Classifications

• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/48—Electric hearing aids using constructional means for obtaining a desired frequency response
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
  • H04R25/603—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of mechanical or electronic switches or control elements
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
  • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
  • H04R25/609—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of circuitry
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R1/00—Details of transducers, loudspeakers or microphones
  • H04R1/20—Arrangements for obtaining desired frequency or directional characteristics
  • H04R1/22—Arrangements for obtaining desired frequency or directional characteristics for obtaining desired frequency characteristic only 
  • H04R1/225—Arrangements for obtaining desired frequency or directional characteristics for obtaining desired frequency characteristic only  for telephonic receivers
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
  • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
  • H04R25/456—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback mechanically
• • H—ELECTRICITY
  • H04—ELECTRIC COMMUNICATION TECHNIQUE
  • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
  • H04R25/00—Electric hearing aids
  • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
  • H04R25/607—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of earhooks

Definitions

• the present invention relates to an electrical / acoustic transducer module for behind-the-ear or in-the-ear hearing aids according to the preamble of claim 1, further an in-the-ear hearing aid according to the
• the loudspeaker housing is not connected to the auditory canal by a mechanically rigid bridge. This is to prevent acoustic feedback from the loudspeaker to the input-side microphone as far as possible. Furthermore, the space available for hearing aids is generally extremely limited and must be used optimally.
• the motor-driven loudspeaker diaphragm and motor driver are mounted therefor.
• the membrane or the motor drivers for this are mounted with respect to the mentioned loudspeaker housing in such a way that the signals acoustically excited by the membrane are transmitted directly to the mentioned housing.
• the arrangement mentioned is mounted in an in-the-ear hearing device housing in such a way that the loudspeaker housing is spaced apart as far as possible from the hearing device housing mentioned, and this means that only acoustic noise is reduced
• the electrical / acoustic converter module is characterized by the characterizing part of claim 1.
• the loudspeaker housing is resiliently mounted in the encapsulation housing makes it possible to install the transducer module in a behind-the-ear or in-the-ear hearing aid, be it positively or even non-positively. Furthermore, the space between the loudspeaker housing and the hearing aid housing, which was necessary anyway, is now used to determine the behavior of the
• the encapsulation housing acts as a magnetic shield and is preferably made of ⁇ -metal for this purpose.
• the cup-shaped part mentioned - after insertion of the loudspeaker housing with loudspeaker - is closed by means of a terminating part which has the acoustic output of the transducer arrangement.
• the mentioned end part comprises, as an acoustic output, an opening, by means of which the first space on one side of the loudspeaker membrane, that is, the one which is connected to the acoustic output of the transducer arrangement, is connected by means of a membrane.
• voltage is separated from the environment.
• the membrane is freely exposed over the opening area.
• the cup is completed by means of a stocking-like rubber-elastic closure.
• the membrane provided according to the invention in the preferred embodiment mentioned is installed in a freely oscillating manner and is not driven by a motor.
• Dimensioning of the acoustically effective spaces provided according to the invention and the membrane characteristics, in the sense of acoustic impedance matching, which is familiar to the person skilled in the art means that the membrane mentioned has hardly any effect on the acoustic transmission behavior of the hearing device on the output side of the loudspeaker.
• At least the exposed part of the membrane is materially homogeneous, i.e. made from a material phase, and further preferably has a constant thickness. This means that the design effort for the membrane mentioned is extremely low and the acoustic behavior of the membrane is clear.
• At least the exposed part of the above-mentioned membrane made of rubber-elastic material, such as, for example, latex or silicone rubber, is extremely inexpensive and has a uniform, low thickness, is resistant and behaves in contact with the living Fabric harmless materials.
• the membrane is preferably airtight. Its thickness is preferably d ⁇ 0.09 mm.
• the loudspeaker housing be clamped in the encapsulation housing by means of elastic bearing blocks.
• the loudspeaker housing is enclosed on all sides by the mentioned space.
• the in-the-ear hearing device according to the invention has an electrical / acoustic transducer arrangement of the type described above.
• the possibility of simple assembly is now exhausted by the fact that the encapsulation housing of the converter module is positioned in the hearing device housing in a positive and / or non-positive manner.
• the acoustic output of the transducer module can be connected to the acoustic output opening of the device housing by means of a hose connector.
• a membrane clamped for free, unimpaired oscillation is provided in any case, which before separating the device environment from the first room on the converter module used according to the invention.
• This membrane can obviously be formed by the aforementioned membrane on the converter arrangement according to the invention itself, but does not have to, in any case the preferred embodiments made in this regard apply.
• the membrane mentioned is attached directly in the region of the acoustic output of the device housing. This prevents any contamination from penetrating not only into the transducer module, but also into the transducer input on the hearing aid itself.
• the acoustic output of the transducer module according to the invention is therefore essentially provided directly at the output opening of the hearing device housing, so that the membrane mentioned, if preferably provided, is located directly on the hearing device housing environment on the one hand and directly at the output of the transducer module on the other hand is provided.
• this solves the dirt trap problem of an exit opening provided on the hearing aid by closing it directly by the membrane mentioned, on the other hand there is the possibility of optimizing the acoustic behavior in such a way that no additional intermediate transmission links from the acoustic Output of the converter module must be provided for the acoustic output of the device.
• the remaining acoustic transmission path can only be implemented on the basis of acoustic impedance matching.
• the acoustic output opening of the hearing device housing is formed by a section, for example welded or glued, connected to the rest of the hearing device housing.
• This embodiment is also preferred proposed that the above-mentioned exit opening be closed by means of a membrane which, however, is now preferably formed in one piece with the above-mentioned part.
• the above-mentioned statements also apply to this membrane, which means that the above-mentioned part preferably consists of rubber-elastic material, for example of latex or silicone rubber.
• the method according to the invention for producing a hearing device is characterized in that the transducer module is positively or non-positively positioned in the hearing device housing. This makes it possible to position the transducer module precisely in the hearing aid housing with little effort, or even to force-fit it between parts of the hearing aid housing or e.g. to cast the converter module with the hearing aid housing.
• the transducer module is now inserted into the hearing aid housing through an opening forming the acoustic output of the hearing aid housing, that is to say from below.
• This provides the basis for a further preferred procedure, namely that the transducer module is positioned in a receiving opening of a support plate and the transducer module is introduced into the hearing aid housing from the end forming the acoustic output of the hearing aid housing by relative movement of the support plate and the hearing aid housing.
• the method of automation that opens up is immediately clear to the person skilled in the art: the corresponding number of transducer modules are positioned in a plurality of receiving openings in the carrier plate mentioned and these are inserted from below into a corresponding number of device housings in-the-ear hearing aids.
• the carrier plate is subsequently used as part of the device housing by connecting it to the device housing, preferably by gluing or welding, and then separating the carrier plate along the outer contour of the hearing device housing.
• the receiving opening for the converter module is formed on the carrier plate as a sack opening, which makes it possible, in a further preferred embodiment, to design the bottom part of the sack opening as the membrane mentioned above, with the carrier plate in one piece. or applied to the carrier plate as a film-like structure.
• the carrier plate is made of material which meets the requirements for the membrane material, i.e. preferably of rubber-elastic material, e.g. made of latex or silicone rubber.
• FIG. 1 shows the diagram of a converter module according to the invention
• FIG. 2a shows a schematic illustration of a further preferred embodiment of the converter module according to the invention.
• FIG. 3 further shows schematically the installation of a converter module according to the invention on an in-the-ear hearing aid
• FIG. 4 in a representation analogous to that of FIG. 3, a further possibility of installing a converter module according to the invention on an in-the-ear hearing aid;
• FIGS. 3 and 4 show a representation analogous to FIGS. 3 and 4, a further preferred embodiment variant of the part of an in-the-ear hearing device forming the acoustic device output, and
• the converter module 1 shows, schematically, a converter module for the basic explanation of the acoustic coupling ratios.
• the converter module 1 comprises a loudspeaker housing 3, in which the loudspeaker membrane 5 is mounted.
• the loudspeaker diaphragm 5 is excited by a motor drive 7, which is only shown schematically.
• a front space R x and a rear space R 2 are formed by the loudspeaker membrane 5.
• One of the two rooms mentioned, for example the rear R 2 is acoustically coupled to an intermediate space 11 via acoustic decoupling openings 9, formed between the loudspeaker housing 3 and an encapsulating housing 13.
• the encapsulating housing 13 and thus the intermediate space 11 surround the loudspeaker housing 3 essentially completely , except for resilient bearing parts 15, by means of which the loudspeaker housing is spaced within the encapsulation housing 13, is mounted essentially "floating". 1, the front space R x is connected to the acoustic output A A of the converter module 1.
• tion housing 13 an acoustic decoupling of speaker effect on encapsulation housing 13 is achieved. Furthermore, the acoustic behavior of the transducer module 1 is significantly improved compared to that of the loudspeaker arrangement in the housing 3 by a notable enlargement of the rear membrane space R 2 , namely now including the intermediate space 11: The low-frequency behavior of the transducer module is increased by several dB. compared to that of the loudspeaker arrangement in the housing 3.
• a diaphragm is provided on the acoustic output A A , as shown schematically at 17.
• the membrane 17 is free-swinging apart from its marginal clamping. It preferably consists of a homogeneous material phase, preferably of a rubber-elastic material, for example of latex or silicone rubber, and, more preferably, has a constant thickness of approximately 100 ⁇ m, preferably of at most 0.09 mm.
• the membrane 17 is achieved practically acoustically appears transparent.
• the loudspeaker housing 3 with the coupling openings 9 is mounted on the encapsulating housing 13 by means of rubber-elastic bearing blocks 19.
• the encapsulation housing 13 is formed by a cup 20, which preferably also acts as a magnetic shield and preferably consists of ⁇ -metal for this purpose. In any case, the cup 20 is preferably made of metal. lish.
• the cup 20 is closed by a closing part 22.
• the membrane 17 already presented in FIG. 1 can be mounted directly on the end part 22.
• the end part 22 and the membrane 17 can be formed in one piece, but then the material of the end part 22 must meet the material requirements for the membrane, for example with regard to rubber elasticity.
• the entire part 22 is then made of latex or silicone rubber.
• the membrane 17 is anchored as a separate part on the end part 22.
• the membrane 17 can also be provided between the acoustic output A 3 in the loudspeaker housing 3 and the clear opening in part 22.
• the membrane 17, as shown in FIG. 2 is provided flush with the clear opening in the end part 22, so that the entire converter module 1 appears as a self-contained, encapsulated unit and can be easily cleaned. This is particularly important if, as will be shown, the output A A of the converter module 1 is located directly at the acoustic output of a hearing aid.
• the converter module or its encapsulation housing 13 can be cube-shaped, cylindrical or in another, essentially any shape, provided that the required intermediate space 11, essentially enclosing the loudspeaker housing 3, is stretched between the loudspeaker housing 3 and the encapsulation housing 13.
• 2a based on the explanations for FIG. 2, is shown only schematically, a further embodiment.
• a rubber-elastic stocking 17a is pulled over the encapsulation housing 13. It forms the end part 22 and membrane 17 at the same time.
• FIG. 3 schematically shows the section of an in-the-ear hearing aid 24 with the acoustic output opening A 24 .
• the converter module 1 constructed according to FIGS. 1, 2 and 2a is installed within the device housing 26, specifically by it is positively or non-positively, as schematized with the mounting and positioning tabs 28 in Fig. 3, held and positioned in the housing 26 of the hearing aid. This is made possible by the acoustic decoupling of the outer coupling housing 13 with respect to the loudspeaker housing 3, which is realized on the converter module explained with reference to FIGS. 1, 2 and 2a.
• the construction of the in-the-ear hearing device is essentially as previously known, in that the acoustic output of the transducer module 1 is connected to the acoustic output opening A 24 of the device via a pipe socket 30.
• the membrane 17 provided in a preferred embodiment is installed in the immediate area of the acoustic output A 24 on the hearing device housing 26.
• the converter module 1 is mounted in the area of the acoustic output A 24 of the hearing aid 24 or the housing 26 in a positive or non-positive manner, as shown with the schematically illustrated brackets 28a.
• the free-floating membrane 17 is provided at the end.
• the housing 26 of the in-the-ear hearing device 24 is formed on the one hand by a main housing part 24a, but at the end, plate-like, a closing part 24b is attached to the part 24a, glued or welded to the part 24a.
• the or a preferably provided membrane of the type described above is shown in a preferred position. 5, be it for hearing aids with a transducer module according to FIGS. 1, 2, 2a or for hearing aids with previously known transducer arrangements, i.e. with a loudspeaker housing directly outside, significant advantages.
• the membrane 17 can be formed in one piece with the part 24b, in particular because the part 24b which is separated from the rest of the housing 26 can be used to select the material of this part in accordance with the requirements of the membrane 17.
• 6 (a) to 6 (c) schematically show the sequence of a preferred production process for in-the-ear hearing aids.
• receiving openings 36 are provided in a carrier plate 34 and the transducer arrangements 30 to be provided on in-the-ear hearing aids are inserted therein.
• the transducer arrangements 30 are of a known type, ie with an external loudspeaker housing and without an encapsulation housing according to FIGS. 1, 2, 2a, then the transducer arrangements 30 are preferably firmly anchored in the carrier plate 34, for example glued to them. 1, 2, 2a, the arrangements 30 need not be held firmly in the carrier plate 34, since, as has been shown, they can be shown in dashed lines in the corresponding device housings 24a indicated at 28b, held in a positive or non-positive manner.
• the carrier plate 34 can be removed after the transducer arrangements 30 have been pushed into the housing 26, the transducer arrangements or modules are held and positioned in the housings 24a. However, in the case of transducer arrangements without an encapsulating housing, the transducers 30 remain in the openings 36 of the plate 34 provided for this purpose.
• the plate 34 is connected to the housing 24a, e.g. glued or welded, and starting from the position shown in FIG. 6 (b), the plate 34 is then machined flush with the outer housing contour (transition to FIG. 6 (c)).
• the in-the-ear hearing device then arises, as shown in FIG. 5.
• this procedure is also preferably used for converter modules, constructed according to FIGS. 1, 2, 2a, i.e. with encapsulation housing.
• the base plate 38 according to FIG. 6 (a) of the openings 36 which are preferably designed as a bag opening, is formed directly as a membrane. This is done either by selecting the material of the carrier plate 34 in accordance with the requirements for the membrane material and thus the membrane being formed in one piece with the plate 34, or, as shown in dashed lines in FIG. 6 (a), by the sack openings 36 only by laminating the Carrier plate 34, with openings 36 which are then still continuous, are formed with a film-like layer 34b which then forms the membrane 17 according to FIG. 5.
• both converter modules according to FIGS. 1, 2, 2a and conventional converter arrangements i.e. To be installed with an external loudspeaker housing in the in-the-ear hearing aid housing. This from the side of the housing on which the acoustic output is located. This enables a largely automated assembly. If, as preferred, the acoustic hearing aid outlet is to be protected from the environment with regard to contamination and designed to be easy to clean, the possibility is also created at the same time of installing a covering membrane 17, as has been explained.

Landscapes

• Health & Medical Sciences (AREA)
• General Health & Medical Sciences (AREA)
• Neurosurgery (AREA)
• Otolaryngology (AREA)
• Physics & Mathematics (AREA)
• Engineering & Computer Science (AREA)
• Acoustics & Sound (AREA)
• Signal Processing (AREA)
• Headphones And Earphones (AREA)
• Battery Mounting, Suspending (AREA)
• Prostheses (AREA)
• Diaphragms For Electromechanical Transducers (AREA)
• Electrostatic, Electromagnetic, Magneto- Strictive, And Variable-Resistance Transducers (AREA)
• Obtaining Desirable Characteristics In Audible-Bandwidth Transducers (AREA)
• Details Of Audible-Bandwidth Transducers (AREA)
• Finger-Pressure Massage (AREA)
• Reverberation, Karaoke And Other Acoustics (AREA)
• Audible-Bandwidth Dynamoelectric Transducers Other Than Pickups (AREA)

Applications Claiming Priority (3)

Publications (1)

Family

ID=4551682

Family Applications (2)

Family Applications Before (1)

Country Status (10)

Cited By (1)

Families Citing this family (17)

Citations (1)

Family Cites Families (7)

• 1999
  • 1999-06-16 AT AT99924637T patent/ATE499806T1/de active
  • 1999-06-16 AU AU41282/99A patent/AU761764B2/en not_active Ceased
  • 1999-06-16 CA CA002375864A patent/CA2375864C/fr not_active Expired - Fee Related
  • 1999-06-16 CN CNB998168319A patent/CN1196377C/zh not_active Expired - Fee Related
  • 1999-06-16 CN CNB2003101242620A patent/CN100382656C/zh not_active Expired - Fee Related
  • 1999-06-16 EP EP99924637A patent/EP1183907B1/fr not_active Revoked
  • 1999-06-16 DK DK99924637.4T patent/DK1183907T3/da active
  • 1999-06-16 DE DE59915249T patent/DE59915249D1/de not_active Expired - Lifetime
  • 1999-06-16 JP JP2001504722A patent/JP4246432B2/ja not_active Expired - Fee Related
• 2000
  • 2000-06-06 JP JP2001504719A patent/JP2003502966A/ja active Pending
  • 2000-06-06 AU AU47401/00A patent/AU769544B2/en not_active Ceased
  • 2000-06-06 WO PCT/CH2000/000311 patent/WO2000079832A2/fr not_active Ceased
  • 2000-06-06 CA CA002340725A patent/CA2340725C/fr not_active Expired - Fee Related
  • 2000-06-06 EP EP00929194A patent/EP1104646A2/fr not_active Withdrawn
• 2001
  • 2001-02-15 NO NO20010769A patent/NO20010769D0/no unknown

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