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EP2723101B1 - Prothèse auditive BTE possédant une antenne équilibrée - Google Patents

Prothèse auditive BTE possédant une antenne équilibrée Download PDF

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Publication number
EP2723101B1
EP2723101B1 EP13175258.6A EP13175258A EP2723101B1 EP 2723101 B1 EP2723101 B1 EP 2723101B1 EP 13175258 A EP13175258 A EP 13175258A EP 2723101 B1 EP2723101 B1 EP 2723101B1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
antenna
extending along
head
segment
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP13175258.6A
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German (de)
English (en)
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EP2723101A3 (fr
EP2723101A2 (fr
Inventor
Søren Kvist
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
GN Hearing AS
Original Assignee
GN Hearing AS
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
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First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=48747397&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP2723101(B1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority claimed from DKPA201270410A external-priority patent/DK201270410A/da
Priority claimed from DKPA201270411A external-priority patent/DK201270411A/da
Application filed by GN Hearing AS filed Critical GN Hearing AS
Priority to DK18202039.6T priority Critical patent/DK3468230T3/da
Priority to EP18202039.6A priority patent/EP3468230B1/fr
Publication of EP2723101A2 publication Critical patent/EP2723101A2/fr
Publication of EP2723101A3 publication Critical patent/EP2723101A3/fr
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Publication of EP2723101B1 publication Critical patent/EP2723101B1/fr
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Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/27—Adaptation for use in or on movable bodies
    • H01Q1/273—Adaptation for carrying or wearing by persons or animals
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/12—Supports; Mounting means
    • H01Q1/22—Supports; Mounting means by structural association with other equipment or articles
    • H01Q1/24—Supports; Mounting means by structural association with other equipment or articles with receiving set
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q9/00—Electrically-short antennas having dimensions not more than twice the operating wavelength and consisting of conductive active radiating elements
    • H01Q9/04—Resonant antennas
    • H01Q9/16—Resonant antennas with feed intermediate between the extremities of the antenna, e.g. centre-fed dipole
    • H01Q9/20—Two collinear substantially straight active elements; Substantially straight single active elements
    • H01Q9/24—Shunt feed arrangements to single active elements, e.g. for delta matching
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/021—Behind the ear [BTE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural

Definitions

  • the present disclosure relates to a hearing aid having an antenna, such as a balanced antenna, the antenna being configured for providing the hearing aid with wireless data communication features.
  • Hearing aids are very small and delicate devices and comprise many electronic and metallic components contained in a housing small enough to fit in the ear canal of a human or behind the outer ear.
  • the many electronic and metallic components in combination with the small size of the hearing aid housing impose high design constraints on radio frequency antennas to be used in hearing aids with wireless communication capabilities.
  • antennas in hearing aids have been used for receiving radio broadcasts or commands from a remote control.
  • such antennas are designed to fit in the hearing aid housing without special concern with relation to the obtained directivity of the resulting radiation pattern.
  • behind-the-ear hearing aid housings typically accommodate antennas positioned with their longitudinal direction in parallel to the longitudinal direction of the banana shaped behind-the-ear hearing aid housing.
  • In-the-ear hearing aids have typically been provided with patch antennas positioned on the face plate of the hearing aids as for example disclosed in WO 2005/081583 ; or wire antennas protruding outside the hearing aid housing in a direction perpendicular to the face plate as for example disclosed in US 2010/20994 .
  • US 2010/0158293 discloses a hearing aid with a radio circuit and an antenna.
  • the antenna is a loop antenna, such as a single or multi loop antenna and the radio circuit is at least substantially within the aperture of the loop antenna, see paragraphs [0029] and [0030].
  • the above-mentioned and other objects are obtained by provision of a hearing aid according to the subject-matter of claim 1.
  • the current induced in the first segment may be symmetric with respect to a plane substantially partitioning the first segment in the middle of the segment.
  • the first segment may be provided in a position substantially orthogonal to a side of the head, when the hearing aid is worn by a user in its intended operational position.
  • the first segment may extend in a direction having at least a vector component being orthogonal to the side of the head, for example the vector component being orthogonal to the side of the head may be at least the same length as a vector component extending parallel to the side of the head.
  • the first segment may short circuit the part of the antenna proximate the first side of the hearing aid and the part of the antenna proximate the second side of the hearing aid to provide a current bridge between the first side of the hearing aid and the second side of the hearing aid.
  • an electromagnetic field emitted by the antenna may propagate along the surface of the head of the user with its electrical field substantially orthogonal to the surface of the head of the user when the hearing aid is worn in its operational position by a user.
  • the electromagnetic field emitted by the antenna propagates primarily along the surface of the head or body of the user.
  • a substantial part of the electromagnetic field, such as 60%, such as 80%, emitted by the antenna may propagate along the surface of the head of the user with its electrical field substantially orthogonal to the surface of the head of the user.
  • the electromagnetic field is diffracted around the head of a user, losses due to the interaction with the surface of the head are minimized.
  • the strength of the electromagnetic field around the head, or the body, of the user is significantly improved.
  • the interaction with other antennas and/or transceivers, as provided in either a second hearing aid of a binaural hearing aid system located at the other ear of a user, or as provided in accessories as mentioned above, which typically are located in front of a user, or other wearable computing devices is enhanced. It is a further advantage of providing an electromagnetic field around the head of a user that an omni-directional connectivity to external devices, such as accessories, is provided.
  • an ear-to-ear path gain may be improved, such as by 10 -15 dB, such as by 10-20 dB.
  • the antenna may emit a substantially TM polarized electromagnetic field for diffraction around the head of a user, i.e. TM polarised with respect to the surface of the head of a user.
  • the first segment of the antenna contributes to an electromagnetic field that travels around the head of the user thereby providing a wireless data communication that is robust and has low loss.
  • the antenna does not, or substantially does not, emit an electromagnetic field in the direction of the first segment, such as in a direction along the first segment
  • the antenna does not, or substantially does not, emit an electromagnetic field in the direction of the ear to ear axis of the user when the hearing aid is positioned in its operational position at the ear of the user; rather, the antenna emits an electromagnetic field that propagates in a direction parallel to the surface of the head of the user when the hearing aid is positioned in its operational position during use, whereby the electric field of the emitted electromagnetic field has a direction that is orthogonal to, or substantially orthogonal to, the surface of the head at least along the side of the head, or the part of the body, at which the antenna is positioned during operation.
  • propagation loss in the tissue of the head is reduced as compared to propagation loss of an electromagnetic field with an electric field component that is parallel to the surface of the head. Diffraction around the head makes the electromagnetic field emitted by the antenna propagate from one ear and around the head to the opposite ear.
  • the hearing aid typically further comprises a microphone for reception of sound and conversion of the received sound into a corresponding first audio signal, a signal processor for processing the first audio signal into a second audio signal compensating a hearing loss of a user of the hearing aid, and a receiver that is connected to an output of the signal processor for converting the second audio signal into an output sound signal.
  • the first segment may preferably be structured so that upon excitation of the antenna, the current flows in at least the first segment in a direction substantially orthogonal to a surface of the head of a user when the hearing aid is worn in its operational position by the user.
  • the first segment may extend in a direction substantially parallel with an ear to ear axis of the user, and thus, substantially orthogonal to a surface of the head, when the hearing aid is worn in its operational position by a user.
  • a part of the antenna extending proximate the first side of the hearing aid is substantially identical to a part of the antenna extending proximate the second side of the hearing aid.
  • the physical shape of the part of the antenna extending proximate the first side of the hearing aid may be substantially identical to the physical shape of the part of the antenna extending proximate the second side of the hearing aid.
  • the part of the antenna extending proximate the first side of the hearing aid and the part of the antenna extending proximate the second side of the hearing aid may have substantially the same free-space antenna radiation pattern.
  • the feed system may comprise a first feed point for exciting at least the antenna proximate the first side of the hearing aid and a second feed point for exciting at least the antenna proximate the second side of the hearing aid.
  • the first feed point and the second feed point may be initially balanced, that is out of phase.
  • the part of the antenna extending proximate the first side of the hearing aid and/or the part of the antenna extending proximate the second side of the hearing aid may be actively fed.
  • the part of the antenna extending proximate the first side of the hearing aid may have a first feed point and the part of the antenna extending proximate the second side of the hearing aid may have a second feed point.
  • the part of the antenna extending proximate the first side of the hearing aid and the part of the antenna extending proximate the second side of the hearing aid may be fed from the transceiver in the hearing aid.
  • the feed system may furthermore comprise one or more transmission lines for connecting the part of the antenna extending proximate the first side of the hearing aid and the part of the antenna extending proximate the second side of the hearing aid to the source, such as to the transceiver.
  • the first feed point may reflect the connection between a first transmission line and the part of the antenna extending proximate the first side of the hearing aid
  • the second feed point may reflect the connection between another transmission line and the part of the antenna extending proximate the second side of the hearing aid.
  • the antenna may be a balanced antenna, and in one or more embodiments, the current from the transceiver to a feed point for the part of the antenna extending proximate the first side of the hearing aid and the current to the feed point for the part of the antenna extending proximate the second side of the hearing aid may thus have substantially the same magnitude but run in opposite directions, thereby establishing a balanced feed line and a balanced antenna. It is envisaged that the current magnitudes may not be exactly the same, so that some radiation, though principally unwanted, from the feed line may occur.
  • the antenna may form a mirrored inverted F-antenna wherein the part of the antenna extending proximate the first side of the hearing aid, and substantially half of the first segment is mirrored to the part of the antenna extending proximate the second side of the hearing aid and substantially the other half of the first segment.
  • the width of the antenna may determine the bandwidth for the antenna, thus by increasing the width of the inverted F-antenna, the bandwidth may also be increased.
  • the part of the antenna extending proximate the first and/or second side of the hearing aid may be monopole antenna structure(s), such as any antenna structure having a free end, such as a linear monopole antenna structure, etc.
  • the length of the part of the antenna extending proximate the first and/or second side of the hearing aid as measured from the short circuit to the free end may be substantially lambda/4, or any odd multiple thereof, where lambda is the center wavelength for the antenna.
  • the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may be an antenna structure having a circumference of substantially lambda/2 or any multiple thereof.
  • the antenna structure may be a circular antenna structure, an annular or ringshaped antenna structure, or the antenna structure may be any closed antenna structure having a circumference of substantially lambda/2.
  • the closed structure may be a solid structure, a strip like structure having an opening in the center, etc. and/or the closed structure may have any shape and be configured so that the current sees a length of lambda/2.
  • the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may extend in a plane being substantially parallel to a side of the head when the hearing aid is worn in its operational position by a user.
  • the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may be planar antennas extending only in the plane being substantially parallel to a side of the head, or the first resonant structure and/or the second resonant structure may primarily extend in the plane being substantially parallel to a side of the head, so that the resonant structures may exhibit e.g. minor, as compared to the overall extent of the resonant structure, folds in a direction not parallel to the side of the head.
  • the area of the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may be maximized relative to the size of the hearing aid to for example increase the bandwidth of the antenna.
  • the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may be a solid structure extending over the entire side of the hearing aid, or at least extending over a large part of the side of the hearing aid, furthermore, the circumference of the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may be maximized allowing for an opening in the structure to accommodate e.g. a hearing aid battery, electronic components, or the like.
  • the part of the antenna extending proximate the first and/or extending proximate a second side of the hearing aid may form part of a hearing aid housing encompassing at least a part of the hearing aid.
  • the hearing aid may have a partition plane, such as a plane of intersection, extending between the first side and the second side of the hearing aid. At least a part of the antenna may intersect the partition plane so that there is a first distance from the first feed point to the partition plane and a second distance from the second feed point to the partition plane. The first distance and the second distance may be substantially the same so that the first and second feed points are provided substantially symmetrically with respect to the partition plane. A relative difference between the first distance and the second distance may be less than or equal a first threshold, such as less the than 25%, such as less than 10%, such as about 0.
  • a first threshold such as less the than 25%, such as less than 10%, such as about 0.
  • the partition plane may be any plane partitioning the hearing aid, such as a plane parallel to the first and/or second side of the hearing aid, such as a plane parallel to the side of a head when the hearing aid is worn in its operational position on the head of a user.
  • the partition plane may form a symmetry plane for the antenna, so that for example the first resonant structure is symmetric with the second resonant structure with respect to the partition plane.
  • the first distance and the second distance may be measured along a shortest path between the first feed point and the partition plane, and the second feed point and the partition plane, such that the distance is the shortest physical distance.
  • the first distance and the second distance may be the distance as measured along a current path between the first or second feed point and the partition plane.
  • the part of the antenna extending proximate the first side of the hearing aid and/or the part of the antenna extending proximate the second side of the hearing aid may form a first resonant structure and a second resonant structure, respectively.
  • the current flowing in a resonant antenna structure forms standing waves along the length of the antenna; and for proper operation, the resonant antenna structure is operated at, or approximately at, a resonance frequency at which the length of the linear antenna equals a quarter wavelength of the emitted electromagnetic field, or any odd multiple, thereof.
  • the first and second resonant structures may be resonant around a center frequency, i.e. around the resonance frequency for the antenna, and typically, the resonant antenna structure may be resonant within a given bandwidth around the center frequency.
  • the first resonant structure and/or the second resonant structure may be actively fed resonant structures.
  • the term actively fed resonant structure encompasses that the resonant structure is electrically connected to a source, such as a radio, such as a transceiver, a receiver, a transmitter, etc.
  • the first and second resonant structures may be driven structures, such as driven resonant structure, such as a driven resonant antenna structure.
  • the actively fed resonant structure is opposed to the passive antenna structure which is not electrically connected to the surroundings.
  • the first resonant structure and the second resonant structure may in some embodiments be fed symmetrically.
  • the first feed point and the second feed point are configured with respect to the short circuit so as to obtain a desired antenna impedance.
  • a distance between the first feed point and the short circuit along the first resonant structure may be configured to achieve the desired impedance
  • a distance between the second feed point and the short circuit along the second resonant structure may be configured to achieve the desired impedance.
  • the overall physical length of the antenna may be decreased by interconnecting the antenna with an electronic component, a so-called antenna shortening component, having an impedance that modifies the standing wave pattern of the antenna thereby changing its effective length.
  • the required physical length of the antenna may for example be shortened by connecting the antenna in series with an inductor or in shunt with a capacitor.
  • the antenna may be configured for operation in the ISM frequency band.
  • the antenna is configured for operation at a frequency of at least 1 GHz, such as at a frequency between 1.5 GHz and 3 GHz such as at a frequency of 2.4 GHz.
  • an antenna system configured to be worn on a body of a user
  • the antenna system comprises a transceiver for wireless data communication interconnected with an antenna for emission and reception of an electromagnetic field.
  • the antenna may extend on a first side of the hearing aid and a second side of the hearing aid.
  • a first segment of the antenna may extend from proximate the first side of the hearing aid to proximate the second side of the hearing aid and a feed system may be provided for exciting the antenna to thereby induce a current in at least the first segment.
  • the feed system may be configured such that the current induced in the first segment has a first local maxima proximate the first side of the hearing aid and a second local maxima proximate the second side of the hearing aid.
  • the current induced on the antenna may reach its maximum on the first segment of the antenna that extends from proximate the first side of the hearing aid to proximate the second side of the hearing aid.
  • the current induced in the first segment may have a first local maximum proximate the first side of the hearing aid and a second local maximum proximate the second side of the hearing aid, depending on the excitation of the antenna.
  • the current induced on the antenna may reach its maximum on the first segment of the antenna that extends from proximate the first side of the hearing aid to proximate the second side of the hearing aid.
  • the current induced in the first segment may have a first local maximum proximate the first side of the hearing aid and a second local maximum proximate the second side of the hearing aid, depending on the excitation of the antenna.
  • the antenna system may be provided in for example a wearable computing device, the wearable computing device having a first side configured to be proximate a users body and a second side configured to be proximate the surroundings when the wearable computing device is worn in the operational position by a user.
  • an electromagnetic field emitted by the antenna propagates along the surface of the body of the user with its electrical field substantially orthogonal to the surface of the body of the user.
  • the body external transceiver may be a processing unit and may be configured to be connected to an operator, an alarm service, a health care provider, a doctors network, etc., either via the internet or any other intra- or interconnection between a number of computers or processing units, either continuously or upon request from either a user, an operator, a provider, or a system generated trigger.
  • the electromagnetic field emitted by the antenna propagates primarily along the surface of the head or body of the user.
  • the current flowing in a resonant antenna structure forms standing waves along the length of the antenna; and for proper operation, the resonant antenna structure is operated at, or approximately at, a resonance frequency at which the length of the linear antenna equals a quarter wavelength of the emitted electromagnetic field, or any odd multiple, thereof.
  • the radiation pattern of an antenna is typically illustrated by polar plots of radiated power in horizontal and vertical planes in the far field of the antenna.
  • the plotted variable may be the field strength, the power per unit solid angle, or directive gain.
  • the peak radiation occurs in the direction of maximum gain.
  • Fig. 1 is a phantom head model of a user seen from the front together with the ordinary rectangular three dimensional coordinate system.
  • the human head can be approximated by a rounded enclosure with sensory organs, such as the nose, ears, mouth and eyes attached thereto.
  • a rounded enclosure 3 is illustrated in Fig. 1 .
  • the phantom head model is shown from the front together with an ordinary rectangular three dimensional coordinate system with an x, y and z axis for defining orientations with relation to the head and for defining the geometrical anatomy of the head of the user;
  • Every point of the surface of the head has a normal and tangential vector.
  • the normal vector is orthogonal to the surface of the head while the tangential vector is parallel to the surface of the head.
  • An element extending along the surface of the head is said to be parallel to the surface of the head, likewise a plane extending along the surface of the is said to be parallel to the surface of the head, while an object or a plane extending from a point on the surface of the head and radially outward from the head into the surrounding space is said to be orthogonal to the head.
  • the point with reference numeral 2 in Fig. 1 furthest to the left on the surface of the head in Fig. 1 has tangential vectors parallel to the yz-plane of the coordinate system, and a normal vector parallel to the x-axis.
  • the y-axis and z-axis are parallel to the surface of the head at the point 2 and the x-axis is orthogonal to the surface of the head at the point 2.
  • the user modeled with the phantom head of Fig. 1 is standing erect on the ground (not shown in the figure), and the ground plane is parallel to xy-plane.
  • the torso axis from top to toe of the user is thus parallel to the z-axis, whereas the nose of the user is pointing out of the paper along the y-axis.
  • the axis going through the right ear canal and the left ear canal is parallel to the x-axis in the figure.
  • This ear to ear axis (ear axis) is thus orthogonal to the surface of the head at the points where it leaves the surface of the head.
  • the ear to ear axis as well as the surface of the head will in the following be used as reference when describing specific configurations of the elements of the present invention.
  • the auricle of the ear is primarily located in the plane parallel to the surface of the head on most test persons, it is often described that the ear to ear axis also functions as the normal to the ear. Even though there will be variations from person to person as to how the plane of the auricle is oriented.
  • the in the ear canal type of hearing aid will have an elongated housing shaped to fit in the ear canal.
  • the longitudinal axis of this type of hearing aid is then parallel to the ear axis, whereas the face plate of the in the ear type of hearing aid will typically be in a plane orthogonal to the ear axis.
  • the behind the ear type of hearing aid will typically also have an elongated housing most often shaped as a banana to rest on top of the auricle of the ear.
  • the housing of this type of hearing aid will thus have a longitudinal axis parallel to the surface of the head of the user.
  • FIG. 2 A block-diagram of a typical (prior-art) hearing instrument is shown in Fig. 2 .
  • the hearing aid 20 comprises a microphone 21 for receiving incoming sound and converting it into an audio signal, i.e. a first audio signal.
  • the first audio signal is provided to a signal processor 22 for processing the first audio signal into a second audio signal compensating a hearing loss of a user of the hearing aid.
  • a receiver 23 is connected to an output of the signal processor 22 for converting the second audio signal into an output sound signal, e.g. a signal modified to compensate for a users hearing impairment, and provides the output sound to a speaker 24.
  • the hearing instrument signal processor 22 may comprise elements such as amplifiers, compressors and noise reduction systems etc.
  • the hearing instrument or hearing aid may further have a feedback loop 25 for optimizing the output signal.
  • the hearing aid may furthermore have a transceiver 26 for wireless data communication interconnected with an antenna 27 for emission and reception of an electromagnetic field.
  • the transceiver 26 may connect to the hearing instrument processor 22 and an antenna, for communicating with external devices, or with another hearing aid, located at another ear, in a binaural hearing aid system.
  • the antenna and the antenna configurations may be contemplated.
  • the obstacle is a head with a hearing aid comprising an antenna located closed to the surface of the head. If the wavelength is too long such as a frequency of 1 GHz and down to lower frequencies greater parts of the head will be located in the near field region. This results in a different diffraction making it more difficult for the electromagnetic field to travel around the head. If on the other hand the wavelength is too short, the head will appear as being too large an obstacle which also makes it difficult for electromagnetic waves to travel around the head. An optimum between long and short wavelengths is therefore preferred. In general the ear to ear communication is to be done in the band for industry, science and medical with a desired frequency centred around 2.4 GHz.
  • the described antenna structure may be equally applied in all other types of hearing aids, including in-the-ear hearing aids, as long as the conducting segment, or first segment, is configured to guide the current in a direction parallel to an ear-to-ear axis of a user, when the user is wearing the hearing aid in the operational position and furthermore, equally applied to other body wearable devices, as long as the first segment is configured to guide the current in a direction orthogonal to a surface of the body, when the user is wearing the hearing aid in the operational position.
  • various sections of the antenna can be formed with many different geometries, they can be wires or patches, bend or straight, long or short as long as they obey the above relative configuration with respect to each other such that at least one conducting segment will carry a current being primarily parallel to the ear axis (orthogonal to the surface of the head 1 of the user at a point 2 in proximity to the ear) such that the field will be radiated in the desired direction and with the desired polarization such that no attenuation is experienced by the surface wave travelling around the head.
  • the obstacle is a head with a hearing aid comprising an antenna located closed to the surface of the head. If the wavelength is too long such as a frequency of 1 GHz and down to lower frequencies greater parts of the head will be located in the near field region. This results in a different diffraction making it more difficult for the electromagnetic field to travel around the head. If on the opposite side the wavelength is too short the head will appear as being too large an obstacle which also makes it difficult for electromagnetic waves to travel around the head. An optimum between long and short wavelengths is therefore preferred. In general the ear to ear communication is to be done in the band for industry, science and medical with a desired frequency centred around 2.4 GHz.
  • a hearing aid 30 is shown schematically, the hearing aid 30 is a hearing aid of the type to be worn behind the ear, typically referred to as a behind the ear hearing aid, or a BTE hearing aid.
  • the hearing aid 30 comprises a battery 31, a signal processor 32, a sound tube 33 connecting to the inner ear, a radio or transceiver 34, transmission lines 35, 36 for feeding the antenna 37.
  • the hearing aid has a first side 38 and a second side 39.
  • the antenna proximate the first side of the hearing aid, i.e. a first part, 40 extends along or proximate the first side 38 of the hearing aid, and the antenna proximate the second side of the hearing aid, i.e.
  • a second part, 41 extend along or proximate a second side 39 of the hearing aid 30.
  • the first part of the antenna 40 may in one or more embodiments be a first resonant structure provided proximate the first side 38 of the hearing aid, and the second part of the antenna 41 may in one or more embodiments a second resonant structure provided proximate a second side 39 of the hearing aid.
  • a first segment 42 short circuits the first part 40 and the second part 41 to provide a current bridge between the first side of the hearing aid and the second side of the hearing aid.
  • the first part 40 is fed via transmission line 35 to feed point 43 and is thus an actively fed part 40.
  • the second part 41 is fed via transmission line 36 to feed point 44 and thus forms a second actively fed part 41.
  • the feed system for the antenna may thus comprise the first and second transmission lines 35, 36 and first and second feed points 43, 44 for feeding antenna 37.
  • a hearing aid 30 is shown schematically, wherein the width 45 of the first part 40 of the antenna 37 and the second part 41 of the antenna 37 is increased to increase the bandwidth of the antenna 37.
  • a hearing aid 30 is shown schematically, wherein the antenna 37 is folded around the hearing aid 30, and thus the antenna extends along the first side 38 and the second side 39.
  • Fig. 6 shows a further embodiment of the invention, wherein the hearing aid 30 has an antenna 37 having a first part 61 and a second part 62.
  • the first part 61 and/or second part 62 are closed antennas having a width 63 allowing for an opening 64 to be formed within the antenna 37.
  • the opening may allow for configuring the antenna so as not to extend over battery 31 and other larger electrical components.
  • the first part 61 and/or the second part 62 may have any width and/or any shape configured according to hearing aid restrictions and/or antenna optimization.
  • the circumference of the first and/or second parts 61, 62 is approximate lambda/2, where lambda is the resonance wavelength for the antenna 37.
  • the first segment 65 short circuits the first part 61 and the second part 62 thereby creating a current bridge along the first segment 65. It is seen that the current bridge forms an elongated structure, and is positioned so that the elongated structure has a direction substantially orthogonal to the surface of the head, that is substantially parallel to an ear-to-ear axis of a user when the hearing aid is positioned in its operational position behind the ear of a user.
  • Fig. 7 shows a further shape of the antenna 37, wherein the first part 40 and the second part 41 has a meander form of the antenna.
  • first segment in Figs. 3-7 is shown as being orthogonal to the surface of the head, also other configurations may be applied, so that the first segments form a non-perpendicular angle with the surface of the head, such as an angle of between 90° and 45°, such as between 90° and 80°.
  • the current will show at least a current component in the direction being orthogonal to the surface of the head.
  • first part 40, 61 and the second part 41, 62 are shown to be identical in Figs. 3-7 , it is envisaged that the shapes of the first part 40, 61 and the second parts 41, 62 may differ.
  • FIGs. 8a-e schematic antennas 80 are shown, illustrating the feed points 83, 84 and the length of the first and second parts 40, 41, 61, 62 and the distances ⁇ between the feed points 83, 84 and the short circuit.
  • an antenna 80 is shown.
  • the antenna has a first part 85 and a second part 86 and a transceiver 82 located between the first side and the second side.
  • First transmission line 87 feeds the first part 85 in a feed point 83
  • second transmission line 88 feeds the second part 86 in a feed point 84.
  • the first segment 89 extends from the first part 85 to the second part 86 and short circuits the first and second parts 85, 86. In that the antenna is balanced, the current in the short circuit will be maximized.
  • the distance ⁇ along the first part 85 between the first feed point 83 and the short circuit 89 is tailored to the desired impedance for the antenna, and the length I of the first part 85 is measured from the short circuit 89 to the free end of the antenna 90 and is lambda/4 in order for the first part to form a resonant antenna structure.
  • the distance ⁇ along the second part 86 between the second feed point 84 and the short circuit 89 is tailored to the desired impedance for the antenna, and the length I of the second part 86 is measured from the short circuit 89 to the free end of the antenna 91 and is lambda/4 in order for the second part to form a first resonant structure.
  • the first resonant structure 85 is actively fed in the feed point 83 and second resonant structure 86 is actively fed in the feed point 84.
  • Fig. 8b shows another embodiment, in which the first and second parts 85, 86 extends a length of lambda/4 on both sides of the short circuit.
  • Fig. 8c shows a further embodiment, in which the antenna 80 extends around the sides of the hearing aid.
  • the length of the sides is larger than lambda/4.
  • Fig. 8d shows a further embodiment in which the short circuit 89 is provided on another side of the transceiver 82.
  • the length of the first part 85 is measured from the short circuit 89 to the free end 90, and is lambda/4 to form a first resonant structure.
  • the length of the second part 86 is measured from the short circuit 89 to the free end 90, and is lambda/4 to form a second resonant structure.
  • the antenna 80 may extend beyond the feed points 83, 84, however, the length of this extension is typically minimized.
  • Fig. 8e shows an embodiment having a closed antenna structure 80 having a first part 95 and a second part 96.
  • the length of the first and second closed part is lambda/2 to obtain a resonant structure.
  • the widths of the first part 95 and the second part 96 may be tailored according to a desired antenna impedance.
  • Figs. 9a-b show how the length of the antenna may be measured along the current path in the first and second parts.
  • the first part is a wide antenna structure
  • the length along a top part is lambda/8
  • the length along a side part is lambda/8, thus having a total length along the current path of lambda/4.
  • Fig. 9b shows an example of thinner first and second parts, wherein the length of the first part along the current path is lambda/4.
  • Figs. 10a-d shows the current along an antenna 40, 80.
  • the current is seen to be zero at the free ends 90 of the antenna. It is furthermore seen that the maximum current is found along the first segment or the conducting segment 42, 89.
  • Fig. 10a showing a wide BTE hearing aid, that is a relatively long current bridge or first segment, the current exhibits two local maxima at each side of the short circuit with a slight decrease towards the middle.
  • the BTE hearing aid is a narrow hearing aid
  • the current may as shown in Fig. 10c , be substantially constantly high across the short circuit or the first segment.
  • the current is maximized in a direction being substantially orthogonal to the side of the head.
  • the first segment, or the conducting segment may have a have a length being between at least one sixteenth wavelength and a full wavelength of the electromagnetic field.
  • Figs. 11a-d show different embodiments of a partition plane 110 partitioning the antenna 80.
  • the antenna 80 is seen to intersect the partition plane 110 at an intersection 111, thus, the antenna may intersect at least at a point 111, or along an axis of the antenna extending through the plane 110.
  • the distances d1, d2 from the feed points 83, 84, to the intersection 111, respectively may be measured along the current path as shown in Figs. 11a and 11c , or the distances d1 and d2 may be measured along the shortest distance from the feed points 83, 84, to the intersection 111.
  • the partition plane 110 may be a symmetry plane 110 for the antenna so that the first part 85 of the antenna is symmetric with the second part 86 of the antenna with respect to the symmetry plane 110.
  • the partition plane 110 may extend exactly mid through the hearing aid, or the partition plane may extend anywhere between a first side of the hearing aid and a second side of the hearing aid. In one or more embodiments, the partition plane extends through the receiver.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Support Of Aerials (AREA)

Claims (15)

  1. Prothèse auditive en arrière de l'oreille (30), comprenant
    un microphone pour la réception du son et la conversion du son reçu en un premier signal audio correspondant,
    un processeur de signal (32) pour traiter le premier signal audio en un deuxième signal audio en compensation d'une perte auditive d'un utilisateur de la prothèse auditive,
    un récepteur qui est relié à une sortie du processeur de signal pour convertir le deuxième signal audio en un signal sonore de sortie,
    un émetteur-récepteur (34) pour une communication de données sans fil inter-connectée avec une antenne (37) pour émettre et recevoir un champ électromagnétique, l'antenne s'étendant sur un premier côté (38) de la prothèse auditive et un deuxième côté (39) de la prothèse auditive,
    un premier segment de l'antenne (42) s'étendant depuis le premier côté de la prothèse auditive jusqu'au deuxième côté de la prothèse auditive,
    un système d'alimentation (35, 36, 43, 44) pour exciter l'antenne de manière à induire un courant dans au moins le premier segment,
    caractérisée en ce que le système d'alimentation est configuré si bien que le courant induit dans le premier segment présente un premier maximum local au premier côté de la prothèse auditive et un deuxième maximum local au deuxième côté de la prothèse auditive.
  2. Prothèse auditive selon la revendication 1, dans laquelle l'antenne est une antenne équilibrée.
  3. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle une partie de l'antenne s'étendant le long du premier côté de la prothèse auditive est essentiellement identique à une partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive.
  4. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle le système d'alimentation comprend un premier point d'alimentation pour exciter au moins l'antenne s'étendant le long du premier côté de la prothèse auditive et un deuxième point d'alimentation pour exciter au moins l'antenne s'étendant le long du deuxième côté de la prothèse auditive.
  5. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle le premier segment présente une direction essentiellement orthogonale à la surface de la tête d'un utilisateur lorsque la prothèse auditive est portée dans sa position opérationnelle par un utilisateur.
  6. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle le premier segment court-circuite la partie de l'antenne s'étendant le long du premier côté de la prothèse auditive et la partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive pour fournir un pont de courant entre le premier côté de la prothèse auditive et le deuxième côté de la prothèse auditive.
  7. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle la partie de l'antenne s'étendant le long du premier côté de la prothèse auditive et / ou la partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive présente la forme d'une structure monopôle d'antenne.
  8. Prothèse auditive selon l'une quelconque des revendications 6 à 7, dans laquelle une longueur de la partie de l'antenne s'étendant le long du premier côté de la prothèse auditive et / ou une longueur de la partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive telle que mesurée à partir du court-circuit jusqu'à une extrémité libre est essentiellement lambda/4.
  9. Prothèse auditive selon l'une quelconque des revendications 1 à 6, dans laquelle la partie de l'antenne s'étendant le long du premier côté de la prothèse auditive et / ou la partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive présente une circonférence de lambda/2.
  10. Prothèse auditive selon l'une quelconque des revendications 1 à 6, dans laquelle l'antenne est une structure d'antenne fermée en forme de bande, telle qu'une structure d'antenne en forme d'annulaire, ayant une circonférence de lambda/2.
  11. Prothèse auditive selon l'une quelconque des revendications précédentes, dans laquelle la partie de l'antenne s'étendant le long du premier côté de la prothèse auditive est une première structure résonnante, et / ou la partie de l'antenne s'étendant le long du deuxième côté de la prothèse auditive est une deuxième structure résonnante.
  12. Prothèse auditive selon l'une quelconque des revendications 4 à 11, dans laquelle la prothèse auditive comporte un plan de séparation s'étendant entre le premier côté de la prothèse auditive et le deuxième côté de la prothèse auditive, et dans laquelle au moins une partie de l'antenne coupe la plan de partition, et dans laquelle une différence relative entre une distance allant du premier point d'alimentation à l'intersection et une distance allant du deuxième point d'alimentation à l'intersection est inférieure ou égale à un premier seuil.
  13. Prothèse auditive selon la revendication 12, dans laquelle le plan de partition est un plan de symétrie pour les première et deuxième structures d'antenne.
  14. Prothèse auditive selon l'une quelconque des revendications 11 à 13, dans laquelle le seuil est inférieur à 25 %, tel que 0.
  15. Prothèse auditive selon l'une quelconque des revendications 4 à 14, dans laquelle respectivement une distance entre le premier point d'alimentation et le court-circuit, et une distance entre le deuxième point d'alimentation et le court-circuit sont adaptées en fonction d'une impédance d'antenne souhaitée.
EP13175258.6A 2012-07-06 2013-07-05 Prothèse auditive BTE possédant une antenne équilibrée Active EP2723101B1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
DK18202039.6T DK3468230T3 (da) 2012-07-06 2013-07-05 BTE-høreapparat med en balanceret antenna
EP18202039.6A EP3468230B1 (fr) 2012-07-06 2013-07-05 Prothèse auditive bte possédant une antenne équilibrée

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DKPA201270410A DK201270410A (en) 2012-07-06 2012-07-06 BTE hearing aid with an antenna partition plane
DKPA201270411A DK201270411A (en) 2012-07-06 2012-07-06 BTE hearing aid having two driven antennas
DKPA201270412 2012-07-06

Related Child Applications (1)

Application Number Title Priority Date Filing Date
EP18202039.6A Division EP3468230B1 (fr) 2012-07-06 2013-07-05 Prothèse auditive bte possédant une antenne équilibrée

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EP2723101A2 EP2723101A2 (fr) 2014-04-23
EP2723101A3 EP2723101A3 (fr) 2014-06-04
EP2723101B1 true EP2723101B1 (fr) 2018-10-24

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Also Published As

Publication number Publication date
EP3468230A1 (fr) 2019-04-10
EP2723101A3 (fr) 2014-06-04
EP2723101A2 (fr) 2014-04-23
DK2723101T3 (en) 2019-02-04
EP3468230B1 (fr) 2022-06-29
DK3468230T3 (da) 2022-08-29

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