Near-field magnetic induction wireless communication system with dynamic change of transmission power

Abstract

A hearing system includes at least three devices, at least two of which are hearing aid devices. The at least three devices are configured to wirelessly communicate with each other via a near-field magnetic induction wireless link based on a predetermined communication protocol. The predetermined communication protocol defines a frame including at least a first time slot and a second time slot. A first pair of devices among the at least three devices is configured to communicate in a first time slot, and a second pair of devices among the at least three devices is configured to communicate in a second time slot. The first pair of devices transmits at a first transmission power level in the first time slot, and the second pair of devices is configured to transmit at a second transmission power level different from the first transmission power level in the second time slot. In particular, the hearing system may be a hearing aid system, and the devices of the hearing aid system are worn at the ears of a user.

Description

Technical Field

[0001] The present invention relates to hearing device systems, in particular to hearing device systems comprising spatially separated devices communicating via a near-field magnetic induction link and a corresponding communication method for a hearing device system. Background Art

[0002] Hearing device systems are generally well known.A hearing device system may include a hearing aid system that provides hearing loss compensating sounds into an ear canal of a user of the hearing aid system.

[0003] Other examples for hearing device systems are headphones, which do not perform hearing loss compensation, but provide sound from a source device (eg a mobile phone or a radio receiver) into the ear canal.

[0004] Radio device systems often include multiple devices, each device having a separate housing, and each device being arranged at a different location on the user, particularly around the user's head.

[0005] The hearing device system acting as a hearing aid system may include two devices worn behind the auricle of each ear of the user. These devices have a behind-the-ear (BTE) housing that is specially shaped to be worn behind the auricle and accommodates electronic components such as microphones, amplifiers, and microcontrollers / signal processors for providing hearing loss compensation. Output transducers (such as miniature loudspeakers or receivers) may be arranged in the external auditory canal as receivers in the ear (RIE) that feed hearing loss compensation sounds to each ear canal of the user. These output transducers may be surrounded by specially shaped in-ear housings, earpiece shells, or ear molds for insertion into the external auditory canal of the user.

[0006] Auxiliary devices that provide, for example, an interface for a hearing aid system to external devices are also known in the art. These external devices may include televisions, mobile phones, digital audio players, streaming devices, programming devices, test equipment, external microphone arrays, etc. Some auxiliary devices may be arranged in a so-called "piggyback" housing that houses the electronic circuitry that provides the interface capability and is specifically adapted to mate with the end of a BTE housing of another device of the hearing device system. Such "piggyback" housings are often referred to as "boots", "pickup audio boots" or "audio shoes".

[0007] Such a modular system configuration is advantageous in terms of convenience to the user and gives additional upgrade capabilities to providers of hearing device systems.

[0008] A hearing device system includes multiple devices and requires communication capabilities between the multiple devices. Some communications between devices are one-way, but some other devices even require two-way communication.

[0009] Direct communication via wired communication, for example using a cable between the BTE housing and the in-ear housing or using physical connectors placed directly adjacent at the BTE housing and the attached backpack housing, is well known in the art.

[0010] However, in particular physical connectors with multiple contacts and external cables require space, which increases manufacturing costs, and are susceptible to wear and damage. These issues are related to the number of separate devices and required inter-device communication links that a hearing device system may include.

[0011] A known method of improving communication between hearing aid devices is to use wireless communication and in particular near field magnetic induction (NFMI). This method is similar to a conventional induction loop. In a known hearing aid system, the two hearing aid devices of a binaural hearing aid system communicate via near field magnetic induction, providing the convenience of synchronized volume adjustment memory and the benefits of binaural signal processing between the two hearing aid devices.

[0012] Typically, the communication protocol for a hearing device system using NFMI communication uses a time division technique for implementing bidirectional communication between each pair of independent devices. Each communication link between two devices allocates a time slot for the communication direction from the first device to the second device, and vice versa. For each communication link between two devices, two time slots are provided by the communication protocol. The number of required time slots increases with the number of communication links between more and more devices of the hearing device system.

[0013] However, using time division multiplexing reduces the advantages of the modular approach because the communication bandwidth and accordingly the data rate of the independent communication channel between the two devices is reduced.

[0014] Thus, prior art hearing device systems consisting of multiple devices linked using an inter-device communication link based on near-field magnetic induction may be amenable to improvement. Summary of the invention

[0015] A hearing device system and a communication method for a hearing device system according to independent claim 1 provide an advantageous solution to the above described problem.

[0016] The dependent claims define further advantageous embodiments.

[0017] A hearing device system comprises at least three devices, in particular at least three devices, two or more of the at least three devices are hearing aid devices, for example, forming a binaural hearing aid system. The at least three devices are configured to wirelessly communicate with each other via a near-field magnetic induction wireless link based on a predetermined communication protocol. The predetermined communication protocol defines a frame including at least a first time slot and a second time slot. At least a first pair of devices among the at least three devices is configured to communicate in the first time slot, and at least a second pair of devices among the at least three devices is configured to communicate in the second time slot. The first pair of devices is configured to transmit at a first transmission power level in the first time slot, and the second pair of devices is configured to transmit at a second transmission power level different from the first transmission power level in the second time slot.

[0018] In some embodiments, one of the at least three devices is included in both the first pair of devices and the second pair of devices. In some of such embodiments, when the hearing device system is worn by the user, a first distance between devices in the first pair of devices is greater than a second distance between devices in the second pair of devices.

[0019] The first pair of devices and the second pair of devices may be configured for use in a configuration where the first distance is greater than the second distance. This is the case, for example, when the first pair of devices is a pair of hearing aid devices configured to be worn in or at respective ears of a hearing aid user and when the second pair of devices comprises one of the hearing aids and an auxiliary device (such as an audio shoe) associated with the one of the hearing aids.

[0020] Also, the first transmission power level is preferably greater than the second transmission power level. Also, in some of such embodiments, the second transmission power level is preferably so weak that it does not cause noticeable interference at about the first distance or longer than the first distance.

[0021] Some embodiments of a hearing device system comprise a first hearing aid device, a second hearing aid device, a first auxiliary device (such as a first audio shoe) adapted to wirelessly communicate with the first hearing aid device, and a second auxiliary device (such as a second audio shoe) adapted to wirelessly communicate with the second hearing aid device.

[0022] In some of such embodiments, when the hearing aid system is worn by the user, the respective distances between the first hearing aid device and the first auxiliary device and the second hearing aid device and the second auxiliary device are shorter than the distance between the first hearing aid device and the second hearing aid device. In some of such embodiments, the first pair of devices includes the first hearing aid device and the second hearing aid device, and the second pair of devices includes the first hearing aid device and the first auxiliary device. In some embodiments, the third pair of devices includes the second hearing aid and the second auxiliary device. The third pair of devices is configured to transmit at a third transmission power level different from the first transmission power level in the second time slot. Each of the second transmission power level and the third transmission power level is weaker than the first transmission power level. An advantage of the latter hearing device system is that the first hearing aid device and the second hearing aid device can communicate with each other in the first time slot using the first transmission power level, and can communicate with their respective auxiliary devices in the second time slot using the second transmission power level and the third transmission power level, while avoiding crosstalk between the two communication channels of the first hearing aid device and the first auxiliary device, and in the second time slot, because the second transmission power level and the third transmission power level are too weak to cause substantial interference between the two communication channels.

[0023] Using different power levels for the near-field magnetic induction wireless link between the first pair of devices and the second pair of devices enables the use of a suitable transmission power level, which is adapted to the spatial arrangement of the devices in question relative to each other when worn by the user in the first pair of devices, and the spatial arrangement of the devices in the second pair of devices relative to each other. Instead of the static transmission power level of the known near-field magnetic induction wireless link between hearing aid devices, the claimed hearing device system allows the use of a reduced transmission power level when a pair of devices are close. Therefore, the power consumption of the hearing device system of the present invention is reduced when compared to the prior art.

[0024] Also, because the reduced transmission power levels now possible reduce or even eliminate interference and / or crosstalk between transmitters and receivers arranged at opposite sides of the user's head, the present hearing device system has the additional benefit of allowing wireless near-field magnetic induction communications to occur simultaneously on the same frequency over different near-field magnetic induction wireless links.

[0025] As in a frequency division multiple access system, there is no need to use different frequencies for different communication channels, which results in a more efficient use of the available spectrum. Thus, in an embodiment of the present invention, the transmissions in the first time slot and the second time slot may be done on substantially the same frequency (e.g. on the same channel or frequency band). This feature allows the hearing device system to transmit in the first time slot and the second time slot on a channel that is subject to minimal interference and reflections from external sources (i.e. the user and the user's own current environment). At the same time, interference between devices of the hearing device system due to different transmission power levels is avoided.

[0026] Even more advantageously, it is not necessary to envisage more time slots in the communication protocol to ensure sufficient separation between different communication channels between different pairs of devices, so that an increase in the communication bandwidth and thus the data transfer rate between the devices is achieved by the present hearing device system.

[0027] According to a preferred embodiment, at least one first device of the at least three devices of the hearing device system comprises a control circuit. The control circuit is configured to select the first transmission power level and / or the second transmission power level based on the received type identifiers of at least two second devices of the at least three devices. Additionally or alternatively, the control circuit is configured to select the first transmission power level and / or the second transmission power level based on a dynamic evaluation of the communication link quality of the corresponding near-field magnetic induction wireless link to each of the second devices of the at least three devices.

[0028] By exchanging device type identifiers between the first device and the second device, for example during an initial pairing session, the spatial arrangement of the devices of the hearing device system may be conveniently determined. Thereby, a suitable transmission power level of the required near-field magnetic induction wireless link may be determined without requiring more complex transmission quality measurements. Thus, the implementation costs of the hearing device system are advantageously low, while fully realizing the benefits over the prior art.

[0029] The hearing device system according to a preferred embodiment is characterized by the following: the control circuit is configured to select the first transmission power level and / or the second transmission power level based on a dynamic evaluation of the communication link quality of the near-field magnetic induction wireless link to each of the second devices of the at least three devices by calculating the communication link quality of the communication signal received by the at least one first device from each of the at least two second devices.

[0030] Supervision of the communication link quality can be performed dynamically and simultaneously by monitoring the received communication signals over the near-field magnetic induction wireless links. This enables online monitoring of the actual quality of the communication and focusing on the actual link quality for selecting a suitable transmission power in order to achieve an acceptable quality for each link without interfering with parallel links. Adaptive or dynamic adjustment of the transmission power level becomes possible during operation of the hearing device system.

[0031] In a preferred embodiment of the hearing device system, the control circuit is configured to increase the transmission power level in case the assessed communication link quality drops below a predetermined minimum communication link quality.

[0032] Thus, a dynamic adaptation of the transmission quality of each near-field magnetic induction communication link quality is possible, even in case of sudden additional noise components in the communication channel. On the other hand, the initially selected transmission power level does not need to take into account every possible additional noise source that may or may not be encountered. Thus, an efficient power management of the hearing device system is possible. This is particularly advantageous in case of battery-operated hearing device systems.

[0033] For example, due to additional interfering RF noise sources, the electromagnetic interference (EMI) level in the surroundings of the hearing device system may suddenly increase and thus the communication link quality deteriorate. However, the adaptive nature of the transmission power level selection according to the present invention may respond by immediately adjusting (here increasing the transmission power level) such that an acceptable communication link quality is achieved at the hearing device system.

[0034] A further advantageous embodiment of the hearing device system is characterized by the control circuit being configured to reduce the transmission power level in case the assessed communication link quality exceeds a predetermined minimum communication link quality.

[0035] Thus, the first device may start the communication session at a maximum or high transmission power level, and then gradually (e.g., stepwise) reduce the transmission power level until the minimum communication link quality threshold is reached. Thus, the final selected transmission power level ensures the most efficient use of the available electrical power. This is most advantageous in the case of battery-driven devices such as hearing device systems and hearing aid systems.

[0036] Advantageously the control circuit of an embodiment of the hearing device system is configured to determine the communication link quality by calculating at least one of a packet error rate and a bit error rate of a communication signal received by the at least one first device from each of the at least two second devices via a near-field magnetic induction wireless link.

[0037] Effective assessment and evaluation of the communication link quality is possible by the control circuit determining the packet error rate, for example by using a cyclic redundancy checksum (CRC) code of received data packets or by performing a bit error rate (BER) calculation.

[0038] In a further advantageous embodiment, the hearing device system is characterized by the control circuit exchanging respective device type identifiers with at least two second devices via the first near-field magnetic induction transceiver in a pairing session.

[0039] Exchanging device type identifiers in a pairing session is an efficient way to obtain information about the distances of the individual devices of the hearing instrument system. Thus, a suitable transmission power level can be selected without requiring complex measurements or evaluations of received communication signals or the generation of specific probe signals for measuring properties of the communication channel of the near-field magnetic induction wireless link.

[0040] The control circuit of a preferred embodiment of the hearing device system is configured to control the first near-field magnetic induction transceiver to transmit an inquiry signal or a beacon signal during a pairing session, in particular at a first transmission power level. The first transmission power level is higher than the second transmission power level.

[0041] Advantageously, the hearing device system comprises at least two second devices of the at least three devices, the at least two second devices of the at least three devices being configured to transmit a response signal comprising a device type identifier for a second device type when receiving the inquiry signal and / or the beacon signal.

[0042] Preferably, one of the at least two second devices is an auxiliary device and comprises at least one of an external microphone arrangement such as a neck-worn microphone system, a wireless receiver, a mobile phone interface, a battery charging device, a remote control interface, an induction loop interface (telecoil) and an FM receiver device.

[0043] The auxiliary device may be arranged in a predefined position at a corresponding relative distance and orientation to other devices of the hearing device system. For example, the auxiliary device may be arranged directly adjacent to the first device, for example in a piggyback configuration with the first device, which may preferably be a hearing aid device. Thus, significantly lower transmission power levels will be sufficient compared to the transmission power levels required for a near-field magnetic induction wireless link between two monaural hearing devices (hearing aid devices) arranged at the left and right ear of the user, respectively. Thus, in the case of a hearing device system comprising an auxiliary device, an adaptively selected transmission power level is particularly advantageous.

[0044] The hearing device system preferably comprises at least one first device, the at least one first device being at least one of a monaural hearing aid device and a monaural headset.According to a second aspect of the invention, a hearing aid device for a hearing device system according to the first aspect solves an objective technical problem.

[0045] The hearing aid device includes a control circuit and a near-field magnetic induction transceiver. The hearing aid device is configured to communicate via the near-field magnetic induction transceiver according to a predetermined communication protocol. The predetermined communication protocol defines a frame including at least a first time slot and at least a second time slot. The control circuit is configured to control the near-field magnetic induction transceiver to transmit a first transmission signal to a second device at a first transmission power level in the first time slot, and to transmit a second transmission signal to a third device at a second transmission power level different from the first transmission power level in the second time slot.

[0046] A communication method for a hearing device system according to a third aspect of the present invention shows a hearing system, the hearing system comprising at least three devices, wherein the at least three devices are configured to wirelessly communicate with each other via a near-field magnetic induction wireless link based on a predetermined communication protocol. The predetermined communication protocol defines a frame system including at least a first time slot and a second time slot. The communication method comprises a step in which a first pair of devices among the at least three devices communicate at a first transmission power level in a first time slot, and a step in which a second pair of devices among the at least three devices communicate at a second transmission power level different from the first transmission power level in a second time slot.

[0047] The communication method for a hearing system according to the third aspect may be used with the hearing device system of the first aspect or the hearing aid device of the second aspect.Also, the hearing device system of the first aspect may comprise the hearing aid device according to the second aspect of the invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0048] The system and method according to the present invention are discussed in more detail with reference to the drawings, wherein

[0049] Figure 1 Provides an overview of the hearing system,

[0050] Figure 2 A timing diagram showing a time division multiple access scheme for a known hearing system,

[0051] Figure 3 depicts a timing diagram of a time division multiple access scheme for a hearing system according to an embodiment,

[0052] Figure 4 shows a simplified block diagram of a hearing device according to an embodiment,

[0053] Figure 5 shows a simplified block diagram of another hearing device according to an embodiment, and

[0054] Figure 6 A flow chart of a communication method for a hearing device system according to an embodiment is provided, and

[0055] Figure 7 A flow chart of a communication method for a hearing device system according to another embodiment is provided. DETAILED DESCRIPTION

[0056] In the detailed description of the drawings of various examples and embodiments of hearing device systems and corresponding communication methods, the same reference numerals refer to the same or corresponding elements. For the sake of brevity, the following discussion of the figures omits discussion of the same or corresponding elements in different figures where considered possible.

[0057] Figure 1 An overview of a hearing device system 1 is provided. The described hearing device system 1 is merely an example and comprises four individual devices 2, 3, 4, 5. Each of the devices 2, 3, 4, 5 has its own housing and is arranged at a different spatial position than each of the other devices 2, 3, 4, 5.

[0058] The hearing device system 1 is preferably a hearing aid system. The first device 2 is a left hearing aid (LHI) arranged at the left ear of a user of the hearing device system 1 . The second device 4 is a right hearing aid (RHI) arranged at the right ear of the user of the hearing device system 1 .

[0059] Thus, in a typical application scenario of the hearing device system 1 , the distance d1 between the first device 2 and the second device 4 may be approximately 0.17 m.

[0060] The third device 3 and the fourth device 5 may each be an auxiliary device in a hearing aid system. For example, the third device 3 may be a wireless audio shoe, sometimes referred to as a wireless direct audio shoe (DAI), preferably arranged in a backpack housing adjacent to the housing of the first device 2. Thus, the third device 3 is placed significantly closer to the first device 2 than the second device 4.

[0061] Thus, in a typical application scenario of the hearing device system 1 , the distance d2 between the first device 2 and the third device 3 may be approximately 0.01 m.

[0062] The fourth device 5 may be an additional auxiliary device in the hearing aid system. For example, the fourth device 5 may also be a wireless audio shoe, sometimes referred to as a wireless direct audio shoe (DAI), arranged in a backpack housing adjacent to the housing of the second device 4. Thus, the fourth device 5 is placed significantly closer to the second device 4 than the first device 2.

[0063] Thus, in a typical application scenario of the hearing device system 1 , the distance d3 between the second device 4 and the fourth device 5 may be approximately 0.01 m.

[0064] Therefore, a large difference between the distance d1 on the one hand and the distances d2, d3 on the other hand exists in the application of the head mounted hearing aid device system 1. This difference between d1 and d2, d3 may even amount to an order of magnitude or more.

[0065] Figure 1 Also depicted are necessary communication links 6, 7, 8 between devices 2, 3, 4, 5. Each of the depicted communication links 6, 7, 8 is a bidirectional communication link that enables bidirectional communication between a pair of devices 2, 3, 4, 5.

[0066] The first communication link 6 provides two communication channels for bidirectional communication between the first device 2 and the second device 4. The second communication link 7 provides another two communication channels for bidirectional communication between the first device 2 and the third device 3. The third communication link 7 provides another two communication channels for bidirectional communication between the second device 4 and the fourth device 5.

[0067] Depend on Figure 1 The first near-field magnetic induction communication unit and the second near-field magnetic induction communication unit of the device 2, device 3, device 4, and device 5, which are not shown in the figure, provide each communication link 6, communication link 7, and communication link 8 between the device 2, device 3, device 4, and device 5. Each first near-field magnetic induction communication unit and the second near-field magnetic induction communication unit are connected to the corresponding near-field magnetic induction antenna ( Figure 1 (not depicted) for generating / sensing a near magnetic field for transmitting / receiving data via a communication signal between the first near-field magnetic induction communication unit and the second near-field magnetic induction communication unit.

[0068] The first antenna and the second antenna may be magnetic field antennas operably connected to a corresponding one of the first near-field magnetic induction communication unit and the second near-field magnetic induction communication unit.

[0069] Near Field Magnetic Induction (NFMI) uses non-propagating magnetic fields for communication between devices. A magnetic field antenna (e.g., a coil) in one device modulates a non-propagating magnetic field, which is received and sensed by a magnetic field antenna in another device.

[0070] NFMI communication systems differ from other types of wireless communication systems that implement so-called "far-field" communication, in which antennas are used to generate and transmit electromagnetic waves that radiate outward into free space. The power density of the radiated electromagnetic waves decreases with the distance from the antenna, that is, with the inverse of the square of the distance (1 / r 2 ) or -20dB / decade, which is good for long-distance communication; however, the NFMI communication system implements so-called "near field" communication, in which the transmission energy is obtained within the local magnetic field. The magnetic field energy is not radiated into free space. The power density of near-field transmission is proportional to the inverse of the sixth power of the distance from the antenna (1 / r 6) or at a rate of -60 dB / decade. The crossover point between the near field and the far field resides at approximately the wavelength λ divided by 2π, at which point the propagated energy from the fMRI communication system follows the same propagation rules as any far-field system, e.g., the power density of the radiated energy decreases as the quadratic power of the distance; however, at the crossover point, the propagated energy level of the fMRI communication system is -40 dB to -60 dB lower than for an equivalent far-field communication system.

[0071] Therefore, the NFMI communication system has a short range, usually less than 2m.

[0072] Standard modulation schemes used in typical RF communications (particularly amplitude modulation, phase modulation, and frequency modulation) can be used in the NFMI communication system.

[0073] Current commercial implementations of near field communications use a frequency of about 13.56 MHz as the most common carrier frequency, and have a wavelength λ of about 22.1 m.

[0074] The preferred monaural hearing device in an embodiment of the present invention performs near field communication using a carrier frequency in the range from 1 MHz to 30 MHz.

[0075] A carrier frequency of 10.66 MHz, 13.56 MHz, 22.66 MHz or the like is particularly preferred.

[0076] In contrast to RF electromagnetic waves, NFMI fields are transmitted through human tissue with very little absorption, making the NFMI communication system particularly suitable for communication between devices arranged at the ears of a human user and thus at opposite sides of the user's head.

[0077] As disclosed in more detail in EP 3 324 650 A1, each of the first magnetic field antenna and the second magnetic field antenna may be embedded in a multilayer printed circuit board (PCB).

[0078] Preferably, each of the first magnetic field antenna and the second magnetic field antenna comprises a coil, preferably a coil having a magnetic core, preferably a ferrite core, for providing a strong magnetic field with low losses and low cost.

[0079] Preferably, when the first shell and the second shell are worn at the intended operating position at the ear of the user for normal use of the monaural hearing device, the first magnetic field antenna and the second magnetic field antenna of the first shell and the second shell are aligned for optimal reception of the magnetic field generated by one of the first magnetic field antenna and the second magnetic field antenna and received by the other of the first antenna magnetic field and the second antenna magnetic field.

[0080] Each of the magnetic field antennas operating as receiving magnetic field antennas outputs a maximum amplitude signal in response to the received modulated magnetic field compared to corresponding output signals for any other orientations and positions of the first and second magnetic field antennas in their respective first and second housings.

[0081] For example, the first magnetic field antenna and the second magnetic field antenna may be positioned in the first housing and the second housing of the monaural hearing device, respectively. When the first housing and the second housing are worn at their intended operating positions at the ears of a user for normal use of the monaural hearing device, the central axis of the magnetic field generated by one of the first magnetic field antenna and the second magnetic field antenna is parallel to the corresponding central axis of the magnetic field generated by the other of the first magnetic field antenna and the second magnetic field antenna.

[0082] Preferably, to achieve optimal reception characteristics, a central axis of the magnetic field generated by one of the first and second magnetic field antennas coincides with a corresponding central axis of the magnetic field generated by the other of the first and second magnetic field antennas.

[0083] For example, the first magnetic field antenna and the second magnetic field antenna may include first and second coils and first and second magnetic cores, respectively, for providing a strong magnetic field.

[0084] The first coil and the second coil having the first magnetic core and the second magnetic core can be positioned in the first housing and the second housing, respectively, so that when the first housing and the second housing are in their intended operating position at or in the ear of a user for normal use of the monaural hearing device, the center axis of the first magnetic core is parallel to the corresponding center axis of the second magnetic core, and preferably, for optimal reception, the center axis of the first magnetic core coincides with the corresponding center axis of the second magnetic core.

[0085] The first magnetic core and the second magnetic core may be ferrite cores.

[0086] The first near-field magnetic induction communication unit connected to the first magnetic field antenna can also be used for near-field wireless communication with another device, for example, for ear-to-ear communication, such as near-field wireless communication between two monaural hearing devices worn on opposite sides of a user's head.

[0087] Near field wireless communication may be performed in a near field wireless communication network.

[0088] A monaural hearing device may advantageously be incorporated into a binaural hearing system, wherein two monaural hearing devices are interconnected using NFMI communication for digital exchange of data (such as digitally encoded audio signals, signal processing parameters, control data, such as identification of signal processing routines, etc.), and optionally interconnected with other devices (such as a remote control, etc.).

[0089] Thus, a binaural hearing system is provided with a first monaural hearing device and a second monaural hearing device, wherein each of the first monaural hearing device and the second monaural hearing device has a first near-field magnetic induction communication unit connected to a first magnetic field antenna, and during connection to each of the first near-field magnetic induction communication units of the respective first magnetic field antenna, each of the first monaural hearing device and the second monaural hearing device is adapted to perform ear-to-ear communication, e.g. near-field wireless data communication, between the first monaural hearing device and the second monaural hearing device of the binaural hearing system.

[0090] One or alternatively both of the first monaural hearing device and the second monaural hearing device have a second housing.

[0091] Figure 2 A timing diagram showing a communication scheme for a known hearing system 1 is shown.

[0092] Figure 2 Describes a time frame (cycle, frame) of a predetermined communication protocol. The predetermined communication protocol is used for Figure 1 The communication between the independent devices 2 , 3 , 4 , 5 of the hearing system 1 is shown.

[0093] A frame is an entity used in a time division multiple access system in which one of the devices may transmit during one or more time slots, receive during at least one other time slot, or neither transmit nor receive during one or more time slots.

[0094] Figure 2 The timing diagram depicted in the Figure 1 The frame includes six time slots 9, which are sequentially numbered as time slots T1 to T6. In order to implement bidirectional communication links 6, bidirectional communication links 7, and bidirectional communication links 8 between devices 2, 3, 4, and 5 of the hearing system 1, the frame includes six time slots 9. Figure 2 It is shown that for each device 2, device 3, device 4, device 5, if device 2, device 3, device 4, device 5 can transmit data, device 2, device 3, device 4, device 5 can receive data, or neither transmit nor receive data.

[0095] During time slot T1 ranging from time t0 to time t1, Figure 2 The first device 2 is shown in a transmission state 10. In the transmission state 10, the near-field magnetic induction communication unit of the first device 2 can transmit data to the second device 4. Therefore, the second device 4 is in a receiving state, in particular its near-field magnetic induction communication unit, during the first time slot T1. The near-field magnetic induction communication units of the other devices 3, 5 of the hearing system 1 are in an inactive state 12 during the time slot T1.

[0096] During time slot T2 in the range from time t1 to time t2, Figure 2 The first device 2 is shown in a receiving state 11. In the receiving state 11, the near-field magnetic induction communication unit of the first device 2 can receive data transmitted by the near-field magnetic induction communication unit of the second device 4. Therefore, the near-field magnetic induction communication unit of the second device 4 is in a transmitting state 10 during the second time slot T2. The near-field magnetic induction communication units of the other devices 3, 5 of the hearing system 1 are in an inactive state 12 during the time slot T2.

[0097] Thus, the time slots T1 , T2 enable bidirectional communication between the first device 2 and the second device 3 .

[0098] In a completely corresponding way, Figure 2 The time slots T3 and T4 of the frame depicted in FIG. 8 are reserved for a bidirectional communication link 7 between the first device 2 and the third device 3 of the hearing system 1 .

[0099] In a completely corresponding way, Figure 2 The time slots T5 and T6 of the frame depicted in are reserved for the bidirectional communication link 8 between the second device 4 and the fourth device 5 of the hearing system 1 .

[0100] The six time slots 9 of the frame of the predetermined communication protocol implement a time division multiple access (TDMA) communication system having bidirectional communication links 6, 7, 8 in time duplex (TD) between pairs of devices 2, 3, 4, 5 of the hearing system 1 (point-to-point communication).

[0101] Figure 3 Depicting a timing diagram of a time division multiple access scheme of a hearing system 1 according to an embodiment.

[0102] The near-field magnetic induction communication units of the devices 2 , 3 , 4 , 5 of the embodiment of the hearing system 1 according to the present invention are capable of transmitting data in a transmission signal at at least the first transmission power level or the second transmission power level.

[0103] Preferably, the near-field magnetic induction communication unit can transmit data in a transmission signal at a plurality of discrete transmission power levels, or transmit a transmission signal at a continuously variable transmission power level in a wide range of transmission powers.

[0104] Figure 3 Describes a single frame (cycle) of a predetermined communication protocol according to an embodiment of the present invention, which enables Figure 1The frame includes only four time slots 9, which are sequentially numbered as time slots T1 to T4. In order to implement a bidirectional communication link 6, a bidirectional communication link 7, and a bidirectional communication link 8 between the devices 2, 3, 4, and 5 of the hearing system 1 of the present invention, the frame includes four time slots 9. Figure 3 It is shown that for each device 2, device 3, device 4, device 5, if device 2, device 3, device 4, device 5 can transmit data at a first transmission power level; if device 2, device 3, device 4, device 5 can transmit data at a second transmission power level; if device 2, device 3, device 4, device 5 can receive data or if device 2, device 3, device 4, device 5 neither transmits nor receives data.

[0105] During time slot T1 ranging from time t0 to time t1, Figure 3 The first device 2 is shown in a first transmission state 13. In the first transmission state 13, the near-field magnetic induction communication unit of the first device 2 can transmit data in a transmission signal at a first transmission power level to the second device 4. Therefore, the second device 4, in particular its near-field magnetic induction communication unit, is in a receiving state 11 during a first time slot T1. The near-field magnetic induction communication units of the other devices 3, 5 of the hearing system 1 are in an inactive state 12 during the time slot T1.

[0106] During time slot T2 ranging from time t1 to time t2, Figure 2 The first device 2 is shown in a receiving state 11. In the receiving state 11, the near field magnetic induction communication unit of the first device 2 can receive data transmitted by the near field magnetic induction communication unit of the second device 4. Therefore, the near field magnetic induction communication unit of the second device 4 is in a first transmission state 13 during the second time slot T2.

[0107] The near-field magnetic induction communication units of the other devices 3 , 5 of the hearing system 1 are in an inactive state 12 during the time slot T2 .

[0108] Thus, the time slots T1 , T2 enable bidirectional communication between the first device 2 and the second device 3 .

[0109] The near-field magnetic induction communication units of the first device 2 and the second device 4 respectively transmit transmission signals at a first transmission power level.

[0110] During time slot T3 ranging from time t2 to time t3, Figure 3The first device 2 is shown in a second transmission state 14. In the second transmission state 14, the near-field magnetic induction communication unit of the first device 2 can transmit data in a transmission signal at a second transmission power level to the third device 3. Therefore, the third device 3, in particular its near-field magnetic induction communication unit, is in a receiving state 11 during the third time slot T3.

[0111] Figure 1 and Figure 3 The example of shows that the second transmission power level is lower than the first transmission power level. The spatial distance d1 between the first device 2 and the second device 4 on the one hand is greater (in particular significantly greater) than the spatial distance d2 between the first device 2 and the third device 3 on the other hand.

[0112] Therefore, the near field communication between the first device 2 and the third device 3 does not interfere with the second device 4 and the fourth device 5 .

[0113] During the time slot T3, the second device 4 is in the second transmission state 14. The near-field magnetic induction communication unit of the second device 2 can transmit data in the transmission signal at the second transmission power level to the fourth device 5. Therefore, the fourth device 5, in particular its near-field magnetic induction communication unit, is in the receiving state 11 or mode during the third time slot T3.

[0114] Thus, the near field communication between the second device 4 and the fourth device 5 does not interfere with the first device 2 and the third device 3 .

[0115] Thus, the near field communication between the first device 2 and the third device 3 does not interfere with the second device 4 and the fourth device 5 .

[0116] During the time slot T4, the second device 4 is in the receiving state 11. The near-field magnetic induction communication unit of the fourth device 5 can transmit data in the transmission signal at the second transmission power level to the second device 4. Therefore, the fourth device 5, in particular its near-field magnetic induction communication unit, is in the second transmission state 14 state 11 during the fourth time slot T4.

[0117] Since the second transmission state 14 only involves transmitting a second transmission power level that is lower than the first transmission power level, and the distance d1 between the first device 2 and the second device 4 on the one hand is greater than the spatial distance d3 between the second device 4 and the fourth device 5 on the other hand, the near field communication between the second device 4 and the fourth device 5 does not interfere with the first device 2 and the third device 3.

[0118] Figure 4 A simplified block diagram showing a hearing aid device 2 , a hearing aid device 3 , a hearing aid device 4 , a hearing aid device 5 according to an embodiment of the hearing system 1 .

[0119] Figure 4 The block diagram shown in particular depicts Figure 1An electronic circuit 21 of a hearing aid device is shown.

[0120] The depicted hearing device circuit 21 comprises a front microphone 22 and a rear microphone 23. The front microphone 22 and the rear microphone 23 convert acoustic sound signals from the surrounding environment of the hearing device system 1 into corresponding microphone audio signals 24, 25 output by the front microphone 22 and the rear microphone 23. The microphone audio signals 24, 25 are fed to respective A / D converters 26, 27 for converting the microphone audio signals 24, 25 into two respective digital microphone audio signals 28, 29. The digital microphone audio signals 28, 29 are optionally pre-filtered, wherein the pre-filter is Figure 4 , and the digital microphone audio signal 28, the digital microphone audio signal 29 are combined in a subsequent signal combiner 30. The signal combiner 30 may, for example, form and output a digital microphone audio signal 31 having directivity, as is well known in the field of hearing aid systems. The digital microphone audio signal 31 is input to a signal router 32. The signal router 32 is configured to output a weighted sum signal 33 based on a weighted sum of the signals input to the signal router 32. The weighted sum signal 33 output by the signal router 32 is then applied to a hearing loss processor 34, which is configured to generate a hearing loss compensation output signal 35 based on the signal router output signal 33. The hearing loss compensation output signal 35 is applied to an output transducer 36 (e.g., a miniature loudspeaker or receiver) for conversion into acoustic sound for transmission into the ear canal of the user and to the eardrum.

[0121] The depicted hearing device circuit 21 is also configured to receive data, including control signals and digital audio signals, from various transmitters, such as mobile phones, smart phones, desktop computers, tablet computers, laptop computers, radio devices, media players, accompanying microphones, public address systems such as those installed in public places (like churches, auditoriums, theaters, cinemas, etc.), public address systems (such as train stations, airports, shopping malls, etc.).

[0122] exist Figure 4 In the embodiment shown, another device may wirelessly transmit data including digital audio signals to the hearing device 21 via a second housing 37, which is removably attached to a first housing 38. The latter housing 38 comprises in particular components of the hearing device circuitry 21, such as the front microphone 22, the rear microphone 23, the A / D converter 26, the A / D converter 27, the signal combiner 30, the signal router 32, the hearing loss processor 34 and the output transducer 36.

[0123] The second housing 37 may specifically house an RF antenna 39 and a wireless transceiver 40 connected to the RF antenna 39. The wireless transceiver 40 extracts digital data received from the signal received from the RF antenna 39 and decodes the digital data, for example, the digital data includes digital audio representing a stereo audio signal or a mono audio signal. The second housing 37 also houses a second near-field magnetic induction communication unit 42, which is configured to modulate the signal received by the RF antenna 39 into a modulated signal suitable for transmission via a second magnetic field antenna 43, so that the second magnetic field antenna 43 emits a local non-propagating magnetic field for reception by a corresponding first magnetic field antenna 44 housed in the first housing 38 and also including a coil wound around a ferrite core. When the second housing 37 is attached to the first housing 38 in its intended operating position, the central axes of the transmission magnetic field antenna 43 and the reception magnetic field antenna 44 are aligned in parallel for optimal or substantially optimal reception. The first housing 38 also houses a first near-field magnetic induction communication unit 45 connected to a first magnetic field antenna 44, and retrieves digital data including digital audio representing a stereo audio signal or a mono audio signal from a signal received from the first magnetic field antenna 44, and forwards the digital data to the signal router 32 to include the digital audio of the stereo channel or the mono audio signal in the audio signal 33, which is input to the hearing loss processor 34 for hearing loss compensation.

[0124] The signal router 32 is also configured to route signals expected from Figure 4 . The first near-field magnetic induction communication unit 45, worn at the other ear of the user, modulates the digital audio of the stereo channel or mono audio signal in question into a modulated signal suitable for transmission, while the first magnetic field antenna 44 emits a local non-propagating magnetic field in the direction of the other hearing aid device not shown, for example, wherein the field is aligned with the ferrite core of the second magnetic field antenna 43 in the first housing 37 of the other hearing aid device for optimal or substantially optimal reception when the two hearing aid devices are worn in their intended operating positions at the respective ears of the user during normal operational use. This is achieved by positioning the ferrite cores of the magnetic field antennas in parallel alignment and preferably coincidence with the longitudinal axis when the two monaural hearing aid devices are worn at the respective ears of the user during normal operational use.

[0125] Another monaural hearing aid device may have Figure 4The same circuit arrangement is shown housed in its corresponding first housing 37, wherein the first magnetic field antenna 44 receives the modulated magnetic field and converts the modulated magnetic field into a corresponding voltage or current, which is applied to the input of the first near-field magnetic induction communication unit 45. The first near-field magnetic induction communication unit 45 is configured to modulate the digital audio of the stereo channel or the mono audio signal and forward the digital audio of the stereo channel or the mono audio signal to the signal router 32. The signal router 32 may include the digital audio of the stereo channel or the mono audio signal in the signal router output signal 33, and the signal router output signal 33 is transmitted to the hearing loss processor 34 for hearing loss compensation processing.

[0126] In this way, the digital audio of the stereo channels or the mono audio signal for the other ear is transmitted to the monaural hearing aid device at the other ear with only little attenuation on its transmission path. The digital audio may include audio signals from a variety of sources, and therefore, the digital audio may form a plurality of input signals for the signal router 32, in particular, one input signal for each audio source.

[0127] In the case of receiving digital audio by the RF antenna 39, the digital audio may be transmitted to the user while the digital microphone audio signal 31 is attenuated during the transmission of the digital audio. The digital microphone audio signal 31 may also be muted. The user may control whether the digital microphone audio signal 31 is muted, attenuated, or remains unchanged by inputting through a user interface of a monaural hearing aid device of a type well known in the art.

[0128] The second housing 37 of the auxiliary device shown also houses a rechargeable energy storage device (e.g., in the form of a capacitor 46) for supplying power to electronic components such as the wireless transceiver 40 and the second near-field magnetic induction communication unit 42 of the electronic circuit 21 housed by the second housing 37. The capacitor 46 is recharged by energy received by the second magnetic field antenna 43 and supplied to the capacitor 46 via the diode 47.

[0129] The first near-field magnetic induction communication unit 45 forwards a high frequency signal (preferably a carrier signal having a frequency of, for example, 10.66 MHz or 22.66 MHz) to the first magnetic field antenna 44 for transmission to the second magnetic field antenna 43 for recharging the capacitor 46 or any other rechargeable storage device.

[0130] Additionally or alternatively, the circuitry contained in the second housing 37 is provided by Figure 4 Powered by a battery not shown.

[0131] The circuits housed in the first housing 38 are, for example, Figure 4 Powered by a battery not shown.

[0132] Figure 5 A simplified block diagram of another hearing device 48 in an embodiment of a hearing aid system is shown. The block diagram shows in particular the electronic circuitry of another monaural hearing aid in the form of a RIE hearing aid, the second housing 37 of which is the housing of the earpiece.

[0133] The earpiece of the monaural hearing aid device shown is similar to the earpiece of the RIE hearing aid device disclosed in EP 3 101 917 A1, except that in the new monaural hearing aid device, the connectors, conductors and cables of the wired interface disclosed in EP 3 101 917 A1 for interconnecting the earpiece with the electronic circuit of the BTE housing have been replaced by a near field wireless interface for communicating with the earpiece in a manner similar to that disclosed in EP 3 101 917 A1. Figure 4 The wireless interface of the electronic circuit depicted in the figure implements near-field wireless data communication with the first magnetic field antenna 44, and the near-field wireless interface includes a first near-field magnetic induction communication unit 45 and a first magnetic field antenna 44 accommodated by the first shell 60, and a second near-field magnetic induction communication unit 42 and a second magnetic field antenna 43 accommodated by the earpiece shell 37.

[0134] Figure 5 The new monaural hearing aid 48 shown in FIG. 1 includes a device adapted to be worn on a Figure 5 The first housing 38 in the form of a BTE housing 38 is placed behind the pinna of the user of the hearing aid 48, not shown in FIG. The first housing 38 accommodates a device similar to Figure 4 The electronic circuit of the housing 38 depicted in FIG. 1 is similar to the electronic circuit of FIG. 1 , except that the output transducer 36 has been moved from the first housing 38 to the second housing 37 of the earpiece.

[0135] As shown in the first housing 38 Figure 4 In the electronic circuit shown in FIG. 1 , the first housing 38 accommodates a first near-field magnetic induction communication unit 45 and a first magnetic field antenna 44 connected to the first near-field magnetic induction communication unit 45 for implementing near-field wireless data communication. Figure 5 In the electronic circuit depicted in , the hearing loss compensation output signal is input to the first near-field magnetic induction communication unit 45 and wirelessly transmitted to the earpiece for transmission to the output device 36 via the second near-field antenna 43 and the first near-field induction communication unit 42 housed in its second housing 37.

[0136] With Figure 4 In the same manner as shown in Figure 5 The electronic circuit of the first housing 38, such as the optional components (e.g., the RF antenna 39 connected to the wireless transceiver 40 (with Figure 5 As shown in the dashed line).

[0137] Thus, the monaural hearing aid device further comprises a second housing 37 in the form of a housing 37 of the earpiece. The housing 37 of the earpiece accommodates a second near-field magnetic induction communication unit 42 and a second magnetic field antenna 43 connected to the second near-field magnetic induction communication unit 42 for performing near-field wireless data communication with the first magnetic field antenna 44 and the first near-field magnetic induction communication unit 45.

[0138] The second housing 37 of the earpiece also houses a microphone 49, a microphone 50 and a microcontroller 51 with a non-volatile memory for storing data related to the configuration of the earpiece as disclosed in EP 3 101 917 A1.

[0139] Figure 5 The output device 36, microphone 49, microphone 50 and microcontroller 51 shown in EP 3 101 917 A1 are respectively Figure 4 The output device 36, microphone 26, microphone 66 and microcontroller 40 shown in FIG. 1 respond, and the output device 36, microphone 49, microphone 50 and microcontroller 51 operate in the same manner as disclosed in EP 3 101 917 A1.

[0140] As needed, the signal router 50 routes signals from the second near-field magnetic induction communication unit 42 to the output device 36 , and routes signals from the microphones 49 , 52 to the second near-field magnetic induction communication unit 42 , and routes signals between the microcontroller 51 and the second near-field magnetic induction communication unit 42 .

[0141] The second housing 37 also houses a rechargeable energy storage device in the form of a capacitor 46 for supplying power to electronic components such as a microcontroller 51 and a second near-field magnetic induction communication unit 42 of the electronic circuit housed in the second housing 37. The capacitor 46 is recharged by energy received by the second magnetic field antenna 43 and supplied to the capacitor 46 through the diode 47.

[0142] The first near-field magnetic induction communication unit 45 forwards a high frequency signal (preferably a carrier signal having a frequency of, for example, 10.66 MHz or 22.66 MHz) to the first magnetic field antenna 44 for transmission to the second magnetic field antenna 43 for recharging the capacitor 46 .

[0143] Alternatively or additionally, Figure 5 A battery, not shown, powers the electronic circuitry housed by the second housing 37 .

[0144] The electronic circuitry contained in the first housing 38 (eg, BTE housing 38) is composed of Figure 5 Also not shown is the battery power supply.

[0145] Figure 6A flow chart of a communication method for the hearing system 1 according to an embodiment is provided. Figure 6 The communication method of in particular provides an example for an initial pairing procedure.The pairing procedure may be carried out, for example, when the power of the first device 2 of the hearing device system 1 is switched on.

[0146] Alternatively or additionally, the pairing process may be run in response to a corresponding user input via a user interface of the hearing device system 1 .

[0147] Preferably, the method steps of the communication method are performed by a control circuit, in particular a microcontroller circuit or a digital signal processor (DSP) of the first device 2 , such as a hearing aid device.

[0148] After starting up the first device 2, the control circuit selects a first transmission power level in step S1. The first power level is a high transmission power level for transmitting a transmission signal emitted by a near-field magnetic induction system.

[0149] High power is preferably the highest transmission power level among a plurality of available transmission power levels.

[0150] In step S2, the first device 2 transmits an inquiry signal at a first power level. The inquiry signal may, for example, include a first device type identifier. The first device type identifier unambiguously identifies the device type of the first device 2.

[0151] For example, the first device type identifier refers to the first device 2 as a hearing aid device in a BTE housing having a specific configuration, in particular a specific circuit configuration.

[0152] In step S3 following step S2, the first device enters a listening state in which the first device (particularly its near-field magnetic induction transceiver) is adapted to receive near-field magnetic induction signals transmitted from other devices magnetically coupled to the near-field magnetic induction antenna of the first device.

[0153] If in step S4 the near field magnetic induction transceiver determines that a response signal has been received, then in step S5 the pairing process continues with evaluating the received response signal.

[0154] Evaluating the response signal may in particular comprise extracting a device type identifier of the third device 3 transmitting the response signal in response to receiving the query signal. The received device type identifier unambiguously identifies the device type of the third device 3.

[0155] For example, the device type identifier of the third device 3 refers to an auxiliary device in a backpack housing that includes specific circuitry (eg, includes a wireless interface, possibly providing a wireless Bluetooth™ interface).

[0156] In step S6, the first device 2 (in particular, its control circuit) determines which device type identifier is included in at least one received response signal. If, for example, the device type identifier in the received response signal is of the second type (yes in step S6), the pairing process continues with step S7 and a second transmission power level is selected. In particular, the first device 2 will select the second transmission power level for transmitting signals to the third device 3 via the near-field magnetic induction transceiver of the first device 2.

[0157] In the example case where the first device 2 is a hearing aid device in a BTE housing and the third device 3 is an auxiliary device in a backpack housing, the first device 2 adjusts the transmission power level of the near-field magnetic induction transceiver from a first power level to a lower second power level during a time slot of a frame of a predetermined transmission protocol, which time slot is allocated for transmitting data from the first device 2 to the third device 3 in a transmission signal.

[0158] In a subsequent step S8, the pairing process ends and the first device 2 continues to step S9. In step S9, the hearing device system 1 comprising the first device 2 and the third device 3 operates in a conventional manner, wherein, however, the first device 2 transmits to the third device 3 at an adjusted transmission power level, in the example discussed, at a second transmission power level lower than the first transmission power level.

[0159] If in step S4 the first device 2 determines that no response signal has been received during step S3 , the pairing process proceeds directly to step S8 and ends the pairing process.

[0160] If in step S6 the first device 2 determines that a response signal has not been received during step S3, the pairing process proceeds to step S8 and ends the pairing process.The first transmission power level selected as the first transmission power level in step S1 then maintains the selected transmission power level.

[0161] Obviously, in step S6, the received device type identifier may be tested whether it corresponds to a plurality of different device type identifiers.Then, based on the result determined in step S8, a corresponding transmission power level corresponding to step S7 may be selected from two or more different power levels.

[0162] The communication operation in step S9 may use the selected transmission power level from the pairing process discussed with reference to steps S1 to S8. Additionally or alternatively, the communication operation in step S9 may include further processes that allow for continuous adaptation of the selected transmission power level during the communication operation.

[0163] Figure 7A simplified flow chart of a communication method for continuously adapting a selected transmission power level during communication operation for a hearing device system 1 according to a preferred embodiment is provided.

[0164] The method for adapting the hearing device system 1 may be performed at regular intervals during the communication operation of the hearing device system 1. Figure 7 In particular, the process for adapting the selected transmission power level may be performed at intervals of each time slot of a predetermined communication protocol for near-field magnetic induction communication between devices 2, 3, 4, 5 of the hearing device system 1.

[0165] In step S9, the hearing device system 1 comprising the devices 2, 3, 4 and 5 carries out communication operations using the transmission power level selected from the pairing process discussed with reference to steps S1 to S8. Additionally or alternatively, the hearing device system 1 starts operation between all devices at a maximum transmission power level for transmission operations of the near-field magnetic induction transceivers of the devices 2, 3, 4 and 5.

[0166] In step S10 , the first device 2 evaluates the reception signal received in the near-field magnetic induction transceiver from the second device 4 in the corresponding time slot 9 .

[0167] In particular, the control circuit of the first device 2 may calculate a packet error rate PER based on a CRC checksum of a received data packet of the received signal. Additionally or alternatively, the control circuit may calculate a bit error rate BER from the data bits received in the received signal. Then, in step S10, the control circuit may determine the reception quality as a link quality measurement of the near-field magnetic induction link from the second device 4 to the first device 2 based on the calculated PER and / or BER.

[0168] Then, in step S11, the determined link quality measurement from step S10 is compared with a quality threshold. The quality threshold may be a preset or selectable threshold that defines a minimum transmission link quality for ensuring the required minimum data rate of the near-field magnetic induction communication link between the first device 2 and the second device 4. If the link quality measurement determined in step S11 exceeds the quality threshold, the method proceeds to step S12 and the transmission power level is reduced. In particular, if the near-field magnetic induction transceiver of the first device 2 is configured to operate at a plurality of different transmission power levels that differ by one or more discrete power values, the control circuit of the second device 2 may reduce the transmission power level of the near-field magnetic induction transceiver of the second device 2 by one power level step.

[0169] The second device 2 may also communicate a reduced transmission power level, or alternatively provide a command in a transmission signal to the second device 4 for reducing the transmission power level by a certain power value (eg a predefined power value step).

[0170] The reducing power level in step S12 is performed under the assumption that transmission power levels lower than the selected transmission power level are available for the first device 2 .

[0171] After adapting (adjusting) the transmission power level in step S12, the method proceeds to step S15, and the communication operation of the near-field magnetic induction wireless link is carried out at the adjusted transmission power level.

[0172] The method may then return to step S10 for the next cycle of the method.

[0173] If the link quality measure determined in step S11 does not exceed the quality threshold (NO in step S11 ), the method proceeds to step S13 .

[0174] In step S13, the determined link quality measurement is less than the quality threshold, the method proceeds to step S14, and the transmission power level is increased. In particular, if the near-field magnetic induction transceiver of the first device 2 is configured to operate at a plurality of different transmission power levels that differ by one or more discrete power values, the control circuit of the second device 2 increases the transmission power level of the near-field magnetic induction transceiver of the second device 2 by one power level step.

[0175] After adapting (adjusting) the transmission power level in step S14, the method proceeds to step S15, and the communication operation of the near-field magnetic induction wireless link is carried out at the adjusted transmission power level.

[0176] The method may then return to step S10 for the next cycle of the method.

[0177] The second device 2 may also communicate the increased transmission power level, or provide a command in the transmission signal to the second device 4 for increasing the transmission power level by a certain power value (eg, a predefined power value step).

[0178] The increasing power level in step S12 is performed under the assumption that transmission power levels less than the selected transmission power level are available for the first device 2. This will not be the case, for example, when executing steps S10, S11, S13 and S14 in a first initial run after powering up the hearing device system 1.

[0179] If the link quality measure determined in step S11 does not exceed the quality threshold (No in step S11), and the link quality measure determined in step S13 does not exceed the quality threshold, the determined link quality measure is determined to be less than the quality threshold, the method proceeds directly to step S15, and the communication operation is continued at an adjusted power level corresponding to the selected transmission power level, and the second device 2 enters the process of steps S10 to S14 at the selected transmission power level. In this case, the adjusted transmission power level corresponds to a power level that ensures an acceptable near field communication link quality due to the dynamic adaptation of the transmission power level to the lowest possible transmission power value, so as to ensure a minimum near field communication link quality with advantageously low power consumption.

[0180] Various embodiments of an advantageous hearing device system 1 , a hearing aid device thereof and a corresponding communication method are discussed above as illustrative examples of the invention as defined in the appended claims.

Claims

1. A hearing device system, comprising at least four devices (2, 3, 4, 5), wherein the four devices (2, 3, 4, 5) include two or more hearing aid devices, wherein the at least four devices are configured to wirelessly communicate with each other via near-field magnetic induction wireless links (6, 7, 8) based on a predetermined communication protocol, wherein the predetermined communication protocol defines a frame comprising at least a first time slot (9; T1, T2) and at least a second time slot (9; T3, T4), wherein at least a first pair of devices (2, 4) of the at least four devices (2, 3, 4, 5) is configured to communicate in the first time slot (9; T1, T2), and at least a second pair of devices (2, 3; 4; 5) of the at least four devices (2, 3, 4, 5) is configured to communicate in the second time slot (9; T3, T4), in, The first pair of devices (2, 4) is configured to communicate at a first power level in the first time slot (T1, T2), and the second pair of devices (2, 3; 4, 5) is configured to communicate at a second power level lower than the first power level in the second time slot (T3, T4); and The first pair of devices comprises a first hearing aid device (2) and a second hearing aid device (4) configured to communicate at a first power level in the first time slot (T1, T2), and the second pair of devices comprises the first hearing aid device (2) and a first auxiliary device (3) configured to transmit at a second power level in the second time slot (T3, T4).

2. The hearing device system according to claim 1, characterized in that At least one first device (2) of the at least four devices (2, 3, 4, 5) comprises a control circuit, wherein the control circuit is configured to select the first power level and / or the second power level based on at least one of: a received type identifier of at least two second devices (3, 4) of the at least four devices (2, 3, 4, 5), and Dynamic evaluation of the communication link quality of the near-field magnetic induction wireless link (6, 7, 8) from the first device (2) to each of the at least two second devices (3, 4) of the at least four devices (2, 3, 4, 5).

3. The hearing device system according to claim 2, characterized in that The control circuit is configured to select the first power level and / or the second power level based on a dynamic evaluation of the communication link quality of the near-field magnetic induction wireless link (6, 7, 8) from the at least one first device (2) to each of the at least two second devices (3, 4) of the at least four devices (2, 3, 4, 5) by calculating the communication link quality of the communication signal received by the at least one first device (2) from each of the at least two second devices (3, 4) via the near-field magnetic induction wireless link (6, 7, 8).

4. The hearing device system according to claim 3, characterized in that The control circuit is configured to increase the power level if the assessed communication link quality is below a predetermined minimum communication link quality.

5. The hearing device system according to claim 3 or 4, characterized in that: The control circuit is configured to reduce the power level if the assessed communication link quality exceeds a predetermined minimum communication link quality.

6. The hearing device system according to claim 2, characterized in that The control circuit is configured to determine the communication link quality by calculating at least one of a packet error rate and a bit error rate of a communication signal received by the at least one first device from each of the at least two second devices (3, 4).

7. The hearing device system according to claim 2, characterized in that The control circuit is configured to exchange respective device type identifiers with the at least two second devices (3, 4) via the first near-field magnetic induction transceiver in a pairing session.

8. The hearing device system according to claim 7, characterized in that The control circuit is configured to control the first near-field magnetic induction transceiver to transmit an inquiry signal or a beacon signal at the first power level during the pairing session, The first power level is higher than the second power level.

9. The hearing device system according to claim 8, characterized in that The at least two second devices (3, 4) of the at least four devices (2, 3, 4, 5) are each configured to transmit a response signal including a device type identifier for a second device type when receiving the query signal and / or the beacon signal.

10. The hearing device system according to claim 2, characterized in that The at least one first device (2) is at least one of a monaural hearing aid device and a monaural headset.

11. The hearing device system (1) according to claim 1, Wherein when the hearing device system (1) is worn by a user, a distance d1 between devices of the first pair of devices (2, 4) is greater than a distance d2 between devices of the second pair of devices (2, 3), and wherein the first power level is greater than the second power level.

12. The hearing device system (1) according to claim 11, further comprising a second auxiliary device (5), and wherein a third pair of devices (4, 5) of the at least four devices (2, 3, 4, 5) comprises the second hearing aid (4) and the second auxiliary device (5), and is configured to communicate in the second time slot (T3, T4) at a third power level different from the first power level, and each of the second power level and the third power level is less than the first power level.

13. A hearing aid device, comprising a control circuit and a near-field magnetic induction transceiver, wherein the hearing aid device is configured to communicate via the near-field magnetic induction transceiver according to a predetermined communication protocol, wherein the predetermined communication protocol defines a frame comprising at least a first time slot (9; T1, T2) and at least a second time slot (9; T3, T4), in, The control circuit is configured to control the near-field magnetic induction transceiver to transmit a first transmission signal to a second device (4) at a first transmission power level in the first time slot (9; T1, T2) and to control the near-field magnetic induction transceiver to transmit a first transmission signal to a second device (4) at a first transmission power level in the second time slot (9; T3, T4) transmitting a second transmission signal to a third device (3) at a second transmission power level lower than the first transmission power level; wherein the second device (4) is an additional hearing aid device; wherein the hearing aid device is configured to transmit a first transmission signal to the additional hearing aid device at the first transmission power level in the first time slot (9; T1, T2), the third device (3) is an auxiliary device; and wherein the hearing aid device is configured to transmit a first transmission signal to the additional hearing aid device at the first transmission power level in the second time slot (9; T3, T4) transmitting a second transmission signal to the auxiliary device at a second transmission power level different from the first transmission power level.

14. A communication method for a hearing system (1) comprising at least four devices (2, 3, 4, 5), the four devices comprising at least two hearing aid devices, wherein the at least four devices (2, 3, 4, 5) are configured to wirelessly communicate with each other via near-field magnetic induction wireless links (6, 7, 8) based on a predetermined communication protocol, wherein the predetermined communication protocol definition includes at least a first time slot (9; T1, T2 and the second time slot (9; T3, T4) frames, The communication method includes: performing a first communication between a first pair of devices (2, 4) of the at least four devices (2, 3, 4, 5) at a first transmission power level via the first time slot (9; T1, T2), and communicating between a second pair of devices (3, 5) of the at least four devices at a second transmission power level lower than the first transmission power level via the second time slot (9; T3, T4); The first pair of devices comprises a first hearing aid device and a second hearing aid device (2, 4) configured to transmit at a first transmission power level in the first time slot (T1, T2), and the second pair of devices comprises the first hearing aid device (2) and a first auxiliary device (3) configured to transmit at a second transmission power level in the second time slot (T3, T4).

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