EP1289337B1 - Hearing aid to be worn in the ear or hearing aid with an otoplastic to be worn in the ear - Google Patents

Abstract

A hearing aid device to be worn in the ear or a hearing aid device with otoplastic to be worn in the ear, has at least two aeration channels in combination with flow resistances arranged in the aeration channels that promote a flow from the enclosed auditory canal volume toward the outside in at least one aeration channel and a flow into the enclosed auditory canal volume in at least one other aeration channel. A flow through the enclosed auditory canal volume results therefrom, so that an air exchange ensues. This improves the wearing comfort of the hearing aid device and contributes to the prevention of diseases caused by a poor ventilation of the auditory canal.

Description

In the practical application of hearing aids, the ear canal is in many cases closed by an earmold or by a hearing aid sitting in the auditory canal. In order nevertheless to ensure a certain ventilation of the enclosed auditory canal volume and to be able to counteract the acoustic effects associated with a closed auditory canal, usually a small ventilation channel, also referred to as ventilation opening or "vent" for short, is integrated into the otoplastic or the hearing aid worn in the ear.

The size of this ventilation duct, however, set limits on the acoustic side, as too many sound components leave the residual auditory canal volume through a large ventilation duct and can thus reach the microphone of the hearing aid. The consequence would be feedback-induced oscillations (feedback). Therefore, usually only a ventilation channel can be used with a relatively small cross-section.

So far, it has been subject to the hearing care professional, to integrate a adapted to the hearing damage and other individual conditions of a hearing aid wearer Vent in a hearing aid. However, due to the higher acoustic stability, predominantly relatively small ventilation openings were used, which is accompanied by insufficient ventilation of the enclosed auditory canal volume.

DE 199 42 707 A1 discloses a hearing aid device that can be worn in the ear or a hearing aid device with earmold that can be worn in the ear, in which a ventilation channel is present. In addition, in the known hearing aid means for throttling or closing the ventilation duct are present. The adjustment of these funds takes place when worn on the ear hearing aid by appropriate controls or by the signal processing unit of the hearing aid or by programming the hearing aid.

A disadvantage of the known hearing aids that can be worn in the ear or hearing aids with earmold that can be worn in the ear is the inadequate ventilation of the auditory canal in the usually small ventilation openings. This often leads to poor comfort or even inflammation in the ear canal.

The object of the invention is therefore to improve the ventilation of the ear canal in a hearing aid worn in the ear or a hearing aid with ear earmold portable.

This object is achieved in an ear hearing aid or a hearing aid with earmold earmold, comprising at least one input transducer for receiving an acoustic or electromagnetic input signal and conversion to an electrical signal, a signal processing unit for processing and amplifying the electrical signal, and a handset for conversion the electrical signal in an acoustic signal, solved by at least one first ventilation duct and at least one second ventilation duct for ventilation of the auditory canal volume enclosed by the hearing aid or the otoplastic, wherein the ventilation channels are each assigned means for favoring a flow direction through the ventilation duct, to favor the Outflow of air from the enclosed auditory canal volume at the first ventilation channel and for promoting the inflow of air into the enclosed auditory canal volume at the z wide ventilation duct.

Furthermore, the object is achieved by a method for operating a hearing aid device that can be worn in the ear or a hearing aid device with earmold that can be worn in the ear, wherein a drive signal has a frequency range that is inaudible to one another generated signal frequency and superimposed on the electrical signal and delivered via the handset into the ear canal for active ventilation of the ear canal.

The hearing aid according to the invention is e.g. an in-ear hearing aid (IdO), a behind-the-ear (BTE) or body-worn hearing aid connected to an earmold earmold, a wearable communication device, an ear-portable part of a communication system, e.g. an ear-earable headset for connection to a mobile phone, etc. In all of these devices, an ear canal occluding member is disposed in the ear canal. As a result, the natural ventilation of the ear canal is largely prevented.

The hearing aid according to the invention comprises an input transducer, for example a microphone, a hearing coil or an antenna, which receives an input signal and converts it into an electrical signal. The electrical signal is further processed in a signal processing unit and usually amplified with frequency-dependent gain. An earpiece converts the electrical signal processed in this way into an acoustic signal that is emitted into the auditory canal of a user.

In a hearing aid worn in the ear, the earpiece is arranged in the hearing aid and thus in the ear canal. Unlike a hearing aid with an earmold. Here, the earpiece can be located in the earmould, but also outside the ear canal, e.g. within a hearing aid device that can be worn behind the ear, in which case the sound conduction from the listener into the auditory canal takes place via a sound tube connected to the earmold.

Through the at least two ventilation channels in conjunction with arranged in the ventilation channels flow resistances, the flow in at least one ventilation channel of the Encapsulating the auditory canal volume to the outside and favoring a flow into the enclosed auditory canal volume in at least one other ventilation channel results in a total flow through the enclosed auditory canal volume, so that an air exchange takes place in the latter. This improves the wearing comfort of the hearing aid and helps to avoid diseases caused by poor ventilation of the ear canal.

The flow is driven, for example, by movements and associated volume changes of the ear canal, as they are caused by speaking or chewing.

According to a preferred variant of the invention, in addition to the useful signal, a further signal, the drive signal, is output via the receiver, which signal lies in a non-audible frequency range and is therefore not perceived by the user. In the interaction of the flow resistances in the ventilation channels with the listener, a diaphragm pump is thereby produced, which ensures an air flow through the enclosed auditory canal volume and thereby causes active ventilation of the enclosed auditory canal volume.

As means for generating the drive signal, a signal generator, for example a sine-wave generator, may be present. In this case, the ventilation effect caused by the listener improves with increasing amplitude of the drive signal, which is why the largest possible amplitude is preferred. In this way, a not caused by the useful signal, preferably low-frequency movement of the receiver membrane, which ensures a uniform inflow and outflow of air in the listener. During operation of the hearing aid device, however, care must be taken that the receiver membrane does not reach its full modulation due to the superimposition of the useful signal with the drive signal, thus producing audible artifacts.

In order to achieve a preferred passage direction of the ventilation ducts, a special structuring of the ventilation ducts comes into consideration. For example, a ventilation duct may narrow slowly and continuously in a forward direction and abruptly expand back to its original extent. In the second, preferably arranged in parallel ventilation duct, the same measure is taken, only here is the slow and continuous narrowing in the reverse direction. For example, with a relation to the external pressure increased pressure in the enclosed auditory canal volume then offers the sound channel, which narrows slowly and steadily outward, a lower flow resistance than the ventilation channel with the trapped volume facing, abrupt constriction. Thus, on the average through the first ventilation channel, an air flow to the outside and through the second ventilation channel an air flow inwards. Overall, this results in an air flow through the enclosed auditory canal volume and thus an exchange of air. The functionality is similar to that of a diaphragm pump.

For operating a hearing aid according to the invention, no special handset is required as a rule. In the case of the commonly used receivers, pressure equalization between the two air volumes separated from the diaphragm is not provided for the dynamic operating state. Any microbores for static pressure equalization that are located on the side of the diaphragm have no effect on dynamic operation.

In order to promote the flow in one direction through a ventilation duct, according to a variant of the invention, valves or flaps can also be arranged at an inlet of the ventilation duct or within the ventilation duct. Although valves or flaps require a higher mechanical effort to manufacture, but they ensure that the flow through the ventilation channel takes place almost exclusively in one direction.

Mechanically even more complex, but still more efficient are automatically operable valves or flaps. These valves or flaps are assigned electrical or magnetic miniature drives, which are preferably controlled directly with the drive signal for the listener. Thus, the valves or flaps are opened or closed in time with the drive signal, wherein the valves or flaps are opened in one ventilation duct, while closing the valves or flaps in the other ventilation duct.

Preferably, the miniature drives, but also the valves or flaps, at least partially made in microstructure technology. Such methods allow cost-effective production of almost any small miniature actuators in large quantities.

The drive signal for controlling the handset in a hearing aid according to the invention is preferably generated by means of a signal generator. For example, this can be a sine-wave generator. But there are also other drive signals, such as rectangular signals, into consideration. In order to be able to adapt the ventilation to the individual needs of a user, the amplitude and / or frequency of the drive signal can advantageously be set. The adjustment can be made for example by programming the hearing aid. This allows adjustment of the per unit of time approximately interchangeable air volume.

A particularly advantageous embodiment of the invention provides that the setting of the drive signal in dependence on characteristic values of the input signal or the electrical signal takes place. To achieve a good ventilation effect, the drive signal advantageously has a relatively high amplitude. It is superimposed on the useful signal and output via the handset. As a result, in particular with a useful signal having a relatively high amplitude, there is the risk of overloading the listener, whereby audible artifacts would be generated. By detecting the signal level of the input signal or the amplitude of the electrical signal, this can be prevented by reducing the amplitude of the drive signal in the case of an electrical signal having a high amplitude. Eventually, the drive signal can also be switched off completely in the case of an electrical signal with a particularly high amplitude. Furthermore, in a very quiet sound environment, the frequency and / or amplitude of the drive signal can be reduced in order to reduce or avoid any flow noises possibly caused by the active ventilation.

The setting of the drive signal depending on the selected hearing program is possible. For example, then the ventilation activity is throttled in the case of a hearing program for quiet environment.

In a particularly convenient embodiment of the invention, a sensor is provided for detecting at least one characteristic value of the auditory canal volume enclosed by the hearing aid device to be worn in the ear or the earmold that is portable in the ear. By means of this sensor, for example, the size of the enclosed auditory canal volume or the relative humidity in the enclosed auditory canal volume can be measured. The ventilation activity is then adjusted to the characteristic values measured in this way. Thus, e.g. be increased at a high relative humidity in the ear canal by increasing the frequency of the drive signal, the ventilation activity.

• Figur 1 ein im Ohr tragbares Hörhilfegerät mit einem Belüftungskanal nach dem Stand der Technik,
• Figur 2 ein im Ohr tragbares Hörhilfegerät mit zwei Belüftungskanälen,
• Figur 3 das Blockschaltbild des Hörhilfegerätes gemäß Figur 2,
• Figur 4 Klappen, die in zwei parallel angeordneten Belüftungskanälen angebracht sind, und
• Figur 5 schematisch eine aus einem Träger mit mehreren Durchlässen und Schwenkelementen zusammengesetzte Anordnung zum Öffnen und Schließen eines Belüftungskanals.

The invention will be explained in more detail with reference to embodiments. Show it:

• FIG. 1 shows a hearing aid device which can be worn in the ear and has a ventilation channel according to the prior art,
• FIG. 2 shows an ear hearing aid device with two ventilation channels,
• FIG. 3 shows the block diagram of the hearing aid according to FIG. 2,
• Figure 4 flaps, which are mounted in two parallel ventilation ducts, and
• Figure 5 schematically shows a composite of a carrier with multiple passages and pivot elements arrangement for opening and closing a ventilation duct.

FIG. 1 shows a schematic illustration of a hearing aid device 1 according to the prior art that can be worn in the ear. A microphone 2 records an acoustic signal and converts it into an electrical signal. The electrical signal is fed to a signal processing unit 3. In the signal processing unit 3, the electrical signal is processed and amplified in response to the signal frequency. The processed electrical signal is converted back into an acoustic signal via a receiver 4 and emitted into the auditory canal of a hearing device wearer. The electronic components of the hearing aid 1 are connected to the power supply to a battery 8.

For ventilation of the auditory canal volume enclosed by the hearing aid device 1 that is portable in the ear, the hearing aid device 1 is traversed by a ventilation channel 5. The ventilation duct represents a bypass to the electroacoustic signal path through the hearing aid device 1. In certain acoustic situations, eg with low acoustic amplification of the hearing aid device 1 due to a loud sound environment, this bypass is opposite the signal path through the hearing aid device 1 dominant. This can lead to certain functions of the hearing aid device 1, such as a desired directivity or a noise reduction, can only be performed limited. In addition, it can also come through the ventilation duct 5 to feedback between the handset 4 and the microphone 2. To avoid these disadvantages, the ventilation channel 5 is usually carried out only with a relatively small cross-section. However, this results in the disadvantage that only a small ventilation effect can be achieved in the enclosed auditory canal volume through the ventilation duct.

FIG. 2 shows, in a highly simplified and schematic representation, a hearing aid device 11 carried in the ear according to the invention, wherein essentially only the components relevant for the invention are shown. The hearing aid device 11 extends deep into the ear canal 12 of a hearing aid wearer, whereby an auditory canal volume 14 is enclosed between the hearing aid device 11 and the eardrum 13. By the hearing aid 11, the natural air circulation in the ear canal 12, which takes place by the heating of the air due to the body heat in a natural way, prevented. In order nevertheless to achieve ventilation of the enclosed auditory canal volume 14, two ventilation channels 15 and 16 are provided in the hearing aid device 11. The openings of the ventilation channels 15 and 16 directed to the inside of the auditory canal 12 are as far apart as possible in order to achieve the best possible ventilation of the entire enclosed auditory canal volume 14. Furthermore, the ventilation channels 15 and 16 are structured in the region of these openings. In the embodiment, the ventilation channels narrow steadily, then abruptly open again to their original width. This structuring creates a flow resistance which depends on the direction of flow of the air through the ventilation channel. In the direction of the slowly and steadily increasing rejuvenation, the air experiences a lower flow resistance than in the opposite direction. Volume changes of the enclosed auditory canal volume 14, which are caused for example by chewing or speaking, so in conjunction with the different flow resistances produce a pumping effect, which causes a flow through the enclosed auditory canal volume 14.

A simplified block diagram of the hearing aid according to FIG. 2 is shown in FIG. As usual with hearing aids, the hearing aid device 11 also comprises a microphone 2 'for receiving an acoustic input signal and converting it into an electrical signal, a signal processing unit 3' for processing and frequency-dependent amplification of the input signal, a receiver 18 for converting the processed electrical signal into an acoustic output signal and a battery 8 'for supplying power to the hearing aid device 11. According to a preferred variant of the invention, the hearing aid device 11 further comprises a signal generator 17. This generates a preferably sinusoidal signal with a frequency lying in the inaudible frequency range. For example, this is a signal with a signal frequency of 10 Hz and the largest possible amplitude. This signal is superimposed on the actual useful signal that is output by the handset 18. In this case, the signal generator 17 is designed so that it does not come to a full modulation of the receiver 18 even by the superposition of the desired signal with the drive signal. As a result of the drive signal, a receiver diaphragm arranged in the receiver 18 performs a uniform pumping movement. In this way arises in the enclosed auditory canal volume with respect to the outside air with the frequency of the drive signal changing positive or negative pressure. As can also be seen from FIG. 2, the structural elements 19 and 20 are oriented oppositely in the parallel ventilation channels 15 and 16, ie the structural element 19 in the ventilation channel 15 increasingly tapers in the direction of the outside of the auditory canal 12 and the structural element 20 tapers in the ventilation channel 16 increasingly towards the inside of the ear canal 12. Thus flows at an overpressure In the auditory canal volume 14 on average more air through the ventilation channel 15 from the inside to the outside than through the ventilation channel 16. To this end flows at a negative pressure in the enclosed auditory canal volume 14 on average more air through the ventilation duct 16 in the enclosed auditory canal volume 14 than through the ventilation channel 15. Overall As a result, as a result of the pumping movement of the receiver membrane of the receiver 18, a uniform flow of air through the enclosed auditory canal volume 14, which is indicated by the arrow 21.

Advantageously, the hearing aid device 11 according to FIG. 3 additionally comprises a sensor 10 directed into the enclosed auditory canal volume. By means of the sensor 10, the relative humidity in the enclosed auditory canal volume can be detected and fed to the signal generator 17. Frequency and amplitude of the control signal output by the signal generator 17 are then determined as a function of this sensor signal, with increasing frequency and / or amplitude of the drive signal are increased with increasing relative humidity.

The invention thus contributes to the fact that the natural air circulation through the ear canal 12 is not prevented even when worn in the ear hearing aid 11. This increases comfort and helps to prevent inflammation due to poor ventilation.

The arrangement and design of the ventilation channels 15 and 16 and of the structural elements 19 and 20 shown in FIG. 2 are to be understood as purely exemplary. Without departing from the scope of the invention, a plurality of possible variations is conceivable here. A further exemplary embodiment for this is shown in FIG. 4. Also in this embodiment, a hearing aid device 22, which is only partially shown, and which is arranged in the auditory canal 12, encloses an auditory canal volume 14. In contrast to Figure 2 are here, however the openings in the auditory canal into two ventilation channels 23 and 24 in the drawing only schematically shown flaps 25 and 26, which open at a pressure gradient in one direction and close at a pressure gradient in the opposite direction. By an opposite orientation of the flaps 25 and 26 in the ventilation channels 23 and 24, the flap assembly 25 is opened at a pressure gradient in the ear canal 12 from the inside out, while the flap assembly 26 closes. As a result, as indicated by the arrows 27, air can flow out through the ventilation channel 23 in this operating state, while no air exchange takes place through the ventilation channel 24. As a result of the further movement of the receiver membrane of the receiver 28 as a result of the activation signal, a negative pressure is created in the enclosed auditory canal volume 14 so that the flap arrangement 26 opens and air flows through the ventilation channel 24 into the enclosed auditory canal volume. In contrast, in this operating state, the flap assembly 25 is closed. Overall, thus results in the pumping movement of the membrane of the listener 28, the direction indicated by the arrow 29 air circulation.

In contrast to the structuring of the ventilation channels according to FIG. 2, the flap arrangement shown in FIG. 4 requires a higher manufacturing outlay. However, this ensures an air flow through the ventilation channels 23 and 24 in almost only one direction. This improves the air circulation.

Mechanically even more complex, but with a nearly perfect opening and closing action is the valve arrangement shown in Figure 5. Shown is a used in a ventilation duct 30, provided with passages 31 carrier 32, wherein a plurality of parallel valves 33 cause the opening or closing of the ventilation duct 30. In this case, inserted into the carrier 32 pivot elements 34 preferably complete opening or closing each one of a pivot member 34 associated passage 31. The carrier 32 is preferably made of a semiconductor material, in which the pivot elements 34 are introduced. The actuation of the pivot elements 34 takes place due to electromagnetic forces, wherein the control of the valves can be coupled directly to the drive signal for controlling the receiver diaphragm.

According to the invention, the valve arrangement shown in Figure 5 is preferably used in pairs in several ventilation channels, wherein the valves are controlled so that the valves close in a ventilation duct while they are open in the other ventilation duct. The operation then corresponds to that shown in Figure 4, only with a further improved opening and closing action against the flap assembly shown there.

Claims (16)

1. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, comprising at least one input transducer (2') for the pickup of an acoustic or electromagnetic input signal and conversion into an electrical signal, a signal processing unit (3') for processing and amplification of the electrical signal, an earphone (18, 28) for converting the electrical signal into an acoustic signal, at least one first aeration channel (15, 23) and at least one second aeration channel (16, 24) for ventilating the auditory canal volume (14) enclosed by the hearing aid device (11, 22) or the otoplastic, whereby the aeration channels (15, 16, 23, 24) have respective structures allocated to them for promoting a flow direction through the aeration channel (15, 16, 23, 24), for promoting the flow of air out of the enclosed auditory canal volume (14) in the first aeration channel (15, 23) and for promoting the flow of air into the enclosed auditory canal volume in the second aeration channel (16, 24)
2. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 1,
   characterized by means for generating a drive signal having a signal frequency in an inaudible frequency range, with the drive signal being superimposed on said processed signal and being output via the earphone (18, 28) for active ventilation of the auditory canal volume (14) enclosed by the earphone (18, 28) or the optoplastic.
3. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 1 or 2
   characterized by a structuring of the aeration channels (15, 16) to promote the flow in one direction through the aeration channel (15, 16) in each case.
4. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 1 or 2
   characterized in that flaps (25, 26) or valves are assigned to the aeration channels, which automatically open if the pressure drops in one direction and close if the pressure drops in the opposite direction.
5. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 1 or 2
   characterized by means for automatic, active opening and closing of the aeration channels (23, 24, 30).
6. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 5
   characterized by valves (33) or flaps to which miniature electrical and/or magnetic drives are assigned, for effective opening and closing of the aeration channels (30).
7. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 5 or 6
   characterized in that means for automatic, active opening and closing of the aeration channels (30) are manufactured at least in part using microstructure technology.
8. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in one of the claims 2 to 7,
   characterized in that amplitude and/or frequency of the drive signal can be selected.
9. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 9,
   characterized by means for detecting characteristic values of the input signal and means for setting the drive signal depending on the characteristic values.
10. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in one of the claims 2 to 9,
    characterized by a sensor for detecting a characteristic value of the auditory canal volume enclosed by a hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, and means for setting the drive signal depending on the characteristic value.
11. Hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in claim 10,
    characterized by a sensor for detecting the enclosed auditory canal volume (14) and/or a sensor (10) for detecting the humidity in the enclosed auditory canal volume (14).
12. Method for operating a hearing aid device to be worn in the ear (11, 22) or hearing aid device with otoplastic to be worn in the ear, as claimed in one of the claims 1 to 11,
    characterized in that a drive signal with a signal frequency lying outside the audible frequency range is generated and superimposed on the electrical signal and emitted via the earphone (18, 28) into the auditory canal (12) for active ventilation of the auditory canal (12).
13. Method as claimed in claim 12,
    characterized in that characteristic values of the electrical signal are detected and frequency and/or amplitude of the drive signal are set depending on the characteristic values.
14. Method as claimed in claim 13
    characterized in that the drive signal is set depending on the amplitude of the electrical signal.
15. Method as claimed in claim 13 or 14
    characterized in that a threshold value is present and the drive signal is set so that the amplitude of the signal produced from the sum of the electrical signal and the drive signal does not exceed the threshold value.
16. Method as claimed in claim 13
    characterized in that the threshold value is set by programming the hearing aid device (11, 22).

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