Hearing aid and method for operating same

Abstract

A hearing instrument (4) is specified with a housing (8) worn in a designated wearing position behind the ear or in the ear, wherein a battery (20), a wireless communication device (22), and a capacitive sensor (28) are arranged in the housing (8). The wireless communication device (22) comprises an antenna (24) and a transmitting and receiving unit (26) electrically connected thereto. The capacitive sensor (28) comprises at least one sensor electrode (32, 32a, 32b, 34, 34a, 34b) and a control and evaluation circuit (30) electrically connected thereto. The battery (20) and / or the antenna (24) or at least a section (48, 50) of the antenna (24) are used as sensor electrodes (32, 32a, 32b, 34, 34a, 34b) of the capacitive sensor (28).

Description

[0001] The invention relates to a hearing instrument with a housing worn in a designated wearing position behind the ear or in the ear. The invention further relates to methods for operating such a hearing instrument.

[0002] A hearing instrument is generally defined as an electronic device that supports the hearing of a person wearing the hearing instrument (hereinafter referred to as the "wearer" or "user"). In particular, the invention relates to hearing instruments designed to fully or partially compensate for the hearing loss of a hearing-impaired user. Such a hearing instrument is referred to as a "hearing aid." There are also hearing instruments that protect or improve the hearing of users with normal hearing, for example, enabling improved speech comprehension in complex listening situations. Hearing instruments also include wireless headphones (worn in or on the ear), in particular so-called ear plugs and headsets.

[0003] Hearing instruments in general, and hearing aids in particular, are usually designed to be worn on the head, and in particular in or on one ear of the user, particularly as behind-the-ear devices (also known as BTE devices) or in-the-ear devices (also known as ITE devices). With regard to their internal structure, hearing instruments usually have at least one (acousto-electrical) input transducer, a signal processing unit (signal processor), and an output transducer. During operation of the hearing instrument, the or each input transducer receives airborne sound from the environment of the hearing instrument and converts this airborne sound into an (input) audio signal (i.e., an electrical signal that conveys information about the ambient sound). In the signal processing unit, the or each input audio signal is processed (i.e.,modified with regard to its sound information) to support the user's hearing ability, in particular to compensate for a hearing loss. The signal processing unit outputs a correspondingly processed (output) audio signal to the output transducer. In modern hearing instruments, signal processing regularly includes a variety of other functions in addition to or as an alternative to frequency-dependent amplification of the input audio signal, e.g., beamforming (i.e., direction-dependent attenuation), active noise cancellation, wind noise suppression, feedback attenuation, binaural processing to support spatial hearing, dynamic and / or spectral compression, etc.

[0004] In most cases, the output transducer is designed as an electro-acoustic transducer, which converts the (electrical) output audio signal back into airborne sound, which is then emitted into the user's ear canal after being modified relative to the ambient sound. In a hearing instrument worn behind the ear, the output transducer, also known as the "receiver," is usually integrated outside the ear in a housing of the hearing instrument. In this case, the sound emitted by the output transducer is guided into the user's ear canal via a sound tube. Alternatively, the output transducer can also be located in the ear canal, and thus outside the housing worn behind the ear. Such hearing instruments are also referred to as "receiver in canal" devices.Hearing instruments worn in the ear that are so small that they do not protrude beyond the ear canal are also called CIC devices (from the English term "completely in canal").

[0005] In other designs, the output transducer can also be designed as an electro-mechanical transducer that converts the output audio signal into structure-borne sound (vibrations), whereby this structure-borne sound is emitted, for example, into the user's skull bone.

[0006] A "hearing system" generally refers to an arrangement of devices and, where appropriate, other structures that provide functions for operating a hearing instrument. In the simplest case, the hearing system consists only of the hearing instrument itself. However, in addition to the hearing instrument, the hearing system usually includes at least one peripheral device that interacts with the hearing instrument during operation, e.g., another hearing instrument for the user's other ear, a remote control, an external microphone, a programming device for the hearing instrument, or a charger. Modern hearing systems often also include, in addition to the hearing instrument, a software application that can be installed on a (particularly mobile) computer, e.g., a smartphone or tablet computer, and provides functions for operating the hearing instrument (e.g., remote control, programming, firmware updates, data backup, complex signal processing, and / or internet connection).The computer on which this software application (hereinafter referred to as the "hearing app") is installed also represents a peripheral device of the hearing instrument during operation, connected to the hearing instrument for data transmission purposes. However, the computer itself is generally not part of the hearing system, as it is manufactured and distributed independently of the hearing system components and can be used for a variety of other applications not related to the hearing system. Rather, the computer (in particular, the user's smartphone or tablet computer) is used by the hearing app only as an external resource for computing power, storage space, and communication services.

[0007] The proper functioning of a hearing instrument, and thus the benefit it provides to its wearer in daily use, depends crucially on the fit of the housing in or on the wearer's ear. In other words, the hearing instrument can generally only satisfactorily fulfill its intended function if it is positioned in the intended wearing position behind the ear or in the ear.

[0008] This is due, on the one hand, to the fact that the signal processing of the hearing instrument is tailored to a specific acoustic situation at the location of the or each microphone of the hearing instrument, e.g., to a specific orientation of at least one microphone in relation to the head and to a specific acoustic shadowing of the or each microphone by the ear. If the housing of the hearing instrument is inserted behind the ear or in the ear in a position deviating from the intended wearing position, this also changes the acoustic situation to which the or each microphone is exposed, and thus also the input audio signal picked up by the or each microphone. Signal processing tailored to a different acoustic situation can regularly no longer optimally process the input audio signal picked up by incorrectly positioned microphones. This can manifest itself, for example, in the fact that the desired useful signal (e.g.,the voice of a conversation partner) is muffled instead of an unwanted background noise, that active noise cancellation and binaural signal processing no longer function to a satisfactory degree, etc.

[0009] Another undesirable effect of incorrect housing positioning can be a compromised acoustic seal in the ear canal by the hearing instrument. In a BTE device, for example, incorrect housing adjustment can lead to the connector being overtightened or bent, thereby exerting a tensile load on the earpiece, which can pull the earpiece completely or partially out of the ear. A compromised acoustic seal in the ear canal can, in turn, lead to undesirable side effects, such as increased noise levels or the occurrence of acoustic feedback.

[0010] However, experience has shown that older people in particular, who represent a typical user group of hearing instruments due to age-related hearing loss, often have considerable problems using hearing instruments correctly.

[0011] Against this background, the invention is based on the object of enabling an improved testing of the proper fit of a hearing instrument.

[0012] With regard to a hearing instrument, this object is achieved according to the invention by the features of claim 1. With regard to a method for operating a hearing instrument, the above object is achieved according to the invention by the features of claim 10. Advantageous and partly inventive embodiments and further developments of the invention are set out in the subclaims and the following description.

[0013] The invention is based on a hearing instrument with a housing that is to be worn in a designated wearing position behind the ear or in the ear of a user. The hearing instrument can therefore be either a BTE device or an ITE device, as described above. In the case of a BTE device, the hearing instrument comprises, in addition to the housing worn behind the ear, an earpiece to be placed in the user's ear and a flexible connecting piece that connects the housing and the earpiece. In this case, the hearing instrument is either a conventional hearing instrument with a receiver arranged in the housing or a RIC device in which the receiver is arranged in the earpiece. In the former case, the connecting piece is formed by a sound tube that conducts the sound produced by the receiver to the earpiece.In the latter case, the connector is an electrical connecting cable through which the output audio signal is transmitted to the earpiece located in the earpiece.

[0014] In all embodiments described above, a battery, a wireless communication device and a capacitive sensor are further arranged in the housing.

[0015] The wireless communication device is used for wireless data exchange between the hearing instrument and a peripheral device, e.g. another hearing instrument or a smartphone of the user, and comprises an antenna and an electrically connected transmitting and receiving unit (transceiver).

[0016] The capacitive sensor can generally detect dielectrically active or electrically conductive structures in the vicinity of the sensor, namely in particular body structures such as the user's head and ear. The capacitive sensor comprises at least one sensor electrode and an electrically connected control and evaluation circuit (also referred to as a "sensor controller"). In the hearing instrument according to the invention, the capacitive sensor is used in particular to check for the correct fit of the housing in the ear or behind the ear. This exploits the fact that the (capacitive) sensor signal emitted by the capacitive sensor depends in a characteristic way on the fit of the housing behind the ear or in the ear due to the variety of surrounding body structures of the user.In other words, the sensor signal emitted by the capacitive sensor changes in a characteristic manner when the user moves the hearing instrument housing behind the ear or inside the ear. The correct fit of the housing in the intended wearing position can be determined based on this dependence of the capacitive sensor signal.

[0017] However, since hearing instruments are very small devices, the arrangement of at least one sensor electrode in the housing is recognized as problematic. In particular, in hearing instruments, the surface of the housing is usually taken up almost exclusively by the battery and the antenna of the wireless communication device. Arranging the at least one sensor electrode of the capacitive sensor next to the battery and the antenna would only be possible if the antenna and the sensor electrode were sufficiently small, which would significantly impair the function of both the wireless communication device and the capacitive sensor.

[0018] To avoid this dilemma, in the hearing instrument according to the invention, the battery and / or the antenna of the wireless communication device, or at least a portion thereof, are additionally used as the sensor electrode of the capacitive sensor. In other words, according to the invention, the sensor electrode or at least one of possibly several sensor electrodes of the capacitive sensor is formed by the battery or the antenna or an antenna portion.

[0019] As a result, no additional space is required to accommodate the at least one sensor electrode in the housing – in comparison to conventional hearing instruments with a battery and wireless communication device, but without a capacitive sensor. The available space in the housing can be effectively utilized for both the antenna and the at least one sensor electrode, allowing both the wireless communication device and the capacitive sensor to operate without mutual interference.

[0020] The control and evaluation circuit (sensor control) of the capacitive sensor is preferably configured to apply an electrical alternating voltage (also referred to as "(capacitive) sensor voltage") to the sensor electrode and to measure a response signal generated under the action of this alternating voltage, which is characteristic of an electrical capacitance associated with the sensor electrode. The control and evaluation circuit (sensor control) is preferably designed as a microcontroller. The functionality of the control and evaluation circuit is implemented as software in this case. However, within the scope of the invention, the control and evaluation circuit can also be designed as a non-programmable (analog or digital) electrical circuit. In both cases, the control and evaluation circuit can be integrated either as a standalone component (e.g., as a separate integrated circuit) or together with other functions in a larger unit, e.g.,in the hearing instrument's signal processor. The sensor voltage can be generated either as a sinusoidal signal or with a different time characteristic (e.g., as a rectangular pulse signal, triangular pulse signal, or sawtooth pulse signal). It can vary around the voltage zero point or a different voltage mean value.

[0021] Within the scope of the invention, the capacitive sensor can be based in particular on one of two conventional functional principles.

[0022] According to a first functional principle, referred to as "single-electrode measurement" or "self-capacitance sensing," the control and evaluation circuit measures the response signal at the same sensor electrode to which it applies the sensor voltage. As a capacitance-dependent response signal, the control and evaluation circuit measures, for example, the current flowing under the action of the sensor voltage on the at least one sensor electrode or the frequency of the sensor voltage (utilizing the fact that the sensor electrode is part of an oscillating circuit with a capacitance-dependent varying resonance). In all cases, the response signal is characteristic of the (electrical) capacitance of the at least one sensor electrode with respect to an external ground potential. In "single-electrode measurement," the external ground potential acts as the counter electrode of the capacitor whose capacitance the sensor measures, which here, for example,formed by the user's body.

[0023] According to a second functional principle, known as "two-electrode measurement," "transmitter-receiver principle," or "relative capacitance measurement" (mutual capacitance sensing), the control and evaluation circuit applies the sensor voltage to a first sensor electrode (transmitting electrode) and measures the response signal at another sensor electrode (receiving electrode). In this case, the control and evaluation circuit measures, as a capacitance-dependent response signal, the current generated in the receiving electrode via an electric field under the action of the sensor voltage. The response signal is characteristic of the (electrical) capacitance of the capacitor formed by the two sensor electrodes. In "two-electrode measurement," the user's body acts as an interference potential, which changes the capacitance of the capacitor formed by the two sensor electrodes and is thereby detected.

[0024] As explained above, the capacitive sensor of the hearing instrument according to the invention can be designed either as a "self-capacitance sensor" or as a "mutual capacitance sensor".

[0025] Preferably, the wireless communication device is configured to emit and receive electromagnetic radiation (radio waves) at a radio frequency of more than 100 MHz, preferably more than 1 GHz, in particular 2.4 GHz. The communication device is particularly designed to transmit and receive data according to the Bluetooth standard.

[0026] In a preferred embodiment, the control and evaluation circuit of the capacitive sensor is configured to generate the sensor voltage at an AC frequency that is significantly lower (preferably at least by a factor of 10, in particular by at least a factor of 100) than the radio frequency of the wireless communication device. This spectral separation prevents undesired interactions between the wireless communication device and the capacitive sensor. In a preferred embodiment of the invention, the control and evaluation circuit of the capacitive sensor is configured to generate the sensor voltage at an AC frequency of less than 10 MHz.

[0027] To prevent interference with the capacitive sensor, a frequency-selective filter is interposed between the capacitive control and evaluation circuit and the or each sensor electrode in a suitable embodiment of the invention. This filter is preferably configured differently depending on whether the battery or the antenna is used to form the respective sensor electrode. Thus, the frequency-selective filter is preferably a high-pass filter (blocking DC voltage) if the sensor electrode is the battery. In contrast, the frequency-selective filter is preferably formed by a low-pass filter (blocking the radio frequency of the wireless communication device) if the sensor electrode is the antenna or an antenna section.In both cases, a bandpass filter can alternatively be used within the scope of the invention, which is permeable to the alternating voltage of the capacitive sensor, but blocks both direct voltages and the radio frequency of the wireless communication device.

[0028] In an advantageous embodiment of the invention, the antenna comprises a first (antenna) section and a second (antenna) section, wherein the two antenna sections are electrically separated from one another for low-frequency signals with the AC frequency of the capacitive sensor. Preferably, the two antenna sections are arranged at least predominantly on different sides of the housing, which in particular are opposite one another. In a hearing instrument designed as a classic BTE or RIC device, in which the housing is worn behind the ear in the intended wearing position, one of these two sides of the housing faces in particular the user's head in the intended wearing position, while the other side of the housing faces away from the user's head in the intended wearing position.

[0029] With the antenna divided into two sections, optionally only one of the two antenna sections is used as the sensor electrode of the capacitive sensor. Alternatively—and preferably—the two sections of the antenna are used as different sensor electrodes of the capacitive sensor. In a practical embodiment of the invention, the two sensor electrodes are operated independently of each other. In this case, an independent response signal is measured at each of the two sensor electrodes, enabling a differentiated detection of body structures in the vicinity of the housing and thus a particularly precise detection of the hearing instrument's fit. In an alternative embodiment of the invention, the two antenna sections used as sensor electrodes act together as the transmitting and receiving electrodes of the capacitive sensor, which in this case operates according to the "transmitter-receiver principle."

[0030] A further embodiment of the invention relates to a hearing system comprising the hearing instrument according to the invention (particularly in one of the variants described above) and a fit control unit. The fit control unit is configured to check the fit of the housing on the user's ear based on a sensor signal output by the capacitive sensor. The fit control unit, which is optionally implemented as a software module or as a non-programmable electronic circuit, preferably performs this check by comparing the sensor signal output by the capacitive sensor with a stored reference value. Since every user has an individual head and ear shape, the reference value is preferably also determined individually for the respective user.In an alternative embodiment, the fit control unit comprises a neural network to which the sensor signal from the capacitive sensor is fed and which is, in particular, individually trained for the respective user in order to check the fit of the hearing instrument based on the sensor signal. The fit control unit is preferably integrated into the hearing instrument. In this case, the hearing system can also consist solely of the hearing instrument itself equipped with the fit control unit. Alternatively, the fit control unit is located outside the hearing instrument, e.g., in a peripheral device or a software application (hearing app) of the hearing system.

[0031] The fit control unit is further configured to trigger the output of a message upon detection of a deviation of the fit from the intended wearing position, alerting the user to the deviating fit of the housing. This message is preferably displayed by outputting a text message or a graphical message (e.g. in the form of a schematic representation of the hearing instrument housing arranged on the ear) on a peripheral device, e.g. by a hearing app assigned to the hearing instrument on the display of a user's smartphone. Additionally or alternatively, the message is output by the hearing instrument itself, e.g. in the form of a signal tone, a voice message played via the receiver of the hearing instrument or by a tactile signal (e.g. vibration).

[0032] In a further embodiment, the fit control unit is configured to adjust at least one signal processing parameter of the hearing instrument based on the capacitive sensor signal output by the capacitive sensor in order to adapt the signal processing (i.e., the function of the signal processor) of the hearing instrument to the fit of the housing. In particular, the fit control unit adjusts the orientation of a beam former of the hearing instrument in such a way that a detected deviation of the fit of the housing from the intended wearing position is compensated.

[0033] In a particularly preferred embodiment of the invention, the seat control unit is designed to carry out the two functions described above

[0034] To combine design variants by adjusting at least one signal processing parameter of the hearing instrument (in particular the alignment of a beamformer) when a slight deviation of the fit from the intended wearing position is detected in order to adapt the signal processing of the hearing instrument to the fit of the housing, and only when a large deviation of the fit from the intended wearing position is detected does it cause the output of the message informing the user of the deviating fit of the housing.

[0035] The method according to the invention utilizes the hearing instrument according to the invention in one of the embodiments described above. The above information regarding design variants and components of the hearing instrument and the associated effects and advantages therefore also applies mutatis mutandis to corresponding embodiments of the method, and vice versa.

[0036] In the course of the method according to the invention, a capacitive sensor signal is determined as a measure of the fit of the housing behind or in the user's ear using the battery and / or the antenna or a section thereof as the sensor electrode of the capacitive sensor. If a deviation of the fit from the intended wearing position is detected, a message indicating the deviated fit of the housing is output. Additionally or alternatively, at least one signal processing parameter of the hearing instrument is adjusted based on the capacitive sensor signal output by the capacitive sensor in order to adapt the signal processing of the hearing instrument to the fit of the housing.

[0037] Exemplary embodiments of the invention are explained in more detail below with reference to a drawing. In the drawings: Fig. 1 shows a schematic representation of a hearing system with a hearing instrument and a software application (hearing app) installed in a smartphone of the user, wherein the hearing instrument is designed as a hearing aid with an output transducer (receiver) to be arranged in the user's ear canal and a housing that can be worn behind a user's ear in a designated wearing position, wherein a battery, a wireless communication device with an antenna and a capacitive sensor are arranged in the housing, and wherein the battery and / or the antenna or a section thereof are used as a sensor electrode of the capacitive sensor, Fig. 2 shows an exploded view of a concrete implementation of the hearing instrument according to Fig. 1 with the housing opened, Fig. 3 shows a perspective view of the battery, the antenna and an electronics frame of the hearing instrument indicated by dashed lines, Fig. 4 shows a schematic view of an embodiment of the wireless communication device and the capacitive sensor, in which two sections of the antenna are used as different sensor electrodes of the capacitive sensor, and wherein the two antenna sections are connected to a control and evaluation circuit of the capacitive sensor in such a way that they interact as transmitting and receiving electrodes and that the control and evaluation circuit measures a response signal that is characteristic of the capacitance of the capacitor formed from the two antenna sections, Fig. 5 shows a view according to Fig. 4 an alternative embodiment of the wireless communication device and the capacitive sensor, in which two sections of the antenna are also used as different sensor electrodes of the capacitive sensor, but wherein the two antenna sections are connected to a control and evaluation circuit of the capacitive sensor in such a way that they are operated as independent sensor electrodes, and that the control and evaluation circuit measures a response signal at each of the two antenna sections, which is characteristic of the capacitance of the respective antenna section against an external ground potential, Fig. 6 in representation according to Fig. 4 a variant of the embodiment of the wireless communication device and the capacitive sensor therein, in which, in addition to the two antenna sections, the two poles of the battery are used as further sensor electrodes of the capacitive sensor, and Fig. 7 shows a schematic representation of an example of a warning message which is displayed on a display of the smartphone at the instigation of a seating control unit of the hearing system when the seating control unit detects, on the basis of a sensor signal from the capacitive sensor, that the seating of the housing deviates significantly from the intended wearing position.

[0038] Corresponding parts and sizes are always provided with the same reference symbols in all figures.

[0039] Fig. 1 shows a roughly schematic representation of a hearing system 2, which is formed from a hearing instrument 4 and an associated software application (hearing app 6).

[0040] The hearing instrument 2 is, for example, a hearing aid, i.e., a hearing instrument designed to support the hearing of a hearing-impaired user. In the embodiment shown here, the hearing instrument 2 is designed as a RIC device. It accordingly comprises a housing 8, which is intended to be worn behind a user's ear, and an earpiece 10, which is intended to be inserted into the user's ear canal, wherein an electro-acoustic output transducer (receiver 12) is integrated into the earpiece 10. The hearing instrument 2 further comprises a flexible connecting piece 14, which mechanically connects the housing 8 to the earpiece 10. In the case of the Fig. 1 In the RIC device shown, the connector 14 comprises an electrical connection cable for the handset 12.

[0041] Within a housing 8, the hearing instrument 4 has the following components: at least one microphone 16 (in the example shown, two microphones 16) as an input transducer, a (particularly digital) signal processor 18, a battery 20, a wireless communication device 22 with an antenna 24 and a transmitting and receiving unit (transceiver 26) electrically connected thereto, and a capacitive sensor 28, which is formed from a control and evaluation circuit (sensor control 30) and a plurality of (two in the embodiment shown) sensor electrodes 32 and 34.

[0042] During normal operation of the hearing instrument 4, the microphones 16 each record airborne sound from the environment of the hearing instrument 4. The microphones 16 convert the sound into an (input) audio signal I, i.e., into an electrical signal containing information about the recorded sound. The respective input audio signal I is fed within the hearing instrument 4 to the signal processor 18, which modifies this input audio signal I to support the user's hearing ability, in particular by frequency-selectively amplifying it to compensate for a hearing loss of the user.

[0043] The signal processor 18 outputs an output audio signal O, i.e., again an electrical signal, which in this case contains information about the processed and thus modified sound, to the receiver 12 via an electrical signal line 36 routed through the housing 8 and the connecting piece 14. The signal processor 18 and all other electrical or electronic components of the hearing instrument 4 are supplied with a direct current voltage referred to as the operating voltage UB from the battery 20.

[0044] The wireless communication device 22 serves for the (wireless) exchange of data between the hearing instrument 4 and the hearing app 6 and / or possibly other components of the hearing system 2, e.g. a further hearing instrument 4 (not shown) for the other ear of the user.

[0045] The hearing app 6 is used in particular for remote control and programming of the hearing instrument 4. During operation of the hearing system 2, the hearing app 6 is installed and executable on a (particularly mobile) computer. In the example shown, this computer is a smartphone 38 of the user. The computer, in particular the smartphone 38, is not itself a component of the hearing system 2, but is used by the hearing app 6 only as an external resource for computing power, storage space, and communication services. In particular, the hearing app 6 accesses a wireless communication device (not shown in detail) of the smartphone 38 in order to exchange data with the hearing instrument 4. The wireless communication device 22 of the hearing instrument 4 and the wireless communication device of the smartphone 38 are generally designed to exchange radio signals (including radio waves, namely electromagnetic radiation with a radio frequency of more than 100 MHz).Preferably, the data transmission between the hearing instrument 4 and the smartphone 38 (and thus the hearing app 6) is based on the Bluetooth standard, at a radio frequency of 2.4 GHz.

[0046] The capacitive sensor 28 is used to detect whether the housing 8 is positioned correctly on the user's ear, i.e., to check whether the housing 8 is in a designated wearing position or a position deviating therefrom. The capacitive sensor 28 uses the battery 20 and / or the antenna 24 as sensor electrode(s) 32, 34. The battery 20 and the antenna 24 are also electrically connected to the sensor controller 30 for this purpose. The sensor controller 30 controls the battery 20 used as sensor electrode 32 and the antenna 24 used as sensor electrode 34 with an electrical alternating voltage referred to as the sensor voltage Us, whose alternating voltage frequency lies between 20 kHz and 10 MHz and is, for example, 100 kHz. The sensor voltage Us is thus spectrally spaced between the operating voltage UB generated by the battery 20 on the one hand and the radio frequency of the wireless communication device 22 on the other.

[0047] The signal processor 18, the transceiver 26 and the sensor controller 30 are each optionally formed by a programmable circuit (e.g., a microprocessor) with software installed therein, by a non-programmable circuit (e.g., in the form of an ASIC), or by a combination of at least one programmable subunit and at least one non-programmable subunit. As in Fig. 1 As indicated by way of example, the signal processor 18, the transceiver 26, and the sensor controller 30 can each be designed as separate circuits. Alternatively, the transceiver 26 and / or the sensor controller 30 are integrated with the signal processor 18 and / or at least one additional control unit of the hearing instrument 4, if present, in a common circuit.

[0048] Fig. 2 shows a concrete realization of the hearing instrument 4 from Fig. 1 with the housing 8, which is here constructed in two parts and has a housing cover 40 and a housing shell 42 which can be assembled therewith. Fig. 2 The hearing instrument 4 is shown in an exploded view, in which the housing cover 40 is removed from the housing shell 42. In this view, an electronics frame 44 of the hearing instrument 4 is inserted into the housing shell 42, on which frame 44, with the exception of the receiver 12, all electrical and electronic components of the hearing instrument 4 are held, in particular the microphones 16, the signal processor 18, the battery 20 (to which Fig. 2 but only an empty battery receptacle 46 of the electronics frame 44 is shown), the wireless communication device 22 and the capacitive sensor 28. The antenna 24 is mounted on the surface of the electronics frame 44. The arrangement of the battery 20 and the antenna 24 with respect to the electronics frame 44 is shown in Fig. 3 clarified again; the electronics frame 44 is indicated here only by a dashed line.

[0049] From the presentation of the Fig. 3 It becomes clear that the antenna 24 is formed from two loop-shaped (antenna) sections 48 and 50, which are arranged for the most part on opposite sides of the housing 8. In an embodiment of the hearing instrument 4 for the user's right ear, the antenna section 48 is arranged on the side of the housing 8 that faces the user's head in the wearing position, while the antenna section 50 is arranged on the side of the housing 8 that faces away from the user's head in the wearing position. In an embodiment of the hearing instrument 4 for the user's left ear, on the other hand, the antenna section 48 is arranged on the side of the housing 8 that faces away from the user's head in the wearing position, while the antenna section 50 is arranged on the side of the housing 8 that faces the user's head in the wearing position. In terms of the antenna design, the Fig. 2 und 3 The antenna 24 shown is a folded dipole antenna.

[0050] Within the scope of the capacitive sensor 28, the antenna 24 can be used in different ways. For example, in a (in Fig. 1 indicated) embodiment, the entire antenna 24 is used as a single sensor electrode 34. In preferred embodiments that use the Fig. 4 und 5 are shown, the two antenna sections 48 and 50 of the antenna 24 are used as different sensor electrodes 34a and 34b. In order to achieve electrical separation of the two antenna sections 48, 50 or sensor electrodes 34a, 34b within the capacitive sensor 28 without impairing the function of the antenna 24 within the wireless communication device 22, an electrical high-pass filter 52 (e.g. in the form of a capacitor) is interposed between the two antenna sections 48 and 50, which is permeable to high-frequency electrical signals of the radio frequency, but blocks the low-frequency sensor voltage Us.Furthermore, in each of the electrical connections of the sensor control 30 to the antenna sections 48 and 50, a further frequency-selective electrical filter, here in the form of an electrical low-pass filter 54, is connected, which is permeable to the sensor voltage Us but blocks high-frequency electrical signals of the radio frequency.

[0051] In the two embodiments according to Fig. 4 und 5 the two antenna sections 48 and 50 (alias sensor electrodes 34a and 34b) are controlled differently by the sensor control 30.

[0052] In the execution according to Fig. 4 The sensor electrodes 34a and 34b are operated by the sensor controller 30 as transmitting electrodes and receiving electrodes, respectively. The sensor controller 30 applies the sensor voltage Us to the sensor electrode 34a. Under the action of the sensor voltage Us, the sensor electrode 34a generates an electric field E in a surrounding spatial volume that changes at the alternating voltage frequency, causing a charge shift in the sensor electrode 34b and thus an electric current flow. The sensor controller 30 preferably measures the current intensity of this current flow at the sensor electrode 34b as a response signal A, wherein this response signal A is characteristic of the (electrical) capacitance of the capacitor formed by the sensor electrodes 34a and 34b. The capacitive sensor 28 is thus designed as a "relative capacitance sensor" (mutual capacitance sensor).

[0053] Close to the housing 8 arranged (and in Fig. 4 Due to the alternating current conductivity of the human body and the electrical connection of the body to the sensor control 30 via ground M, the user's body structures 56 (shown schematically), e.g. the head and the ear, behind which the housing 8 is worn, act as an interference potential, which reduces the capacitance of the capacitor formed by the sensor electrodes 34a and 34b, and thus the value of the measured response signal A, the larger the body structure is and the closer it is arranged to the antenna 24.

[0054] In the execution according to Fig. 5 the sensor electrodes 34a and 34b are operated by the sensor controller 30 as separate (i.e., independent of one another) sensor electrodes. The sensor controller 30 applies the sensor voltage Us to both sensor electrodes 34a and 34b and measures the response signal A generated under the action of the sensor voltage Us independently for each of the sensor electrodes 34a and 34b; in this case, too, the current intensity of the current flowing to the respective sensor electrode 34a, 34b is preferably measured as the response signal A. The response signal A assigned to the respective sensor electrode 34a, 34b is characteristic of the capacitance of the respective sensor electrodes 34a and 34b with respect to ground M. The capacitive sensor 28 is thus designed as a "self-capacitance sensor" in this embodiment.The two sensor electrodes 34a and 34b are preferably supplied with the sensor voltage Us in phase, so that no electric field E runs between the two sensor electrodes 34a and 34b themselves.

[0055] The electric field E generated by the respective sensor electrode 34a, 34b under the influence of the control voltage Us runs here between the respective sensor electrode 34a, 34b and the nearest body structures 56 of the user. The body structures 56 of the user in the vicinity of the housing 8, which are connected to ground M for alternating voltages, in particular the head and the adjacent ear, act in this embodiment of the capacitive sensor 28 as counter electrodes to the respective sensor electrode 34a, 34b. In other words, each of the sensor electrodes 34a, 34b, together with the nearest body structures 56, forms the capacitor, the capacitance of which is measured at the respective sensor electrode 34a, 34b. This capacitance and thus the value of the measured response signal A is - unlike in the embodiment according to Fig. 4 - the higher the larger the body structures 56 are and the closer they are arranged to the respective sensor electrode 34a, 34b.

[0056] The embodiment according to Fig. 5 has compared to the execution according to Fig. 4 The advantage is that, with comparable structural complexity, it provides two response signals A instead of a single response signal A and can therefore detect the environment more accurately. The embodiment according to Fig. 5 is, however, more susceptible to (unwanted) interference than the embodiment according to Fig. 4 .

[0057] In a further embodiment according to Fig. 6 , the two antenna sections 48,50 (alias sensor electrodes 34a, 34b) - analogous to the embodiment according to Fig. 4 - operated as a transmitting electrode and receiving electrode. In addition, the sensor control 30 in the embodiment according to Fig. 6 but the two poles of the battery 20 as further sensor electrodes 32a and 32b. In the embodiment according to Fig. 6 These sensor electrodes 32a and 32b are also operated by the sensor controller 30 as transmitting electrodes and receiving electrodes, respectively, by the sensor controller 30 applying the sensor voltage Us to the sensor electrode 32a and measuring the response signal A (namely, the current intensity of the current flow generated under the action of the sensor voltage Us and the resulting electric field E) at the sensor electrode 32b. The response signal A is characteristic of the capacitance of the capacitor formed by the sensor electrodes 32a and 32b. The capacitive sensor 28 is thus also designed as a "relative capacitance sensor" (mutual capacity sensor) with respect to the poles of the battery 20 used as sensor electrodes 32a, 32b.In order to electrically decouple the sensor inputs and outputs of the sensor controller 30 from the operating voltage UB, a frequency-selective electrical filter, here in the form of an electrical high-pass filter 58, is connected to the sensor controller 30 and to each of the two poles of the battery 20 (alias the two sensor electrodes 32a and 32b), which is permeable to the sensor voltage Us but blocks the operating voltage UB output by the battery 20 as a DC voltage.

[0058] In addition to the Fig. 4 bis 6 In addition to the exemplary embodiments of the capacitive sensor 28 described above, numerous further embodiments can be used within the scope of the invention, which in particular result from other combinations of the embodiments described above. For example, in a modification of the embodiment according to Fig. 6 also the sensor electrodes 32a and 32b - analogous to the embodiment according to Fig. 5 - be operated as independent sensor electrodes. In addition, in a further modification of the embodiment according to Fig. 6 one of the sensor electrodes 32a, 32b formed on the battery 20 can also be used with one of the sensor electrodes 34a, 34b formed on the antenna 24 as a cooperating pair of transmitting and receiving electrodes.

[0059] In all of the embodiments described above, the or each measured response signal A is used during operation of the hearing instrument 4 in a method for checking the fit of the hearing instrument 4. To automatically carry out this method, the hearing system 2 comprises a fit control unit 60 which is configured to check the fit of the housing 8 on the user's ear based on a sensor signal S output by the capacitive sensor 28, i.e. to determine whether the housing 8 is in a designated wearing position behind the user's ear or whether the fit of the housing 8 deviates from the designated wearing position.

[0060] Within the scope of the invention, the seat control unit 60 can be formed by a non-programmable electronic circuit, e.g., in the form of or as part of an ASIC. Preferably, however, the seat control unit 60 is formed by a software module, which is, for example, integrated in the signal processor 18 (see FIG. Fig. 1 ) or possibly another programmable control circuit of the hearing instrument 4. In a further embodiment of the invention, the seating control unit 60 is implemented outside the hearing instrument 4 as part of the hearing app 6.

[0061] The sensor signal S output by the sensor controller 30 to the seat control unit 60 contains the (unchanged) value of the or each response signal A or a quantity derived therefrom, for example the capacitance assigned to the or each sensor electrode 32, 32a, 32b, 34, 34a, 34b or a quantity inverted or scaled thereto.

[0062] In order to check the fit of the housing 8 behind the user's ear, the fit control unit 60 compares the sensor signal S in a preferred embodiment of the method with a stored reference value that reflects the value of the sensor signal S when the housing 8 is positioned in the intended wearing position. If the fit control unit 60 detects a significant deviation of the sensor signal S from the reference value (in particular a deviation that exceeds a predetermined tolerance value), it triggers the output of a (warning) message to the user, which alerts the user to the incorrect fit of the housing 8 (i.e., deviating from the intended wearing position).

[0063] Since the value of the sensor signal S is also influenced by the approach of other body parts to the housing 8, e.g. the approach of a hand or a finger, but these interference influences are generally only of short duration, the seat control unit 60 is preferably designed to trigger the output of the warning message only if the sensor signal S deviates significantly from the reference value for longer than a predetermined time interval (e.g. more than 2 min).

[0064] The warning message is displayed, for example, in the form a signal tone emitted into the user's ear via the earpiece 12 or emitted by the hearing app 6 via a loudspeaker of the smartphone 38, a voice message emitted into the user's ear via the earpiece 12 or emitted by the hearing app 6 via a loudspeaker of the smartphone 38, a text message or graphic displayed by the hearing app 6 on the display of the smartphone 38, or a tactile alarm (e.g. a vibration signal) emitted via the hearing instrument 4 or the smartphone 38 or a combination of the aforementioned notification methods. The reference value is preferably individually learned during the fitting of the hearing instrument 4 to the user, e.g., by detecting the sensor signal S and storing it as a reference value after the housing 8 has been positioned by a specialist in the correct intended wearing position behind the user's ear.

[0065] In a further developed embodiment of the invention, the fit control unit 60 stores not only a single reference value for the sensor signal S, but also a function or characteristic curve or characteristic value table which, in addition to the characteristic value characteristic for the intended wearing position, also contains characteristic values ​​for different positions of the housing 8 behind the ear. The function, characteristic curve, or characteristic value table is also determined, for example, during the adjustment of the hearing instrument to the user by having the housing 8 placed behind the ear in various positions by a specialist, and by recording and storing the respective value of the sensor signal S in each position together with a position specification.In this embodiment, during operation of the hearing instrument 4, the fit control unit 60, according to the method, not only qualitatively determines whether the fit of the housing 8 corresponds to the intended wearing position by comparing the current value of the sensor signal S with the function, characteristic curve, or characteristic value table. Rather, the fit control unit 60 quantitatively determines how much and in which direction the fit of the housing 8 deviates from the intended wearing position.

[0066] If the seat control unit 60 in the above-mentioned embodiment detects a significant deviation of the sensor signal S from the reference value determined for the intended wearing position, it causes (e.g. using one of the methods described above) the output of a warning message to the user, which alerts the user to the incorrect fit of the housing 8 and contains an instruction to correct the fit.

[0067] Alternatively, the fit control unit 60 adjusts at least one signal processing parameter of the hearing instrument 4 based on the sensor signal S output by the capacitive sensor 28, so that the effect of the incorrect positioning of the housing 8 is fully or partially compensated. For example, the fit control unit 60 adjusts a beamformer of the signal processor 18 of the hearing instrument 4 such that a directional lobe of the beamformer is aligned with respect to the user's head in the same way as in the intended wearing position (e.g., always perpendicular to the longitudinal axis of the head), even when the housing 8 is incorrectly positioned.

[0068] In a further refined embodiment of the invention, the fit control unit 60 follows a differentiated process sequence. As described above, the fit control unit 60 adjusts the at least one signal processing parameter of the hearing instrument 4 to compensate for a detected incorrect fit of the housing 8 only if the detected deviation of the fit of the housing 8 from the intended wearing position is small (in particular, does not exceed a stored threshold value). Otherwise, i.e., in the event of a more severe mispositioning of the housing 8, the fit control unit 60, as also described above, triggers the output of the warning message, which alerts the user to the incorrect fit of the housing 8 and contains instructions for correcting the fit.

[0069] An example of a graphical variant of such a warning message, which is displayed on the display of the smartphone 38 by the hearing app 6 at the instigation of the seat control unit 60, is shown in Fig. 7 The exemplary warning message contains an image of a human ear 62, a first image 64 of the housing 8 in the current position determined by the sensor signal S (in Fig. 7 shown with a solid line) and another figure 66 of the housing 8 in the intended carrying position (in Fig. 7 shown with a dashed line). The user can already infer the instructions for correcting the fit from the deviation shown in the two figures 64 and 66 of the housing 8. As an additional (optional) instruction for correcting the fit, the warning message contains an arrow 68, which instructs the user, in the example shown, to move the housing 8 further down on the ear.

[0070] In a further embodiment of the invention, the seat control unit 60 contains a neural network individually trained for the user, which contains the sensor signal S as an input signal and, in the event of a significant misfit of the housing 8, initiates at least one corrective measure, in particular (as described above) an adjustment of at least one signal processing parameter of the hearing instrument 4 to compensate for the misfit and / or the output of a warning message to the user.

[0071] In further embodiments of the invention, the hearing instrument is a conventional BTE device with a housing worn behind the ear and a receiver arranged in this housing, or an ITE device with a housing worn in the ear canal. The above explanations regarding the design and arrangement of the capacitive sensor and for testing the fit of the housing behind the ear or in the ear can be easily applied to these device types.

[0072] The invention is particularly clear from the exemplary embodiments described above, but is by no means limited thereto. Rather, further embodiments of the invention can be derived from the claims and the above description. List of reference symbols

[0073] 2Hearing system 4Hearing instrument 6Hearing app 8Housing 10Earpiece 12Receiver 14Connector 16Microphone 18Signal processor 20Battery 22(Wireless) communication device 24Antenna 26Transceiver 28(Capacitive) sensor 30Sensor control 32Sensor electrode 32aSensor electrode 32bSensor electrode 34Sensor electrode 34aSensor electrode 34bSensor electrode 36Signal line 38Smartphone 40Housing cover 42Housing shell 44Electronics frame 46Battery receptacle 48(Antenna) section 50(Antenna) section 52High-pass filter 54Low-pass filter 56Body structure 58High-pass filter 60Fit control unit 62Ear 64Figure 66Figure 68Arrow AResponse signal E(electric) field IInput signal MGround OOutput signal UOperating voltage UsSensor voltage SSensor signal

Claims

1. Hearing instrument (4) with a housing (8) worn in a designated wearing position behind the ear or in the ear, wherein a battery (20), a wireless communication device (22) and a capacitive sensor (28) are arranged in the housing (8), - wherein the wireless communication device (22) comprises an antenna (24) and a transmitting and receiving unit (26) electrically connected thereto, - wherein the capacitive sensor (28) comprises at least one sensor electrode (32, 32a, 32b, 34, 34a, 34b) and a control and evaluation circuit (30) electrically connected thereto, and - wherein the battery (20) and / or the antenna (24) or at least a section (48, 50) of the antenna (24) is additionally used as a sensor electrode (32, 32a, 32b, 34, 34a, 34b) of the capacitive sensor (28) are used.

2. Hearing instrument (4) according to claim 1, wherein the control and evaluation circuit (30) of the capacitive sensor (28) is configured to apply an electrical alternating voltage (Us) to the sensor electrode (32, 32a, 32b, 34, 34a, 34b) and to measure a response signal (A) generated under the action of this alternating voltage (Us), which is characteristic of an electrical capacitance assigned to the sensor electrode (32, 32a, 32b, 34, 34a, 34b).

3. Hearing instrument (4) according to claim 1 or 2, wherein the wireless communication device (22) is configured to emit and receive electromagnetic radiation with a radio frequency of more than 100 MHz, preferably more than 1 GHz, in particular 2.4 GHz.

4. Hearing instrument (4) according to claim 2 or 3, wherein the control and evaluation circuit (30) of the capacitive sensor (28) is configured to generate the sensor voltage (Us) with an alternating voltage frequency of less than 10 MHz.

5. Hearing instrument (4) according to one of claims 1 to 4, wherein a frequency-selective filter (54, 58) is connected between the capacitive control and evaluation circuit (30) and the or each sensor electrode (32, 32a, 32b, 34, 34a, 34b).

6. Hearing instrument (4) according to one of claims 1 to 5, wherein the antenna (24) comprises a first section (48) and a second section (50), and wherein only one of the two sections (48, 50) of the antenna (24) is used as a sensor electrode (34a, 34b) of the capacitive sensor (28) or wherein the two sections (48, 50) of the antenna (24) are used as different sensor electrodes (34a, 34b) of the capacitive sensor (28).

7. Hearing instrument (4) according to one of claims 1 to 6, wherein the control and evaluation circuit (30) of the capacitive sensor (28) is configured to apply the sensor voltage (Us) to the same sensor electrode (32a, 32b, 34a, 34b) and to measure the response signal (A).

8. Hearing instrument (4) according to one of claims 1 to 7, wherein the capacitive sensor (28) has at least two sensor electrodes (32a, 32b, 34a, 34b) electrically connected to the control and evaluation circuit (30), wherein the control and evaluation circuit (30) of the capacitive sensor (28) is designed to apply the sensor voltage (Us) to one of the two sensor electrodes (32a, 34a) and to measure the response signal (A) at the other sensor electrode (32b, 34b).

9. Hearing system (2) with a hearing instrument (4) according to one of claims 1 to 8, and with a fit control unit (60) which is configured to check the fit of the housing (8) behind or in the user's ear on the basis of a sensor signal (S) output by the capacitive sensor (28) and, if a deviation of the fit from the intended wearing position is detected, to cause the output of a message indicating the deviating fit of the housing (8), and / or which is configured to adjust at least one signal processing parameter of the hearing instrument (4) on the basis of the sensor signal (S) output by the capacitive sensor (28) in order to adapt the signal processing of the hearing instrument (4) to the fit of the housing (8).

10. A method for operating a hearing instrument (4) according to one of claims 1 to 8, - wherein, using the battery (20) and / or the antenna (24) or a section (48, 50) thereof as a sensor electrode (32, 32a, 32b, 34, 34a, 34b) of the capacitive sensor (28), a sensor signal (S) is determined as a measure of the fit of the housing (8) behind or in the user's ear, and - wherein, upon detection of a deviation of the fit from the intended wearing position, a message indicating the deviating fit of the housing (8) is output, and / or - wherein, based on the sensor signal (S) output by the capacitive sensor (28), at least one signal processing parameter of the hearing instrument (4) is adjusted in order to adapt the signal processing of the hearing instrument (4) to the fit of the housing (8).

Images