EP3582512A1 - Method for the identification of an earpiece, hearing system and earpiece set - Google Patents

Abstract

A method for identifying a receiver (6) of a hearing system (2) is specified. The receiver (6) belongs to one of several types of receiver. An electrical input signal (104) is fed to the receiver (6) for sound output, the input signal (104) being a primary signal (110) and a secondary signal (112) being generated on the basis of the sound output, which is dependent on the input signal (104). The secondary signal (112) is detected by a sensor (14), which generates an electrical sensor signal (114) depending on the secondary signal (112). A phase measurement is also carried out by determining a phase difference between the input signal (104) and the sensor signal (114). The receiver (6) is then identified by assigning the receiver (6) to one of the several receiver types on the basis of the phase difference. A corresponding hearing system (2) and a handset are also specified.

Description

The invention relates to a method for identifying a receiver, a hearing system and a receiver set.

A hearing system has one or two hearing aids that are worn by a user in or on the ear. A hearing system with two hearing aids, which are then worn in or on the ears on different sides of the head, is also referred to as a binaural hearing system. A hearing aid has a handset for sound output, which depending on the hearing aid type is either inserted into the ear or worn outside the ear, the sound signals then e.g. be inserted into the ear via a sound tube. A binaural hearing system therefore has two listeners. Hearing aid types are, for example, BTE, ITE, or RIC hearing aids.

A hearing system generally serves to output sound signals and often specifically to improve the hearing ability of the user. The user typically has limited hearing and the hearing system is then generally used to amplify sound signals from the environment, with the aim of compensating for deficient hearing. A respective hearing system is usually individually adapted and adjusted to the respective user in order to do justice to their individual hearing ability and to optimally compensate for the individual hearing impairment. Frequently, the user's hearing ability is specifically determined as part of an adjustment and then the hearing system is adjusted accordingly, possibly different for both ears. A hearing system can also be headphones in general. An essential component of a hearing system is the receiver, which is used for sound output and which is available in systems with an external or a modular receiver unit in a large number of variants. Depending on the hearing ability, a correspondingly suitable earpiece is then selected and used in the hearing system. For example, different earphones differ in the performance class, ie in the maximum possible power of the sound signal output and the maximum possible amplification which can be achieved with the hearing system during operation. In the case of severe hearing loss, a handset of a higher performance class must be selected in order to be able to compensate for the hearing loss accordingly. The hearing system is usually parameterized in such a way that its transmission behavior is adapted to the connected handset.

It is problematic that in principle different earphones can be used in a hearing system or that both sides are set differently or both and there is therefore a risk of confusion. The hearing system is typically designed in such a way that various receivers of different types of receivers can be connected as required. If several different types of listeners are now available, when assembling the hearing system, ie when connecting a listener to the hearing system, it must be ensured that the correct type of listener is also used. If a handset with handsets of different performance classes is available and a handset of a certain performance class is to be used, there is a risk that a handset of the wrong performance class may be accidentally picked up and used. When cleaning a hearing system, for example, there is also the risk that it will first be disassembled into several parts for cleaning and then assembled incorrectly. This is particularly problematic in the case of binaural hearing systems, since there are, in principle, two listeners which can differ accordingly on the two sides due to a different hearing ability, that is to say they can belong to different types of listeners. If the two earphones are accidentally swapped, the earpiece intended for the left side is used on the right side and vice versa. In general, using the wrong handset poses a significant security risk to the user Users, especially if a too high performance class is accidentally used.

To differentiate between listeners with different characteristics, the US 8,433,072 B2 proposed to use and measure the electrical resistance of a receiver as a characteristic parameter. It is also proposed to provide a handset with an identification tag, for example an RFID tag, and then to read it out in order to determine the properties of the handset.

Against this background, it is an object of the invention to improve the identification of a listener. For this purpose, a suitable method, a suitable hearing system and a suitable earphone set are to be specified. In general, different types of listeners should be recognized as reliably as possible. In particular, the risk of damage to the user by inserting and operating the wrong handset is to be reduced.

The object is achieved according to the invention by a method with the features according to claim 1. Furthermore, the object is achieved by a hearing system with the features according to claim 14 and by a receiver set with the features according to claim 15. Advantageous refinements, developments and variants are the subject of the dependent claims , The explanations regarding the method apply mutatis mutandis to the hearing system and the handset and vice versa.

The method serves to identify a listener of a binaural hearing system and is expediently also used for this. The method preferably serves to identify the listener in the hearing system, ie while the listener is connected to the hearing system, ie connected to it. The identification is thus carried out, so to speak, in situ, that is, when used as intended, and preferably by the hearing system itself and precisely not decoupled from the hearing system. The hearing system has in particular a control unit which is designed such that it carries out the method. Suitable is, however, also a variant in which the listener is alternatively or additionally identified outside the hearing system and independently of it, for example in a separate test procedure at the audiologist. As an alternative or in addition, the control unit is integrated in an external device, for example in a smartphone or a computer.

The listener belongs to one of several, in particular different, listener types. The handset is now identified by assigning it to one of the several handset types. The terms “identification” and “identify” in the context of a handset mean that it is not only recognized whether a handset is connected, but rather what type of handset is connected. In other words, the listener type is determined specifically and not just the presence of any listener, so that different, that is to say at least two, different listener types can be distinguished from one another and can also be distinguished.

An electrical input signal, or simply an input signal, is fed to the listener for sound output. The listener converts the input signal into an acoustic sound signal, in short simply a sound signal, and outputs it. So there is a sound output. The input signal is generally a primary signal and, based on the sound output, a secondary signal is now generated which is dependent on the input signal. The secondary signal is not necessarily the sound signal itself. A large number of different signals can be considered as the secondary signal, it being particularly important that the secondary signal is causally related to the input signal.

The secondary signal is then detected by a sensor which, depending on the secondary signal, generates an electrical sensor signal, briefly only a sensor signal. The secondary signal is therefore measured by the sensor. The sensor signal is therefore dependent on the input signal. The dependency of the sensor signal on the input signal is determined in particular by a transfer function, which does not necessarily have to be known. The transfer function describes in particular the change that the input signal experiences during the conversion into the sensor signal along a transfer path.

A phase measurement is also carried out by determining a phase difference between the input signal and the sensor signal. The phase measurement is therefore in particular an electrical comparison measurement in which two electrical signals, namely the input signal and the sensor signal, are compared with one another and the phase of which is determined relative to one another. The handset is then identified by assigning it to one of the several handset types based on the phase difference.

In the method, the receiver is connected to a receiver connection, preferably to a receiver connection of the hearing system. The input signal is provided to the listener via the handset connection. The invention is based in particular on the idea of identifying a listener in that listeners of different types of listeners are designed in such a way that they cause different phase changes and thus phase differences on the same handset connection and for the same input signal, and then recognize these phase differences in order to easily and easily reliable way to make a corresponding assignment of the handset to one of the handset types. In short: the listeners of different types of listeners differ in that they result in different phase differences in the phase measurement. In contrast, different listeners of the same listener type expediently also result in the same phase difference. Therefore, an earphone set according to the invention has at least two earphones, which belong to different types of earphones and which are designed such that they can be differentiated accordingly by the phase measurement described.

In order to generate the phase difference for the purpose of identifying the listener, the listener and the sensor are advantageously designed in such a way that their interaction produces the overall phase difference. In principle, a so-called transfer phase difference may already result from the transfer function between the input signal and the sensor signal. To identify the listener, an identification phase difference, or ID phase difference for short, is now added in addition to the transfer phase difference as a function of the listener type. Overall, different phase differences then also result for different types of listeners, with the transfer path in particular remaining the same or only slightly changed. Along the transfer path, an additional phase for identification, ie an identification phase or ID phase, is thus impressed, which is then present in the sensor signal in addition to a possible transfer phase difference due to the transfer path itself. The transfer phase difference is then suitably taken into account as an offset in the phase measurement and is preferably estimated or measured in advance, for example.

A core idea of the invention therefore consists, in particular, in designing a hearing system or a receiver for one or both such that a receiver of an incorrect and unused type of receiver results in a discernably different phase difference during phase measurement, that is to say an actual phase difference which is recognizable by deviates from an expected phase difference which a listener of a correct listener type would result in. An important aspect here is phase measurement, which can be implemented in a particularly simple manner and enables a particularly compact structure. A particular advantage of phase measurement is that no special or additional components such as resistors or RFID tags are required to identify the listener. Accordingly, a sensor is preferably used as the sensor, which is already installed in the hearing system anyway and which is then also used for other purposes, in particular when the hearing system is operated as intended. A further particular advantage is in particular that the listener initially only requires two signal contacts to connect to the hearing system and a third contact, which is designed as an identification contact and in particular solely for identifying the listener, is not required. Such a third contact is therefore preferably dispensed with and corresponding installation space is saved.

When identifying the listener, it is therefore known in particular which type of listener produces which phase difference. For this purpose, an assignment rule, in particular an assignment table, is expediently stored in a memory, in particular of the hearing system. The assignment rule assigns a certain phase difference to each type of listener, so that during the phase measurement the type of listener can be determined via the assignment table and expediently also determined. The memory is in particular part of the control unit.

The method can be used particularly advantageously to determine whether a receiver is also connected to a respective side of a binaural hearing system, which belongs to a type of receiver that is also provided for this side. In a particularly preferred embodiment, the hearing system is therefore binaural and a first of the plurality of handset types is a left handset, which is intended for use on the left side of the hearing system, and a second of the plurality of handset types is a right handset, which is intended for use on the right Side of the hearing system is provided. The hearing system therefore has a left hearing device and a right hearing device. The left hearing aid serves to care for the left ear of a user and is worn on the left side when used as intended, the right hearing aid serves analogously to care for the right ear of the user and is worn on the right side when used as intended. A mix-up is not provided and should rather be prevented since the user may have different hearing abilities on both sides and therefore the two hearing aids are expediently individually adapted to supply the corresponding side. A side recognition is then carried out within the scope of the method in that the listener is identified as a left listener or as a right listener on the basis of the phase difference. The phase measurement is therefore preferably used for side detection and in particular to distinguish between exactly two types of listeners. The two types of listeners then preferably produce phase differences which differ by 180 ° and are therefore particularly easy to discriminate, ie distinguishable. Using page recognition a user is then advantageously prevented from incorrectly using the two earphones of a binaural hearing system in an interchanged manner.

In principle, however, an embodiment is also possible in such a way that more than two handset types are distinguished by means of the phase measurement, in that the handset types accordingly generate more than two different phase differences and recognize them.

The generation of different phase differences by listeners of different types of listeners can be realized in different ways, as will be explained in more detail below.

In a suitable embodiment, the receiver has two signal contacts, and the receiver can be connected to and preferably also connected to a hearing device of the hearing system by means of the signal contacts. The receiver and especially the two signal contacts are thus designed to be protected against polarity reversal. A first handset type and a second handset type of the plurality of handset types now differ from one another in that they are designed to be reverse polarity-proof, so that the two phase differences that are generated by a handset of the first handset type and by a handset of the second handset type are 180 ° differentiate. The signal contacts of the two handset types are thus designed to be reverse polarity-proof. One of the two handset types therefore results in an additional phase of 180 ° being impressed when the input signal is converted to the sensor signal, so that there is a corresponding phase difference relative to the other handset type. In a suitable embodiment, the first type of receiver is provided for the left side of a binaural hearing system and the second type of receiver for the right side. If one of the two listeners is wrongly connected on the other side, a phase difference is measured as part of a side detection that deviates by 180 ° from an expected phase difference, the expected phase difference being the phase difference that would be generated by the other listener.

In detail, this concept is preferably implemented as follows with two types of receiver that are designed to be reverse polarity-proof: the receiver has a signal interface for connection to a hearing aid of the hearing system. The signal interface has a first signal contact and a second signal contact. The signal contacts are each associated in particular with a specific pole of the listener, the first signal contact is then always a positive pole and the second signal contact is always a negative pole. In particular, the hearing aid has a correspondingly complementary hearing aid signal interface, which has two poles, for connecting the signal contacts, one pole per signal contact. The signal interface is now designed to be protected against polarity reversal such that one of the signal contacts can only be connected to a first pole of the hearing device and the other the signal contact can only be connected to a second pole of the hearing device and not vice versa. This is achieved, for example, by different geometries of the individual signal contacts and poles or by a corresponding plug-in contour. A first handset type and a second handset type of the plurality of handset types then differ from one another in particular in that in the first handset type the first signal contact can only be connected to the first pole and the second signal contact can only be connected to the second pole, whereas the second handset type compared to the first handset type is reversed in polarity such that, conversely, the first signal contact can only be connected to the second pole and the second signal contact can only be connected to the first pole. In the case of one type of handset, the positive pole is also connected to a positive pole on the hearing aid and, accordingly, a negative pole on the handset is connected to a negative pole on the hearing aid, and in the other handset a negative pole is connected to a positive pole. In general, it is advantageously achieved that the two phase differences, which are generated by the two types of listeners, differ by 180 ° if they are connected on the same side, that is to say on the same hearing aid signal interface.

In a first suitable variant, the electrical input signal is supplied to the listener via the signal contacts, and the sensor is arranged outside the listener and independently of the listener. The polarity reversal is thus realized that the transmission of the input signal to the listener is polarity reversed, so that, in principle, the secondary signal generated by a listener of the first handset type then has an opposite sign with respect to the secondary signal generated by a listener of the second handset type. The phase difference for identifying the listener is thus generated in particular when the input signal is transferred to the listener, ie the ID phase is impressed when the input signal is transferred to the listener and thus at the beginning of the transfer path. The sensor then generates a corresponding sensor signal depending on the secondary signal. In this variant, the listeners themselves are designed to be reverse-polarized.

For optimum hearing comfort, especially in the first variant in normal hearing operation, or hearing operation for short, the input signal is preferably passed to the listener on the one side with the opposite sign, so that the secondary signals on both sides are then no longer opposed, but in particular in phase. The original input signal is then expediently used to identify the listener in order to be able to generate secondary signals correspondingly in phase opposition, so that the two types of listeners can then be distinguished and also differentiated.

In a second suitable variant, on the other hand, it is not the listeners themselves who are polarized with respect to the input signal, but rather the sensors on both sides of the hearing system. The sensor is expediently integrated into the receiver and firmly connected to it, so that the sensor and the receiver together form in particular an inseparable assembly. This applies accordingly to both sides of a binaural hearing system, with a binaural hearing system generally also having two sensors, namely one for each of the two listeners. In the second variant, the sensor signal is now transmitted via the signal contacts and not the input signal. However, the above explanations for the first variant also apply mutatis mutandis to the second variant, in which the input signals and also the secondary signals are now basically in phase, but in which the sensor signals are in phase opposition. The phase difference for identifying the listener is thus when the sensor signal is generated, generated more precisely when the sensor signal is transferred to the control unit, ie the ID phase is impressed on the sensor signal and thus at the end of the transfer path. This has the particular advantage that the input signal need not be manipulated for normal hearing.

In the second variant, the listener has in particular two signal interfaces, a polarized signal interface for the sensor signal and a further, non-polarized signal interface for the input signal. In contrast, the listener in the second variant has only one signal interface, namely for the input signal, and otherwise no further signal interfaces.

In the second variant in particular, the sensor is connected to the receiver in such a way that it cannot be separated if handled properly. The sensor is thus permanently and clearly assigned to the listener. The sensor is therefore designed in particular as a component of the receiver. This ensures that the correct sensor is always connected to the associated handset, since identification of the same is not possible based on the handset alone. This is because the sensor and, more specifically, its special polarity reversal is used. To integrate the sensor into the handset, the sensor is attached to the handset, e.g. glued to it, poured into a housing of the receiver or part of the receiver itself.

Basically, a variety of different concepts are suitable for phase measurement. An important point here is in particular that a sensor signal is generated which is connected to the input signal via a transfer function and that an additional phase difference is added when the sensor signal is generated from the input signal, i.e. an additional phase is impressed, which one or which then is used to identify the listener. This phase is therefore referred to as the ID phase, as already described above. In principle, however, all types of secondary signals and a wide variety of sensors are suitable for measuring them. Some preferred combinations of secondary signal and sensor are explained in detail below. The variants mentioned can also be combined with one another.

In a preferred embodiment, the secondary signal is a sound signal which is generated by the listener when the sound is output, and the sensor is a microphone which picks up the sound signal. A microphone of the hearing system is advantageously used as the sensor, in particular a microphone which is part of a hearing device of the hearing system and which is used in a hearing mode to record noises from the environment in order to subsequently amplify them and output them via the receiver of the hearing device. However, e.g. a microphone worn by the user when used as intended, in particular a structure-borne sound microphone, or alternatively an additional microphone. The secondary signal is in particular a sound signal that is generated anyway for output to the user. This is usually modified further by reflections, self-modes and diffractions in the auditory canal of the user before it is picked up by the sensor.

In a further preferred embodiment, the secondary signal is a magnetic field, which is generated by the listener when the sound is output, and the sensor is a magnetic field sensor, which measures the magnetic field. This variant is based on the consideration that a listener generates a magnetic field, which depends on the electrical input signal, so that an additional phase difference can be recognized particularly well when compared with the input signal. The sensor is suitably a Hall sensor, a coil or a telephone coil that is already present in a hearing aid of the hearing system, also referred to as a T-coil.

In a further preferred embodiment, the secondary signal is a vibration, which is generated in particular at least indirectly by the listener when the sound is output, and the sensor is a vibration or acceleration sensor which picks up the vibration. A vibration sensor differs from a microphone in particular in that a vibration sensor is not excited directly by a sound signal, but rather measures vibration, ie mechanical acceleration, in particular of the surrounding environment or the surrounding components or of both. For example, the sensor measures then during the sound output a vibration of the handset or more precisely a housing of the handset. In a suitable embodiment, a vibration or acceleration sensor comprises an oscillating test mass which is excited accordingly by sound or vibration or both, so that the vibration or acceleration sensor then generates a sensor signal which is dependent on the input signal.

In particular, it should be noted that a suitable sampling rate for the sensor is used to measure the phase difference as reliably as possible. The input signal usually has a frequency spectrum in the range audible to normal hearing, in particular 20 Hz to 20 kHz, so that the secondary signal also lies in this frequency range accordingly. The sampling rate for the sensor is therefore expediently chosen such that the sensor signal also reproduces such frequencies. In particular, an acceleration sensor is typically operated with a sampling rate of only a few measured values per second, that is to say well below 20 Hz, when used as intended. To measure the secondary signal, a sampling rate between 40 Hz and 40 kHz is then expediently generally selected for the sensor.

In principle, any signal can be used as the input signal, in particular also any sound signal recorded and converted in the listening mode from the environment or, alternatively or additionally, an electrical audio signal. However, in order to identify the listener as early and advantageously as possible outside of the regular hearing mode, the electrical input signal in a practical embodiment is a start signal, which when switched on, i.e. is played when the hearing system is started up. As a result, the listener is identified before an actual hearing operation. The start signal is preferably a start melody, which is played when the hearing system is switched on and for the acoustic display of the start-up.

Alternatively or additionally, the listener is advantageously identified in the context of an open-loop gain measurement of the hearing system. This open loop gain measurement is also referred to as calibration operation and, more precisely, is a calibration operation for calibrating a maximum amplification of the hearing aid, which usually depends on the respectively existing and possibly changing environmental conditions. Here, the hearing system therefore has a gain control, which is calibrated in the calibration mode by using a test signal as the input signal, whereby a calibration signal is generated in order to set the maximum gain of the hearing system. The calibration signal is in particular a microphone signal, so the test signal is output and resumed in order to characterize the environment. In combination with the test signal, the calibration signal then serves in particular to determine, in particular to estimate, the transmission function from the hearing aid of the hearing system to the eardrum of the user, and to set the maximum amplification as a function thereof. The calibration signal is now advantageously also used as a sensor signal, ie the calibration signal is the sensor signal. In this respect, this embodiment is similar to the embodiment described above with the sound signal as a secondary signal and the microphone as a sensor. The identification of the listener is then advantageously carried out parallel to the open-loop gain measurement, so that the outlay in terms of apparatus and control technology for identifying the listener is minimal, since the same calibration signal is used for both purposes. The measurement described is also not limited to a special calibration operation, but is carried out in an advantageous embodiment during operation, in particular during normal operation. The measurement is preferably carried out adaptively. The phase is then advantageously continuously determined during the running time of the hearing system, ie recurring. For this purpose, the sensor is connected in particular to a suitable signal processing block, which estimates the transfer function. The signal processing block is preferably part of the control unit.

In addition to identifying the listener by means of the phase measurement, a performance class of the listener is preferably also determined by means of an amplitude measurement, the amplitude measurement preferably being carried out with the sensor. The amplitude measurement is in particular a measurement of an amplitude frequency response. The listener thus has a performance class, which by an additional amplitude measurement is determined, which is carried out in particular at the same time as the phase measurement. The performance class is suitably defined by a transmission behavior of the listener, ie in particular by an amplitude frequency response which is assigned to a specific performance class. As a result, the performance class of the listener is then determined by measuring the amplitude, ie by measuring the amplitude.

Alternatively or additionally, in a suitable embodiment, in addition to identifying the listener by means of the phase measurement, a performance class of the listener is also determined by means of an impedance measurement. The listener thus has a performance class which is determined by an additional impedance measurement, which is carried out in particular at the same time as the phase measurement. The performance class is suitably defined by an electrical resistance of the handset, i.e. An electrical resistance is integrated into the receiver, which has a specific resistance value which is assigned to a specific power class. This then determines the performance class of the listener by measuring the resistance.

Particularly advantageous in the case of power class detection as described above is an embodiment in which the phase measurement is used for side detection, so that a listener is then assigned to a power class on the one hand by means of an amplitude or resistance measurement and on the other hand by a phase measurement of one side of the hearing system. The listener is then identified in two dimensions, so to speak, one with regard to the performance class and one with respect to the side. In this respect, a handset type is therefore characterized by two parameters, namely by a first parameter "performance class" and a second parameter "side".

A particular advantage in determining the performance class is, in particular, that with the same measurement, also referred to as the measurement routine, the phase difference can also be measured at the same time, ie the phase measurement is generally part of the measurement routine, so that the performance class and the Side can be determined simultaneously with a single measurement and expediently also be determined.

The phase measurement is preferably carried out at a frequency of at most 500 Hz. This is based in particular on the observation that the phase difference can be determined better at low frequencies than at high frequencies, since signals at high frequencies are more susceptible to interference. At higher frequencies, interferences from e.g. the individual geometry of the user's ear or the selected length of a sound tube of a hearing aid of the hearing system. Basically, the entire acoustic frequency range can be considered for measurement, but low frequencies, i.e. Frequencies of at most 500 Hz, enable particularly reliable measurements. However, the phase measurement is preferably carried out at least at a frequency of 20 Hz. The sampling rate of the sensor is expediently adapted to the frequency and preferably corresponds to at least twice the frequency.

A hearing system according to the invention is designed to carry out the method described above and, in particular, has a control unit for this purpose. In a suitable embodiment, the control unit is integrated in a hearing device of the hearing system. In a variant that is also suitable, the control unit is designed as a separate part of the hearing system.

Fig. 1

ein binaurales Hörsystem

Fig. 2

eine schematisierte Darstellung des Hörsystems aus Fig. 1,

Fig. 3a, 3b

eine erste Variante eines Hörsystems,

Fig. 4a, 4b

eine zweite Variante eines Hörsystems,

Fig. 5a, 5b

eine dritte Variante eines Hörsystems.

An exemplary embodiment of the invention is explained in more detail below with reference to a drawing. Each shows schematically:

Fig. 1

a binaural hearing system

Fig. 2

a schematic representation of the hearing system Fig. 1 .

3a, 3b

a first variant of a hearing system,

4a, 4b

a second variant of a hearing system,

5a, 5b

a third variant of a hearing system.

In the Fig. 1 A binaural hearing system 2 is shown, with or two hearing aids 4, which are each worn by a user in or on the ear. However, the following explanations can also be applied analogously to a hearing system 2 with only one hearing device 4. In the exemplary embodiment shown, a respective hearing device 4 has a receiver 6 for sound output, which is either inserted into the ear or worn outside the ear, depending on the hearing device type. In the present case, a so-called RIC hearing device is shown by way of example, in which the receiver 6 is worn in the ear and is connected to the rest of the hearing device 4 via an electrical connection 8.

The hearing system 2 shown is generally used to amplify sound signals from the environment, with the aim of compensating for a hearing loss of the user that is deficient. For this purpose, the hearing system 2 is individually adapted and adjusted to the user in order to meet their individual hearing ability and to compensate for the individual hearing impairment. In a variant not shown, the hearing system 2 is generally headphones.

An essential component of a hearing system 2 is the receiver 6, which is used for sound output and is available in a large number of variants. Depending on the hearing ability, a suitable receiver 6 is selected and used in the hearing system 2. The hearing system 2 is now designed such that the risk of confusing the receiver 6 is reduced, i.e. the risk of incorrectly using a receiver 6 of a receiver type that is not intended for the user. For this purpose, a method is carried out by means of which the receiver 6 is identified, i.e. is assigned to one of several handset types. In the present case, the method is carried out by a control unit 10, which is part of the hearing system 2 and is accommodated in one of the hearing aids 4.

The procedure is based on Fig. 2 explained in more detail in which one of the hearing aids 4 Fig. 1 is shown very schematically as a circuit diagram. Basically is the hearing system 2 is initially designed such that a microphone 12 picks up sound signals 100 from the surroundings and converts them into a microphone signal 102. This is forwarded to the control unit 10 and amplified there. The control unit 10 thus generates an amplified microphone signal, which is an electrical input signal 104, which is passed on to the receiver 6 for output. The receiver 6 converts the input signal 104 as part of a sound output into a sound signal 106, which is output to the user. In the present case, the receiver 6 also generates a magnetic field 108 due to the principle. The sound signal 106 and the magnetic field 108 are therefore dependent on the input signal 104, which is also referred to as the primary signal 110. Therefore, the sound signal 106 and the magnetic field 108 are also referred to as secondary signal 112. Other secondary signals 112, not shown, are, for example, a vibration generated during the sound output or an acceleration.

The method now serves to identify the receiver 6, which belongs to one of several different receiver types. At least one of the secondary signals 112 is now detected by a sensor 14, which generates an electrical sensor signal 114 as a function of the secondary signal 112. The dependency of the sensor signal 114 on the input signal 112 is determined in particular by a transfer function T, which does not necessarily have to be known and which describes the change which the input signal 104 undergoes during the conversion into the sensor signal 114 along a transfer path. Accordingly, in Fig. 2 two transfer functions T for the two transfer paths indicated by arrows, namely once from receiver 6 to sensor 14 and once from receiver 6 to microphone 12, which can also be used as sensor 14. In the present case, the control unit 10 also carries out a phase measurement by determining a phase difference between the input signal 104 and the sensor signal 114. The receiver 6 is then assigned to one of the several receiver types on the basis of the phase difference and thereby identified.

The receiver 6 is connected to a receiver connection 16 of the hearing system 2, the input signal 104 being transmitted to the receiver 6 via the receiver connection 16 becomes. The earphones 6 of different earphone types are now designed such that they cause different phase differences at the same earphone connection 16 and for the same input signal 104. The phase measurement therefore results in different phase differences for different types of listeners. Different listeners 6 of the same listener type, however, also result in the same phase difference. In principle, a so-called transfer phase difference may already result due to the transfer function T between the input signal 104 and the sensor signal 114. In order to identify the receiver 6, an identification phase difference, or ID phase difference for short, is now added in addition to the transfer phase difference depending on the receiver type , Overall, different phase differences also result for different types of listeners with the same transfer path. Along the transfer path T, an additional phase for identification, ie an identification phase or ID phase, is thus impressed, which is then present in the sensor signal 114 in addition to a possible transfer phase difference due to the transfer path T itself. The ID phase can generally be stamped at different points along the transfer path.

In Fig. 1 A variant is shown in which the secondary signal 112 is a sound signal 106, which is generated by the receiver 6 when the sound is output. Here, the sensor 14 is the microphone 12, which is used in a hearing mode to pick up noises from the environment in order to subsequently amplify them and output them via the receiver 6 of the hearing device 4. Alternatively, another microphone is used.

Also in Fig. 1 a variant is shown in which the secondary signal 112 is a magnetic field 108 which is generated by the receiver 6 when the sound is output. The sensor 14 is a magnetic field sensor, which measures the magnetic field 108. The sensor 14 is, for example, a Hall sensor, a coil or a telephone coil of the hearing device 4, also referred to as a T-coil.

Another variant is not shown, in which the secondary signal 112 is a vibration, which in particular is at least indirectly transmitted by the receiver 6 Sound output is generated, in which case the sensor 14 is a vibration sensor which picks up the vibration. Also not shown is a variant in which the secondary signal 112 is an acceleration which is generated at least indirectly by the sound output, the sensor 14 then being an acceleration sensor which measures the acceleration.

The variants shown and not shown can also be used individually or combined as desired.

The method is used in the present case to determine whether a receiver 6, which belongs to a type of receiver, which is also intended for use on this side, is also connected to a respective side of the binaural hearing system 2. A first of the several handset types is then a left handset, which is intended for use on the left side of the hearing system 2, and a second of the several handset types is a right handset, which is intended for use on the right side of the hearing system 2. A side recognition is then carried out within the scope of the method in that the listener 6 is identified as a left hand listener or as a right hand listener on the basis of the phase difference.

In the 3a, 3b, 4a, 4b and 5a, 5b illustrates how the generation of different phase differences can be realized by listeners 6 of different types of listeners. The show 3a and 3b a first variant, the 4a and 4b a second variant and the 5a and 5b a third variant. In all variants, the receiver 6 can be connected to a hearing device 4 of the hearing system 2 with reverse polarity protection and is thus designed to be protected against reverse polarity. The first type of listener, each in the 3a, 4a and 5a shown, and the second type of listener, each in the 3b, 4b and 5b shown, differ from one another in that they are designed to be reverse polarity-proof so that the two phase differences, which are generated by a receiver 6 of the first receiver type and by a receiver 6 of the second receiver type, differ by 180 °. One of the two handset types therefore results in an additional phase of 180 ° being impressed when the input signal 104 is converted to the sensor signal 114 is, so that there is a corresponding phase difference relative to the other handset type. In the present case, the first handset type is provided for the left side of the binaural hearing system 2 and the second handset type is provided for the right side. If one of the two earphones 6 is now wrongly connected on the other side, a phase difference is measured as part of a side detection, which differs by 180 ° from an expected phase difference, the expected phase difference being the phase difference that is generated by the other earphone 6 would.

In the exemplary embodiments shown, this concept is implemented, for example, as follows with two types of listeners that are designed to be reverse-polarity-proof: the listener 6 has a signal interface 18 for connection to one of the hearing aids 4, more precisely to the handset connection 16, which therefore has a correspondingly complementary hearing aid signal interface is. The signal interface 18 has a first signal contact 20 and a second signal contact 22. The hearing device 4, more precisely the receiver connection 16, now has two poles 24, 26 for connecting the signal contacts 20, 22. The signal interface 18 is now designed to be protected against polarity reversal, that one of the signal contacts 20, 22 can only be connected to a first pole 24 of the hearing device and the other of the signal contacts 20, 22 only to a second pole 26 and not vice versa. This is, for example, as in the 3a, 3b, 4a, 4b . 5a, 5b shown realized by different geometries of the individual signal contacts 20, 22 and poles 24, 26. The first handset type and the second handset type then differ from one another in that, in the first handset type, the first signal contact 20 can only be connected to the first pole 24 and the second signal contact 22 can only be connected to the second pole 26, whereas the second handset type is different from the first handset type is reversed in polarity so that, conversely, the first signal contact 20 can only be connected to the second pole 26 and the second signal contact 22 can only be connected to the first pole 24. This ensures that the two phase differences that are generated by the two types of receiver , by 180 ° if they are connected on the same side, that is to say on the same hearing aid signal interface 18.

With one type of handset in 3a, 4a and 5a the first signal contact 20 is a positive pole and can be connected to the first pole 24, which is also a positive pole. The second signal contact 22 is a negative pole and can be connected to the second pole 26, which is also a negative pole. At the in 3b, 4b and 5b shown the other type of receiver, the first signal contact 20 is also a positive pole but vice versa 3a, 4a and 5a connectable to the second pole 26, which is now a negative pole. The second signal contact 22 is then a negative pole and can be connected to the first pole 24, which is now a positive pole. The listeners 6 of the 3a and 3b are polarized against each other. The two in the 3a and 3b Handset 6 shown also form together a handset set. Both apply accordingly to the two listeners 6 4a and 4b and for the two listeners 6 the 5a and 5b ,

The variant of 3a, 3b is now characterized by the fact that the electrical input signal 104 is fed to the receiver 6 via the signal contacts 20, 22 and that the sensor 14 is arranged outside the receiver 6 and independently of it, here as part of the hearing device 4. The polarity reversal is thus thereby realizes that the transmission of the input signal 104 to the receiver 6 is polarized, so that, in principle, the secondary signal 112, which is transmitted by the receiver 6 of the first receiver type Fig. 3a is generated with respect to the secondary signal 112, which is generated by a receiver 6 of the second receiver type in Fig. 3b is generated, has an opposite sign. The phase difference for identifying the receiver 6 is thus generated when the input signal 104 is transferred to the receiver 6 and thus at the beginning of the transfer path.

In contrast, the second variant of the 4a, 4b it is not the earphones 6 which are polarity reversed with respect to the input signal 104 itself, but the sensors 14 on both sides of the hearing system 2. The respective sensor 14 is integrated in the respective earpiece 6 and is permanently connected to it and forms an inseparable assembly with it as shown. The sensor signal 114 is now transmitted via the signal contacts 20, 22 and not the input signal 104. The phase difference for identifying the receiver 6 is thus generated when the sensor signal 114 is generated, more precisely when the sensor signal 114 is transferred to the control unit 10 generated, ie at the end of the transfer path. The input signal 104 is transmitted separately to the receiver 6 via an additional signal line with two additional signal contacts 28, 30. These signal contacts 28, 30 for the input signal 104 are then not reversed in polarity in the case of different handset types. Different types of listeners are therefore always connected in phase with respect to the input signal 104 and, in particular, are always connected in phase regardless of the side. Overall, the receiver 6, especially its signal interface 18, points into the 4a, 4b that is, four signal contacts 20, 22, 28, 30 open, two signal contacts 28, 30 for the input signal 104 and two further signal contacts 20, 22 for the sensor signal 114.

The 5a and 5b now show a combination of the two variants of 3a, 3b and 4a, 4b , In the 5a, 5b the two types of listeners are polarity reversed with respect to the input signal 104, ie as in the variant of FIG 3a and 3b educated. In contrast to the variant of the 3a, 3b is however in the variant of 5a, 5b the sensor 14 is integrated into the receiver 6, as in the variant of FIG 4a, 4b , With regard to sensor signal 114, the handset types are according to the variant 5a, 5b however, not reverse polarity, but always in the correct phase. The variant of 5a, 5b is based on the variant of 3a, 3b , wherein the sensor 14 is now integrated in the respective receiver 6.

In principle, any signal can be used as input signal 104, e.g. Alternatively or in addition to the amplified microphone signal 102, an electrical audio signal can also be used. In a variant not shown, a start signal is used as input signal 104, which when switched on, i.e. is played when the hearing system 4 is started up and is generated, for example, by the control unit 10 or is stored therein. As a result, the receiver 6 is identified even before actual hearing operation.

In a variant, also not shown, the receiver 6 is identified in the context of an open-loop gain measurement of the hearing system 4. This open-loop gain measurement is also referred to as a calibration operation and, more precisely, is a calibration operation for calibrating a maximum gain of the hearing device 4, which is usually dependent on the particular present and possibly depends on changing environmental conditions. The hearing system 2 thus has a gain control, which is calibrated in the calibration mode by using a test signal as the input signal 104, as a result of which a calibration signal is generated in order to set the maximum gain of the hearing system 4. In combination with the test signal, the calibration signal is used in particular to determine the transfer function from the receiver 6 of the hearing system 4 to the eardrum of the user and to set the maximum amplification as a function thereof. The calibration signal is then also used as sensor signal 114. Alternatively or additionally, the measurement described takes place adaptively during operation and not or not exclusively during calibration operation.

In a variant not shown, in addition to identifying the receiver 6 by means of the phase measurement described, a performance class of the receiver 6 is also determined by means of an impedance measurement or by means of an amplitude measurement or both. The power class is defined, for example, by an electrical resistance of the receiver 6, ie an electrical resistance is integrated in the receiver 6, for example similar to the sensor 4 in FIGS 4a, 4b , The resistance has a specific resistance value, which is assigned to a specific power class, so that the power class of the receiver 6 is determined by measuring the resistance.

LIST OF REFERENCE NUMBERS

2

hearing

4

hearing Aid

6

receiver

8th

connection

10

control unit

12

microphone

14

sensor

16

jack

18

Signal interface

20, 22

signal contact

24, 26

pole

28, 30

signal contact

100

sound signal

102

microphone signal

104

input

106

sound signal

108

magnetic field

110

primary signal

112

secondary signal

114

sensor signal

T

transfer function

Claims (15)

Method for identifying a receiver (6) of a hearing system (2),
the listener (6) belonging to one of several listener types,
an electrical input signal (104) being fed to the receiver (6) for sound output,
wherein the input signal (104) is a primary signal (110) and, based on the sound output, a secondary signal (112) is generated which is dependent on the input signal (104),
wherein the secondary signal (112) is detected by a sensor (14) which generates an electrical sensor signal (114) depending on the secondary signal (112),
wherein a phase measurement is carried out by determining a phase difference between the input signal (104) and the sensor signal (114),
wherein the handset (6) is identified by assigning the handset (6) to one of the several handset types based on the phase difference. Method according to claim 1,
the hearing system (2) being binaural,
wherein a first of the plurality of handset types is a left handset, which is intended for use on the left side of the hearing system (2), a second of the plurality of handset types is a right handset, which is intended for use on the right side of the hearing system (2) A side recognition is carried out by identifying the listener (6) as a left listener or as a right listener based on the phase difference. Method according to one of claims 1 to 2,
the receiver (6) having two signal contacts (20, 22),
wherein the receiver (6) can be connected to a hearing device (4) of the hearing system (2) by means of the signal contacts (20, 22) so that they are protected against polarity reversal,
whereby a first type of handset and a second type of handset of the plurality of handset types differ from one another in that they are designed to be reverse polarity-proof, so that the two phase differences differ from one handset (6) of the first handset type and one handset (6) of the second handset types are generated, differ by 180 °. Method according to claim 3,
the electrical input signal (104) being fed to the receiver (6) via the signal contacts (20, 22),
the sensor (14) being arranged outside the receiver (6) and independently of the receiver (6). Method according to claim 3,
the sensor (14) being integrated in the receiver (6) and being firmly connected to it,
wherein the sensor signal (114) is transmitted via the signal contacts (20, 22). Method according to one of claims 1 to 5,
wherein the secondary signal (112) is a sound signal (106) which is generated by the listener (6) when the sound is output,
wherein the sensor (14) is a microphone (12) which picks up the sound signal (106). Method according to one of claims 1 to 6,
wherein the secondary signal (112) is a magnetic field (108) which is generated by the receiver (6) during the sound output,
wherein the sensor (14) is a magnetic field sensor which measures the magnetic field (108). Method according to one of claims 1 to 7,
wherein the secondary signal (112) is a vibration which is generated by the receiver (6) when the sound is output,
the sensor (14) being a vibration sensor or an acceleration sensor which receives the vibration. Method according to one of claims 1 to 8,
the electrical input signal (104) being a start signal which is played when the hearing system (4) is switched on. Method according to one of claims 1 to 9,
wherein the hearing system (2) has a gain control which is calibrated in a calibration operation by using a test signal as the input signal (104), whereby a calibration signal is generated in order to set a maximum amplification of the hearing system (2),
wherein the calibration signal is also used as the sensor signal (114). Method according to one of claims 1 to 10,
the receiver (6) having a performance class which is determined by an additional amplitude measurement with the sensor (14), which is carried out in particular at the same time as the phase measurement. Method according to one of claims 1 to 11,
the receiver (6) having a power class which is determined by an additional impedance measurement, which is carried out in particular at the same time as the phase measurement. Method according to one of claims 1 to 12,
the phase measurement being carried out at a frequency of at most 500 Hz. Hearing system (2) which is designed to carry out a method according to one of claims 1 to 13. Handset, which is designed for use in a method according to any one of claims 1 to 13.

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