021] When the interaction between the charging device and the hearing aid ends, in particular because the hearing aid is removed from the charging device, this happens comparatively abruptly, so that the voltage present at the two contacts drops relatively quickly. Conversely, when the charging device is separated from the possible power supply network or at least the energization of the charging device ends, the operation of the charging device is still partially maintained for a short period of time due to the inductance and / or capacitance present in the charging device, but wherein the amount of energy exchanged between the charging device and the hearing aid is reduced. As a result, the voltage present at the two contacts drops in another way. Since the operating mode of the hearing aid is set in accordance with the time course of the drop, this operating mode is set in accordance with how the interaction ends. Thus, depending on whether the hearing aid is separated from the charging device or the energization of the charging device itself ends, the hearing aid is then operated in different ways. Due to this method, the needs of the hearing aid user are thus taken into account, increasing the comfort. However, no additional components such as sensors are required here, which is why the production costs are reduced.

[0022] For example, in order to determine the time course, the voltage is detected only at two different points in time. Here, for example, a time interval between the two points in time is predefined and the voltage is detected at the two different points in time. From the magnitude of the difference of the voltage at the two points in time, the respective time course is inferred. In an alternative to this, for example, a value of the voltage is predefined and the time course is determined from the time interval between the points in time at which the voltage corresponds to the predefined value. Since in both variants only two measurements are made or at least the time course is determined from only two different values, the complexity and thus also the computational effort is reduced. Thus, the method is relatively resource-friendly and can be performed even in the case of a low-performance hearing aid.

[0023] In an alternative, for determining the time course, the voltage is detected over a relatively long period of time and an analysis is performed. For example, a Fourier analysis is performed on the voltage. Particularly preferably, however, for determining the time course, a time derivative of the voltage is created. The derivative is preferably used as the time course. For example, if the derivative has a defined maximum, a defined minimum and / or a defined average, a defined operating mode is used, and conversely, in the case of further minimums / maximums / averages, a different operating mode is used. Due to the use of the derivative, the accuracy is improved, and for example relatively short-term fluctuations or other disturbances do not lead to a change in the operation of the hearing aid.

[0024] When the voltage drops slower than a first boundary value, a stand-by operating mode is particularly preferably selected. Here, for example, the difference between the voltage detected at two different points in time is less than a certain value, by means of which the first boundary value is defined, the two different points in time being separated from one another by a certain time interval. As an alternative to this, the first boundary value is determined from the derivative, and this derivative is suitably less than a further boundary value. In the stand-by operating mode, for example, individual components or all components of the hearing aid are switched off, or one or some of the components are operated with a relatively low energy requirement, wherein, for example, the functional range is limited. In the case of a slow drop in the voltage, the connection to the charging device or at least the interaction with the charging device continues to exist, so that it can be assumed that the charging device is no longer powered and only breaks down the residual voltage present. In this case, the user presumably does not directly follow up with the use of the hearing aid, and due to the stand-by operating mode, the energy requirement of the hearing aid is reduced. Thus, when the user does subsequently want to use the hearing aid, this has a relatively high state of charge. If the hearing aid was already in the stand-by mode when it was being charged, it is suitably left as it is.

[0025] As an alternative to this or particularly preferably in combination with this, when the voltage drops faster than a second boundary value, an operating mode is selected. For example, in this case, the difference between the voltage detected at two different points in time is greater than a certain boundary value, the two different points in time being separated from one another by a constant time interval, or the derivative, in particular the minimum, the maximum or the average, is greater than a further boundary value. When the hearing aid is placed in the operating mode, some of the hitherto unpowered components of the hearing aid are preferably powered. In particular, the control device or other circuits, in particular microprocessors, are placed from the stand-by operating mode into the operating mode. In the case of a rapid drop, the interaction of the hearing aid with the charging device ends comparatively abruptly, so that it can be assumed that the hearing aid has been mechanically removed from the charging device. In this case, the user mostly wishes to use the hearing aid immediately, and due to this method, no additional operation is required for this. If the hearing aid is already in the operating mode, the operating mode is in particular not changed.

[0026] It is particularly preferred that the first boundary value is chosen to be equal to the second boundary value, so that depending on the time course of the drop only one of the two operating modes is selected respectively. The complexity is thus reduced and the user is provided with an understandable operation.

[0027] For example, a drop is detected when the amount of electrical energy fed into the energy store is below a certain value. Preferably, however, a drop is detected when the voltage present at the two contacts is below a third boundary value. The third boundary value is suitably relatively large and is for example between 95% and 75%, 90% or 70% or between 85% and 80% of the voltage present at the electrical contacts during the charging process. Due to such a third boundary value, fluctuations in the interaction of the charging device with the hearing aid do not affect the charging process of the hearing aid, on the contrary, the respective operating mode of the hearing aid is already selected when the hearing aid is relatively early detached from the charging device or the energization of the charging device ends. For this method only the voltage needs to be determined, so that the hardware requirements are reduced.

[0028] The hearing aid has a charging terminal with two electrical contacts. The charging terminal is for example designed as an inductive charging terminal or as a wired charging terminal. The electrical contacts are here in particular respectively adapted accordingly and a direct voltage is suitably present at the electrical contacts respectively independently of the respective design of the charging terminal when the hearing aid is charging or at least interacting with the charging device. The hearing aid is operated according to the method in which a drop in the voltage present at the two contacts is detected. The operating mode of the hearing aid is then set depending on the time course of the drop.

[0029] The hearing aid in particular comprises a control unit which is suitable for, in particular set up and designed for, carrying out the method. The control unit is for example formed by means of electronics which suitably also comprises a signal processor. The hearing aid suitably comprises an energy store such as a battery which can be charged in particular by means of the charging terminal. To this end, the energy store is for example electrically connected to the charging terminal directly or particularly preferably by means of a charging circuit. The charging terminal is in particular a component of the charging circuit.

[0030] It is particularly preferred that an analog-digital converter is used for determining the time course. Suitably, the analog-digital converter is additionally also used for evaluating the voltage present at the electrical contacts and in particular the start of the voltage drop is detected by means of the analog-digital converter. It is particularly preferred that the possible charging circuit is operated by means of the analog-digital converter. The analog-digital converter thus fulfils different tasks. A corresponding analog-digital converter is already present in some hearing aids, so that in particular no additional hardware requirements arise. The manufacturing costs are thus not increased.

[0031] It is particularly preferred that the (digital) signal created by means of the analog-digital converter is evaluated by means of electronics of the hearing aid, for example by means of a comparator. For this purpose, inter alia, a signal processor is used which, for example, processes the (acoustic) output signal by other means, preferably if the hearing aid is not being charged and / or if the hearing aid is in the operating mode.

[0032] The system comprises a hearing aid with a charging connection having two electrical contacts. The system also has a charging device for charging the hearing aid, i.e. the energy store. The charging device is suitable, in particular designed and constructed, for this purpose. In operation, electrical energy is transferred to the hearing aid, in particular to the energy store of the hearing aid, by means of the charging device. In general, the charging device of the hearing aid is understood in particular as a charging device for the hearing aid, wherein the charging device is not an integral part of the hearing aid. Here, the charging device and the hearing aid are separate units / components of the system, which can be removed from one another. Conversely, the charging device and the hearing aid act together when charging.

[0033] In one embodiment, for establishing the interaction, each mating contact is mechanically detachably connected at the respectively associated contact, and the contacts and mating contacts are composed of an electrically conductive material. In an alternative to this, the contacts and mating contacts are preferably in electrical contact with the coils respectively by further components. In particular, the mating contacts are in contact with the associated coils by means of inverters, and the contacts are in contact by means of rectifiers. Suitably, the contacts are additionally in electrical connection with a capacitor. For establishing the interaction, the two coils are here next to one another, and the inverters are operated in particular such that an alternating voltage is applied to the associated coils.

[0034] The hearing aid is operated in accordance with a method in which a drop in the voltage present at the two contacts is detected. The operating mode of the hearing aid is set in dependence on the time course of the drop.

[0035] The two mating contacts of the charging device are particularly preferably connected by means of a capacitor, so that the possible inverters are suitably fed by means of this capacitor. Here, the inverters are preferably also operated by means of the voltage present at the capacitor, so that the connection is simplified. The capacitor is particularly preferably a capacitor or has at least one capacitor.

[0036] Due to the capacitor, in the case of a change in the energization of the charging device, the inverters are still operated for an extended period of time, so that the voltage drops at the contacts relatively slowly. Conversely, in the case of removal of the hearing aid from the charging device, the voltage continues to drop relatively quickly. Due to the capacitor, the course of the drop is increased in dependence on the type of end of the interaction between the charging device and the hearing aid.

[0037] The extension design and advantages set forth in connection with the method can also be transferred analogously to the hearing aids / systems and among each other and vice versa. BRIEF DESCRIPTION OF DRAWINGS

[0038] Embodiments of the application are explained below in more detail according to the drawings. Herein in the drawings:

[0039] Figure 1 A system with a hearing aid and a charging device is schematically and simplified shown,

[0040] Figure 2 A method for operating a hearing aid is shown, and

[0041] Figure 3 , Figure 4 Different time courses of the voltage present at the two electrical contacts of the hearing aid are shown.

[0042] Corresponding components are provided with the same reference signs in all the figures. DETAILED DESCRIPTION

[0043] In Figure 1 A system 2 with a hearing aid 4 in the form of a hearing assistance device is shown in Fig. 1, which is arranged and designed to be worn behind the ear of a user (wearer, hearing aid wearer, wearer). In other words, the hearing assistance device is a behind-the-ear hearing assistance device. The hearing aid 4 comprises a hearing aid housing 6, which is made of plastic by means of an injection molding process. A microphone 8 is arranged within the hearing aid housing 6. The microphone 8 is coupled in a signal-technical manner with electronics 10, which comprise a not shown signal processing unit with an amplifier circuit and a signal processor. The electronics 10 are formed by means of circuit elements, for example electrical and / or electronic components. The signal processor is a digital signal processor (DSP) and is connected in a signal-technical manner with the microphone 8 by means of a not shown analog-digital converter.

[0044] A receiver 12 is coupled in a signal-technical manner with the electronics 10. In operation, the (electrical) signals provided by means of the electronics 10 are converted into an output sound, i.e. into sound waves, by means of the receiver 12. The sound waves are introduced into a not shown sound hose, one end of which is fixed at the hearing aid housing 6. The other end of the sound hose is surrounded by means of a dome, which is arranged in the ear canal of the user in the normal state. The energization of the electronics 10, the microphone 8 and the receiver 12 takes place by means of an energy store in the form of a battery 14, which is arranged in the hearing aid housing 6.

[0045] The hearing aid 4 further comprises a charging circuit 16, which is electrically connected to the battery 14 and serves for charging the battery 14. To this end, the charging circuit 16 comprises a regulating unit, not shown in detail, by means of which the voltage present at the battery 14 is regulated. Furthermore, the charging circuit 16 comprises a charging contact 18 with two contacts 20. The contacts 20 are connected to the battery 14 by means of a regulating unit, not shown in detail. The voltage present at the contacts 20 is detected by means of an analog-digital converter 21, and the regulating unit is operated in accordance therewith. The two contacts 20 are electrically connected to one another by means of a capacitor 22 and lead to a rectifier 24, i.e. a diode rectifier. The diode rectifier is connected to and fed by an electric coil 26, also referred to simply as coil.

[0046] The system 2 further comprises a charging device 28 with two mating contacts 28. The mating contacts 28 are connected to and fed by a further rectifier 30. The further rectifier 30 in turn is fed by a plug 32, which serves for electrically contacting the charging device 28 to a power supply network, by means of which a direct voltage of, for example, 230 V or 110 V is guided. The two mating contacts 28 lead to an inverter 34, by means of which a coil 36 of the charging device 28 is fed. Furthermore, the two mating contacts 28 are electrically connected to one another by means of a capacitor 38. The capacitor 38 is a capacitor here.

[0047] In order to charge the hearing aid 4, i.e. the battery 14, the plug 32 is electrically contacted to the power supply network, as a result of which the capacitor 36 is charged by means of the further rectifier 30. The inverter 34 is operated by means of the capacitor 38, and as a result an alternating voltage is applied at the coil 36 of the charging device 28. The coil is placed directly adjacent to the charging contact 18, i.e. the coil 26, so that an alternating voltage is induced therein. The alternating voltage is rectified by means of the rectifier 24 and smoothed by means of the capacitor 22, so that an essentially constant (direct) voltage is present at the contacts 20. The (direct) voltage is detected by means of the analog-digital converter 21, and in accordance therewith the regulating unit is set such that the battery 14 is charged.

[0048] Furthermore, the hearing aid 4 is operated in accordance with a method 40 shown in Figure 2 , which is implemented at least partially by means of the electronics 10. In a first working step 42, a drop in the voltage 44 present at the two contacts 20 is detected, the temporal course of which is shown in Figure 3is detected. In other words, the voltage 44 present is also monitored during charging by means of the analog-digital converter 21 and the electronics 10.

[0049] In a subsequent second work step 48, the time profile 50 of the drop in voltage 44 is determined. To this end, in one embodiment, a time derivative 52 of the voltage 44 is created. In an alternative, to determine the time profile 50, the voltage 44 is detected at two different time points 54 after the drop has been detected, wherein the first of the time points 54 coincides with the time point at which the voltage 44 deviates from the third boundary value 46. The second of the time points 54 lies behind the first of the time points 54 at a fixed time interval 56.

[0050] In a subsequent third work step 58, the operating mode 60 of the hearing aid 4 is set in dependence on the time profile 50 of the drop. If the voltage 44 drops faster than a second boundary value 62, the work mode is used as the operating mode 60. The second boundary value 62 is exceeded if the user manually removes the hearing aid 4 from the charging device 28. In this case, the user usually wishes to use the hearing aid 4 subsequently. In the case of the work mode being set, the electronics 10, i.e. the signal processing unit, the amplifier circuit and the signal processor, are placed in an operating mode in which there is an increased energy requirement. Possible settings stored in software or memory are also loaded, so that the hearing aid 4 is ready for use when the user places it on the body.

[0051] When the hearing aid 4 is removed from the charging device 28, the application of the alternating voltage to the coil 36 of the charging device 28 by means of the inverter 34 also continues unchanged at first, so that an electric field is generated around the coil. However, due to the increased distance, less voltage is induced in the coil 26 of the hearing aid 4. As a result, the voltage 44 present at the contact 20 drops to 0 V. Since the hearing aid 4 is removed relatively suddenly from the charging device 28, the interaction between them also ends relatively suddenly. In other words, the energy transfer between the charging device 28 and the hearing aid 4 ends suddenly.

[0052] In this variant, a specific value in relation to the derivative 52 is used as the second boundary value 62, in which case the time profile 50 of the drop in voltage 44 is determined by means of the derivative 52. Figure 3In the example shown, the derivative 52 exceeds the particular value. In other words, the second boundary value 62 is exceeded when the derivative 52 is greater than the second boundary value 62 and thus the voltage 44 drops to 0 V relatively quickly. The second boundary value 62 is exceeded if, in accordance with the time progression 50 determined from the voltages 44 detected at the two time points 54, the difference between the two voltages 44 detected is greater than the particular value corresponding thereto.

[0053] In contrast, if the plug 32 is removed from the power supply network and the position of the two coils 26, 36 relative to one another does not change, the capacitor 38 is no longer fed by the further rectifier 30. However, the inverter 34 continues to operate for a longer period of time as a result of the voltage still present at the capacitor 38 and the electrical energy stored thereby. As a result, the energy transfer from the charging device 28 to the hearing aid 4 continues, but in which the voltage induced in the coil 26 drops relatively slowly, so that the voltage 44 present at the contact 20 also drops relatively slowly.

[0054] As a result, as shown in Figure 4 the derivative 52 is below the second boundary value 62, which is selected to be equal to the first boundary value 64. In other words, the two boundary values 62, 64 are equal. The difference between the voltages 44 detected at the time points is also greater than the corresponding particular value. In this case, the standby operating mode is selected as the operating mode 60. In summary, the standby operating mode is selected when the voltage 44 drops slower than the first boundary value 64. In the standby operating mode, the electronics 10 are operated in an operating mode in which the energy requirement is reduced, if this is not already the case. To this end, for example, the amplifier circuit, the signal processing circuit and / or the signal processor are completely switched off. The regulating unit is also switched off. As a result, the energy requirement of the hearing aid 4 is reduced and the hearing aid can be stored for a relatively long period of time. If the user wants to use the hearing aid 4, he has to put it into the operating mode, which is done by means of a corresponding input, in particular by manipulating a switch.

[0055] The application is not limited to the embodiments described above. Rather, a person skilled in the art can derive further variants of the application therefrom without departing from the subject matter of the application. In particular, all individual features described in connection with the embodiments can also be combined with one another in other ways without departing from the subject matter of the application.

[0056] List of reference signs

[0057] 2 system

[0058] 4 hearing aid

[0059] 6 hearing aid housing

[0060] 8 microphone

[0061] 10 electronics

[0062] 12 earpiece

[0063] 14 battery

[0064] 16 charging circuit

[0065] 18 charging contact

[0066] 20 contact

[0067] 21 analog-digital converter

[0068] 22 capacitor

[0069] 24 rectifier

[0070] 26 coil

[0071] 28 mating contact

[0072] 30 further rectifier

[0073] 32 plug

[0074] 34 inverter

[0075] 36 coil of the charging device

[0076] 38 capacitance

[0077] 40 method

[0078] 42 first working step

[0079] 44 voltage

[0080] 46 third boundary value

[0081] 48 second working step

[0082] 50 time progression

[0083] 52 derivative

[0084] 54 time point

[0085] 56 time period

[0086] 58 third working step

[0087] 60 operating mode

[0088] 62 second boundary value

[0089] 64 first boundary value

Claims

1. A method (40) for operating a hearing aid (4), which has a charging contact (18) with two electrical contacts (20), in which method - a drop in the voltage (44) present at the two electrical contacts (20) is detected, and - different operating modes (60) of the hearing aid (4) are set in dependence on the time course (50) of the drop by - selecting one of the operating modes as a stand-by operating mode when the voltage (44) drops more slowly than a first boundary value (64) during a period in which the user is not using the hearing aid, and in which stand-by operating mode at least some components of the hearing aid are switched off, or at least one component of the hearing aid is operated in a functionally restricted manner with a lower energy requirement relative to the operating mode, and - selecting another one of the operating modes as an operating mode when the voltage (44) drops more quickly than a second boundary value (62) during a period in which the user is using the hearing aid, and in which operating mode components of the hearing aid which are not yet energized are energized, and these components are brought from the stand-by mode into the operating mode.

2. The method (40) as claimed in claim 1, characterized in that - in order to determine the time course (50), the voltage (44) is detected only at two different points in time (54).

3. The method (40) as claimed in claim 1, characterized in that - in order to determine the time course (50), a time derivative (52) of the voltage (44) is created.

4. The method (40) as claimed in any of claims 1 to 3, characterized in that - the drop is detected when the voltage (44) present at the two electrical contacts (20) falls below a third boundary value (46).

5. A hearing aid (4) which has a charging contact (18) with two electrical contacts (20), and which is operated in accordance with the method (40) as claimed in any of claims 1 to 4.

6. The hearing aid (4) according to claim 5, characterized in that - an analog-digital converter (21) for determining the time course (50) of the drop.

7. A system (2) with a charging device, which has two electrical mating contacts (28) which are electrically connected by means of a capacitor (36), and which has a hearing aid (4) as claimed in claim 5 or 6.

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