WO2012162859A1 - 一种深耳道自适应变形听力装置 - Google Patents

一种深耳道自适应变形听力装置 Download PDF

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Publication number
WO2012162859A1
WO2012162859A1 PCT/CN2011/001084 CN2011001084W WO2012162859A1 WO 2012162859 A1 WO2012162859 A1 WO 2012162859A1 CN 2011001084 W CN2011001084 W CN 2011001084W WO 2012162859 A1 WO2012162859 A1 WO 2012162859A1
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WO
WIPO (PCT)
Prior art keywords
hearing
ear canal
deep
tube
soft
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Application number
PCT/CN2011/001084
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English (en)
French (fr)
Inventor
赵勇
赵金萍
Original Assignee
江苏贝泰福医疗科技有限公司
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Publication of WO2012162859A1 publication Critical patent/WO2012162859A1/zh

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Classifications

    • 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
    • H04R25/65—Housing parts, e.g. shells, tips or moulds, or their manufacture
    • H04R25/652—Ear tips; Ear moulds
    • H04R25/656—Non-customized, universal ear tips, i.e. ear tips which are not specifically adapted to the size or shape of the ear or ear canal

Definitions

  • This invention relates to a hearing device, and more particularly to a deep ear canal hearing device suitable for use in human ear canal of different physiological structure shapes and sizes, and which does not distinguish between left and right ears. Background technique
  • Hearing aids are also known as hearing devices or hearing compensation devices.
  • manufacturers of digital hearing aids generally focus on increasing the power of hearing aids to obtain larger audio output signals or gains, suppress environmental noise, eliminate sound feedback signals, etc. Guarantee the quality of the output signal. In this way, the consequences are: Even if the quality of the output signal is good, the gain that the user effectively receives is small, and the user cannot obtain a better hearing aid effect.
  • custom hearing aids are generally placed on the auricle, the behind-the-ear hearing aids are placed behind the ear. The sound from the speakers is still a considerable distance from the human eardrum. Due to the interaction of acoustic conduction damping and reflection, the sound is in this complex physiology.
  • the loss in the transmission process of the ear canal of the structure generally has a gain loss of nearly 20%-30%, so many patients with severe hearing loss complain that the power of the hearing aid is small and the external sound cannot be clearly distinguished.
  • the industry has invented a full-aesthetic (CIC) hearing aid or an in-the-ear hearing aid to reduce the loss of sound during transmission in the ear.
  • the full-aural hearing aid is a custom-made hearing aid.
  • the ear mold is printed on the ear canal of each hearing-impaired patient at the fitting center, and then the ear mold is sent to the factory for manual processing of the hearing aid housing. Since the body of the hearing aid is not exposed to the outside of the ear, its concealment is the goal pursued by some hearing-impaired patients, but it is due to the occlusion effect, feedback whistling, and hard contact with the ear canal due to its side effects.
  • the fitting center In order to make the fitting center know the same when filling in the "customized machine customer order", it is convenient for the fitting center to select the length of the ear canal made by the customized machine, and improve the success rate of the first fitting of the fitting center.
  • the literature reports a standard definition of the physiological anatomy of the ear canal. Referring to FIG. 1, the ear canal lengths of the short ear canal 21, the middle ear canal 22, the long ear canal 23, and the deep ear canal 24 are explained by FIG.
  • Short ear canal 21 Do not exceed the center line of the first curve a1 and the second curve a2 (generally suitable for hearing aids with good hearing loss and no influence on the appearance of the custom machine, not suitable for the whole ear canal Hearing aid).
  • Middle ear canal 22 More than one corner of the curve and the second curve of the second curve a2, but the second curve a2 (suitable for hearing aids with a slightly better hearing loss, not for full-aural hearing aids).
  • Long ear canal 23 More than one side (mm) of the second curve a2 (applicable to hearing aids with slightly less hearing loss or full-ear hearing aids).
  • an object of the present invention is to provide a deep-ear canal adaptive deformation hearing device, wherein the entire hearing device is stably fixed in the ear canal, and the air in the ear is circulated when worn, and is suitable for human ear canal of different physiological structure shapes and sizes. And regardless of the left and right ears, can adapt to the physiological structure of the ear canal deformation and stable placement in the deep ear canal, the receiver is closer to the human eardrum, reduce gain loss, and improve the comfort of long-term wear.
  • a deep-ear canal adaptive deformation hearing device comprising a body and a hearing conduction device, wherein the body is connected with a hearing conduction device, the hearing conduction device comprising a hearing tube and being fixed inside the hearing tube
  • the hearing tube is prepared by a two-stage three-dimensional bending deformation soft body material suitable for two curves of the ear canal physiological structure, and the hearing tube has a single pole single side bending angle of less than or equal to 75 degrees.
  • the body and the hearing conduction device are connected as a unitary or detachable soft connection, and the body comprises an internal hard plastic shell and an external soft shell, and the soft shell of the body It is sleeved on the outer surface of the hard plastic shell of the body, and the soft shell of the body is made of soft material.
  • the hard plastic shell of the body is made of hard plastic ABS (Acrylonitrile Butadiene St rene ), PP (polypropylen ), PE ( olyethylen ), PC (Polycarbonate ) or PC/ABS polymer.
  • ABS Acrylonitrile Butadiene St rene
  • PP polypropylen
  • PE olyethylen
  • PC PC/ABS polymer
  • One or more of the materials; the material of the soft shell of the body is silicone rubber (Nussil rubber, Nusil Med 4930).
  • part or all of the external soft material of the body and the hearing tube are overmolded or insert molded and the body is tightly assembled, or the body is manufactured and assembled. .
  • the hearing tube has a circular, elliptical, rectangular, square, polygonal, symmetrical or asymmetrical cross section.
  • the soft ear mold and the hearing tube head are provided with a protective net outside the head of the hearing tube, and the outer diameter of the hearing tube head is smaller than the outer diameter of the middle portion of the hearing tube, and the receiver Placed on the inner wall of the middle of the hearing tube, the head of the hearing tube is an elastic soft body structure, and the protective net hearing tube is manufactured and assembled separately.
  • the soft ear mold has a single-stage, multi-stage mushroom type, an umbrella shape or a spiral shape, wherein the soft ear mold is made of silicone rubber (nusil Med). 4930), polyurethane, thermoplastic rubber (TPU rubber), thermoplastic elastomer (TPE) or one or more of silicone and polyurethane polymers, soft ear mold and hearing tube integral injection molding , or after disassembly, manufacture.
  • silicone rubber non-stage, multi-stage mushroom type, an umbrella shape or a spiral shape
  • TPU rubber thermoplastic rubber
  • TPE thermoplastic elastomer
  • a receiver and a gas conduit are mounted in the hearing tube.
  • One end of the air conduit is connected to the receiver, and the other end is connected to the protective net.
  • the air conduit has a wall thickness of 0.01 To 1.5 mm, the material is a single or mixed high molecular polymer having a hardness of between 20 and 80.
  • the polymer is silicone rubber, polyurethane, chloranil rubber or plastic.
  • the protective net is a porous mesh structure made of silicone rubber, polyurethane, chlorinated rubber or plastic.
  • the hearing tube has only a receiver, and the inner wall of the hearing tube and the outer wall of the receiver are tightly airtight, and the inner wall of the head of the hearing tube and the outer wall of the protective net are tightly airtight.
  • the outer surface of the soft shell of the body has all or part of an elastically deformable structure.
  • the deep ear canal adaptive deformation hearing device is further provided with a pull rod, which is attached to the end of the body or integrally molded with the outer layer of the deep ear canal adaptive deformation hearing device;
  • the track adaptive deformation hearing device further includes a battery door, a programming interface, a sound pressure switch and a microphone sound inlet, wherein the programming interface, the sound pressure switch and the microphone sound inlet are all disposed on the battery door, and the sound pressure switch is light
  • the acoustic vibration or sound wave converted electrical signal generated by the ear is used to control the deep ear canal adaptive deformation hearing device.
  • the deep ear canal adaptive deformation hearing device disclosed by the invention is composed of a two-stage three-dimensional bending deformation hearing tube suitable for two curves of the ear canal physiological structure and a receiver fixed inside the hearing tube, so that the hearing conduction device is suitable for
  • Figure 1 is a schematic diagram showing the physiological anatomy of the human ear canal in the literature
  • FIG. 2 is a schematic structural view of a deep ear canal adaptive deformation hearing device according to a preferred embodiment of the present invention
  • FIG. 3 is an exploded perspective view of the deep ear canal adaptive deformation hearing device of the present invention
  • FIG. 4 is a schematic structural view showing the state of use of the embodiment of the ear mold of the present invention.
  • Figure 5 is an assembly view of the internal body of the present invention
  • Figure 6 is a schematic view showing the internal structure of the deep ear canal adaptive deformation hearing device of the present invention
  • FIG. 7 is a schematic structural view of one of the applications of the elastically deformable structure of the present invention.
  • Figure 8 is a schematic structural view of the second application of the elastically deformable structure of the present invention.
  • FIG. 9 is a schematic structural view of the third application of the elastically deformable structure of the present invention.
  • the markings in the figure are: 1 for the hearing device, 2 for the ear canal, 11 for the body, 12 for the hearing conduction device, 13 for the hard plastic shell of the body, 14 for the soft shell of the body, 15 for the hearing tube, 16 for the receiver, 17 for Soft ear mold, 18 is elastic deformable structure, 21 is short ear canal, 22 is middle ear canal, 23 is long ear canal, 24 is deep ear canal, al is first curve, a2 is second curve, 111 For the microphone, 112 is the chip, 113 is the battery, 114 is the circuit bracket, 115 is the protection frame, 116 is the battery door, 117 is the button switch, 118 is the programming interface, and 119 is the drawbar. detailed description
  • FIG. 2 is a schematic structural diagram of a preferred embodiment of a deep-ear canal adaptive deformation hearing device according to the present invention.
  • the deep-ear canal adaptive deformation hearing device 1 mainly includes a body 11 and a hearing conduction device 12. Most of the body 11 is connected to the hearing conduction device 12, which is a one-piece or detachable soft connection.
  • FIG. 3 is a schematic exploded view of the deep ear canal adaptive deformation hearing device of the present invention.
  • the hearing conduction device 12 includes a hearing tube 15 and a receiver 16 fixed inside the hearing tube 15.
  • the hearing tube 15 is made of a soft material of two-stage three-dimensional bending deformation suitable for two curves of the physiological structure of the ear canal, and the single-pole bending angle of the hearing tube is less than or equal to 75 degrees
  • the hearing tube I of the present invention 5 is made of silica gel material
  • the soft ear mold 17 is arranged outside the head of the hearing tube 15 and the protective net 15 is built in the head of the hearing tube 15 (not shown), or there is no soft ear mold 17, the head of the hearing tube 15
  • the outer diameter is smaller than the outer diameter of the middle portion of the hearing tube 15, the receiver 16 is placed on the inner wall of the middle portion of the hearing tube 15, and the head of the hearing tube 15 is an elastic soft body structure.
  • connection between the body 11 and the hearing conduction device 12 in the present invention may be an integral soft connection or Detachable flexible connection
  • the hearing tube 15 is made from silicone material, the inner wall of the receiver 16 placed in the middle of listening tube 15, so I 5 hearing pipe bending segment, the receiver electronics 15 and the inner end of the inner tube portion 11 of the body hearing
  • the 16-connected circuit jacket has a protective hose to protect the wire from breakage or fatigue damage when the hearing tube 15 is deformed multiple times.
  • the body 11 includes an inner plastic case 13 and an outer body soft case 14.
  • the inner body hard plastic case 13 facilitates fixing and protecting internal components and circuits, and the body soft case 14 is set on the body hard plastic.
  • the soft shell 14 of the present invention is made of a soft material, and the soft surface of the soft shell 14 of the body is in elastic contact with the skin of the ear canal and can move with the muscles of the ear canal, is easy to wear for a long time, and is not easy to slide out of the ear canal.
  • the material of the middle body hard plastic shell 13 may be a combination of one or more of hard plastic ABS (Acrylonitrile Butadiene Styrene), PP (polypropylen), PE (polyethylen), PC (Polycarbonate) or PC/ABS polymer.
  • the material of the soft shell 14 is silicone rubber (nusil Med 4930), polyurethane, TPU rubber, thermoplastic elastomer (TPE) or polymer of silica gel and polyurethane.
  • TPE thermoplastic elastomer
  • the material of the body soft shell 14 is made of silica gel.
  • the hearing device 1 of the present invention has a small generality: the body 11 is less than or equal to 15 mm (height) X 10 mm (width) x 8 mm (thickness); the outer surface of the hearing tube I 5 is: the maximum diameter is less than or equal to 6 faces, and the axial length is 10 ⁇
  • the outer diameter of the head of the hearing tube 15 is smaller than the middle outer diameter of 0. lmm or more, the length of the head variable section is 0. 2 faces - 5. 0mm; suitable for different physiological structure shapes and sizes
  • the human ear canal, and regardless of the left and right ears, can adapt to the deformation of the physiological structure of the ear canal, and the entire hearing device 1 is placed in the deep ear canal 24, completely concealed.
  • the entire hearing device 1 in the present invention can be stably fixed in the ear canal 2, and its fixation is mainly provided by the end soft ear mold 17, the body 11 merely provides auxiliary support, and the body 11 is elastically contacted with the ear canal 2, which not only increases
  • the body 11 is suitable for the versatility of the size and shape of the human ear canal 2 and the movement of the muscles of the ear canal 2, and makes the ear canal 2 more breathable.
  • the soft ear mold 17 is in close elastic contact with the wall of the deep ear canal 24 to provide a fixation.
  • the soft ear mold 17 mainly includes two types of open type and closed type, and the open ear mold is suitable for medium and Mild hearing compensation, closed ear molds for severe hearing compensation.
  • the structure of the soft ear mold 17 may be single-stage, multi-pole mushroom type, umbrella shape or spiral shape, and the material thereof may be silicone rubber, polyurethane, thermoelastic polyurethane rubber, thermoplastic elastomer, and polymer of silica gel and polyurethane.
  • the soft ear mold 17 can be detachable or integrally formed with the hearing tube 15, i.e., the soft ear mold 17 can be integrally molded with the hearing tube 15, or can be assembled separately and assembled.
  • the soft ear mold 17 has two types of separate type and closed type, and the soft ear mold ⁇ simultaneously plays a supporting and fixing function; the protective net is assembled and reassembled for detachment, and is detachable for removing dirt.
  • the soft body material of the outer surface of the body 11 and the hearing conduction device 12 can increase the comfort of the hearing device for a long time, and the outer body soft silicone of the body 11 and the hearing tube 15 can be partially or completely overmolded with the body 11 tightly, or manufactured separately. Reassembly (interference fit set or glue assembly).
  • the outer soft shell 14 of the body 11 may be injection molded once, or may be subjected to secondary injection molding or insert molding with the inner hard plastic shell 13 of the inner layer.
  • the inner hard plastic shell 13 of the inner layer may be injection molded, injection molded or quickly printed by a three-dimensional printer; the outer soft shell 14 may partially or completely cover the inner hard plastic shell 13 of the inner layer, and may be passed through an interference suit, Adhesive, overmolding or injection molding methods tie the outer soft body to the inner hard shell.
  • FIG. 4 is a schematic view showing the structure of the ear mold according to the embodiment of the present invention.
  • the special shape and structure design of the deep ear canal adaptive deformation hearing device 1 is suitable for the human ear canal of different physiological structure shapes and sizes.
  • the two-stage large curvature of the hearing conduction device 12 is adapted to the first curve a1 and the second curve a2 of the ear canal, respectively, and is more easily bent and deformed in the horizontal direction, bringing the receiver 16 closer to the eardrum of the human body, reducing gain loss.
  • the hearing tube 15 of the present invention may have a circular, elliptical, rectangular, square, multi-deformed, symmetrical or asymmetrical cross-section, and the hearing tube 15 is connected to the body 11 by structure and material design and manufacture.
  • the structural bending stiffness of the portion is smaller than the stereoscopic direction in the plane direction, so that when the head of the hearing tube 15 is subjected to pressure along the long axis direction of the hearing tube 15 (i.e., when the deep ear canal adaptive deformation hearing device 1 is pushed into the deep ear canal 24, At the corner of the ear canal 2, the head of the hearing tube 15 is in contact with the wall of the ear canal, and the hearing tube 15 is more likely to bend in the horizontal direction, which is consistent with the curve of the ear canal 2 .
  • the soft ear mold 17 can produce a horizontal plane bending deformation at the second curve a2 of the ear canal 2. Since the head of the hearing tube 15 has a soft liner and a protective net built therein, the ear mold and the hearing tube 15 are bent without bending or Folding, that is, the air conduction path between the receiver 16 and the human eardrum.
  • FIG. 5 is an assembly diagram of the inner part of the body 11 of the present invention.
  • the functional components in the body 11 mainly include a microphone 111, a chip 112, a battery 113, a circuit bracket 114, a protective frame 115, a battery door 116, and a switch 117. .
  • the microphone 111 When assembled, the microphone 111 is placed in the circuit holder 114, and the battery 113 is placed in the battery door 116; then the battery door 116 is inserted into the protection frame 115 and then connected to the circuit holder 114 to be connected to form a bracket; the push button switch 117 The tail end is inserted into the battery door 116 to reach the tail end of the microphone 111 of the circuit holder 1", so that the button switch 117 is connected to the microphone 111, and the sound quality of the microphone 111 and the listening environment of the setting are controlled by the button switch 117 or voice control; The chip 112 is connected to the bracket and placed above the battery 113.
  • the above-mentioned functional components realize the functions of turning on and off the hearing aid, receiving, amplifying, filtering, and adjusting the power of the audio signal.
  • FIG. 6 is a schematic diagram showing the internal structure of the deep-ear canal adaptive deformation hearing device of the present invention.
  • the deep ear canal adaptive deformation hearing device 1 of the present invention further comprises a battery door 116, a programming interface 118, a sound pressure switch (not shown) and a microphone 111 sound inlet, a programming interface 118, a deep ear canal adaptive deformation hearing device 1
  • An external programming interface 118, a push button switch 117 or a sound pressure switch (not shown) and a microphone 111 sound inlet are all disposed on the battery door 116.
  • the sound pressure switch refers to the control of the deep ear canal adaptive deformation hearing device 1 by the acoustic vibration or sound wave converted electrical signal generated by tapping the ear.
  • the deep-ear canal adaptive deformation hearing device 1 of the present invention is further provided with a tie rod 120, which may be adhered to the inner and outer layers of the body 11 or the outer surface of the body 11 near the end of the body 11, that is, the battery door 116, or may be deep
  • the ear canal adaptive deformation hearing device 1 is integrally molded by the outer layer.
  • the outer surface of the body soft shell 14 has all or part of the elastic deformable structure 18, that is, the outer surface of the body soft shell 14 has a joint or non-joined elastic deformable structure 18, such as a single or a plurality of protruding spikes, columns, tubes, sheets, etc., which may be radially radiated or longitudinally arranged, may be symmetrically arranged or asymmetrically arranged, and the diameter of the elastically deformable structures 18
  • the length of the length is in the range of 0. 5mm - 4. Omm. 8 and 9, respectively, the elastic deformable structure 18 on the outer surface of the soft shell 14 of the body--a local asymmetric barb; the outer surface of the soft shell 14 of the body The elastic deformation structure 18 on the surface - a partially symmetrical barb.
  • the whole hearing device is stably fixed in the ear canal 2, and the body 11 is in elastic contact with the ear canal 2, which not only increases the size and shape of the body 11 for the human ear canal 2 and the ear.
  • the hearing conduction device 12 comprises a two-stage three-dimensional bending deformation hearing tube 15 suitable for two curves of the physiological structure of the ear canal and a receiver fixed inside the hearing tube 15 16 is composed of human body ear canal 2 which is suitable for different physiological structure shapes and sizes, and is independent of the left and right ears, that is, independent of the three-dimensional physiological structure of the complex ear canal which varies from person to person and from left to right ear.
  • the two-stage large bending of the hearing conduction device 12 is suitable for the first curve a1 and the second curve a2 of the ear canal, respectively, and is easier to be in the horizontal direction. Bending deformation, bringing the receiver 16 closer to the human eardrum, reducing gain loss; the soft ear mold 17 includes both open and closed types, and the open ear mold is suitable for moderate and Severe hearing compensation applicable to dense closed earmould or more severe hearing compensation; Hearing conductive material 12 and the soft outer surface of the body 11 of the apparatus improved comfort in extended wear hearing device.

Abstract

本发明揭示了一种深耳道自适应变形听力装置，包括机体和听力传导装置，所述的机体和听力传导装置连接，所述的听力传导装置包括听力管以及固定于听力管内部的受话器，其中，所述的听力管由适用于耳道生理结构两道弯的两级三维弯曲变形的软体材料制得，所述的听力管的单极单边弯曲角度小于或等于75度。本发明所提供的深耳道自适应变形听力装置，整个听力装置稳定固定在耳道内，佩戴时耳内空气流通，其适用于不同生理结构形状和尺寸的人体耳道，并且不分左右耳，能自适应耳道生理结构变形和稳定置放于深耳道内，受话器更靠近人体耳膜，减少增益损失，并且提高了长期佩戴的舒适性。

Description

说 明 书
一种深耳道自适应变形听力装置
技术领域
本发明涉及一种听力装置， 尤其是涉及一种深耳道听力装置， 适用于不同生 理结构形状和尺寸的人体耳道， 并且不分左右耳。 背景技术
助听器也称为听力装置或者听力补偿装置， 目前生产数字式助听器的厂家 一般都专注于加大助听器功率以获得较大的音频输出信号或增益、 抑制环境噪 声、 消除声音反馈信号等内容， 用来保证输出信号的质量。 如此， 产生的后果 是： 即使输出信号的质量很好， 但是使用者有效接收到的增益很少， 使用者也 不能获得较好的助听效果。 因为定制式助听器一般都放置在耳廓上， 耳背式助 听器放置于耳背后， 扬声器发出的声音距离人体耳膜还有相当一段距离， 由于 声波传导阻尼和反射交互作用， 会导致声音在这段复杂生理结构的耳道中传输 过程中的损失， 一般有将近 20%-30%的增益损失， 因此许多重度听力损失患者抱 怨助听器功率小而不能清晰的分辨外部声音。
为了提高助听器的工作效率， 业界发明了全耳道式（CIC )助听器或耳内式 助听器， 从而减少声音在耳朵内传递过程中的损失。 全耳道式助听器是一种定 制式助听器， 需要先在验配中心对每一个听障患者耳道印制耳模， 然后将耳模 送到工厂手工加工制作助听器壳体。 由于助听器机体没有暴露在耳朵外面， 它 的隐蔽性强是部分听障患者所追求的目标， 但正是由于放置在耳内， 其副作用 产生的闭塞效应、 反馈啸叫、 与耳道全面硬接触不能适应耳道肌肉相对运动而 影响佩戴稳定性、 以及由于三维复杂耳道生理解剖结构使其难以放置到深耳道 等是其主要弊病。 由于体积的限制， 全耳道式助听器的功率通常较小， 不适合 严重听力损失的人士使用。
为了使验配中心在填写 "定制机客户订单" 时能统一认识， 便于验配中心 对定制机制作的耳道长度进行选择， 提高验配中心的首次验配成功率， 特此， 文献报道对耳道生理解剖结构进行标准定义。请参考图 1，通过图 1来解释短耳 道 21、 中耳道 22、 长耳道 23、 深耳道 24等耳道长度。
短耳道 21 : 不超过第一弯道 al与第二弯道 a2的中心线（一般适用于听力 损失较好且不影响定制机配戴外观的助听器选配者， 不适用于全耳道式助听 器）。
中耳道 22:超过笫一弯道 al与第二弯道 a2的中心线，不过第二弯道 a2 (适 用于听力损失略好的助听器选配者， 不适用于全耳道式助听器）。
长耳道 23: 超过第二弯道 a2的 1麵（毫米）左右（适用于听力损失略重或 全耳道式助听器的助听器选配者）。
深耳道 24: 超过第二弯道 a2的 3mm-5隱（适用于听力损失较重， 达到助 听器的验配极限范围的助听器选配者， 不太适用于第二弯道弯 a2度较大、 听力 损失较好或年纪较大的助听器选配者）。
器， 它不需对每个患者的耳道印制耳膜和专门手工制作， 但在耳道内的固定主 要依靠突出端部较大的耳塞， 硬塑料机体与耳道硬接触并随由于讲话、 吃食物、 喝饮料等引起的耳道肌肉运动而滑动。 当前通用型耳内机的主要技术问 ¾ ^无 法深入耳道、 不能消除闭塞效应和反馈啸叫、 佩戴稳定性和舒适度较差。 发明内容
针对上述缺陷， 本发明的目的在于提供一种深耳道自适应变形听力装置， 整个听力装置稳定固定在耳道内， 佩戴时耳内空气流通， 其适用于不同生理结 构形状和尺寸的人体耳道， 并且不分左右耳， 能自适应耳道生理结构变形和稳 定置放于深耳道内， 受话器更靠近人体耳膜， 减少增益损失， 并且提高了长期 佩戴的舒适性。
一种深耳道自适应变形听力装置， 包括机体和听力传导装置， 所述的机体 和听力传导装置连接， 所述的听力传导装置包括听力管以及固定于听力管内部 的受话器， 其中， 所述的听力管由适用于耳道生理结构两道弯的两级三维弯曲 变形的软体材料制得， 所述的听力管的单极单边弯曲角度小于或等于 75度。
在本发明一个较佳实施例中， 所述的机体和听力传导装置连接为整体式或 者可拆卸式软连接， 所述的机体包括内部的机体硬塑料壳和外部的机体软壳， 机体软壳套在机体硬塑料壳的外表面， 机体软壳是由软体材料制得。
在本发明一个较佳实施例中， 所述的机体硬塑料壳的材料为硬塑料 ABS ( Acrylonitrile Butadiene St rene )、 PP ( polypropylen )、 PE ( olyethylen )、 PC ( Polycarbonate )或者 PC/ABS聚合物中的一种或多种； 所述的机体軟壳的材料 为硅橡胶（ silicone rubber, Nusil Med 4930 ). 聚氨酯（polyurethane )、 热弹塑性 聚氨酯橡胶（TPU rubber )、 热塑性弹性体（ TPE )或者硅胶与聚氨酯的聚合物 中的的一种或多种。
在本发明一个较佳实施例中， 所述的机体和听力管的外部软体材料部分或 全部二次注模 ( overmolding )或嵌件成型 ( insert molding )与机体紧密套装， 或分体制造再组装。
在本发明一个较佳实施例中， 所述的听力管的横截面为圆形、 椭圆形、 长 方型、 正方形、 多边形， 对称或者非对称。
在本发明一个较佳实施例中， 所述的听力管头部外设有软耳模和听力管头 部内置有防护网,所述的听力管头部外径小于听力管中部外径， 受话器置于听力 管中部内壁， 听力管头部是弹性软体结构， 所述的防护网听力管为分体制造再 组装。
在本发明一个较佳实施例中， 所述的软耳模的结构为单级、 多级蘑菇型、 伞状或者螺旋状， 其中， 软耳模的的材料为硅橡胶（silicone rubber, Nusil Med 4930 )、 聚氨酯（polyurethane )、 热弹塑性聚氨酯橡胶（ TPU rubber )、 热塑性弹 性体（TPE )或者硅胶与聚氨酯的聚合物中的的一种或多种，软耳模与听力管整 体注模制造， 或分体制造后再組装。
在本发明一个较佳实施例中， 所述的听力管内安装有受话器和气导管。 所 述气导管一端与受话器连接， 另一端与防护网连接。 所述气导管的壁厚为 0.01 至 1.5mm，材料是硬度在 20 至 80之间的单一或混合高分子聚合物。所述聚合物 为硅橡胶、 聚氨酯、 氯酊橡胶或塑料。 所述防护网是一多孔网状结构， 其材料 为硅橡胶、 聚氨酯、 氯酊橡胶或塑料。 在本发明一个较佳实施例中， 所述听力 管内只有受话器， 听力管内壁与受话器外壁紧密不透气套装， 听力管头部内壁 与防护网外壁紧密不透气套装。
在本发明一个较佳实施例中， 所述的机体软壳的外表面全部或局部有弹性 可变形结构。
在本发明一个较佳实施例中， 所述的深耳道自适应变形听力装置还设置有 拉杆， 拉杆粘贴在机体末端或者与深耳道自适应变形听力装置外层整体注模制 造； 深耳道自适应变形听力装置还包括电池门、 编程接口、 声压开关和麦克风 声音入口， 所述的编程接口、 声压开关和麦克风声音入口都设置于电池门上，所 述的声压开关通过轻拍耳部产生的声震动或声波转换的电讯号对深耳道自适应 变形听力装置进行控制。 '
本发明揭露的深耳道自适应变形听力装置， 听力传导装置是由适用于耳道 生理结构两道弯的两级三维弯曲变形听力管以及固定于听力管内部的受话器组 成的， 使其适用于不同生理结构形状和尺寸的人体耳道， 并且不分左右耳， 亦 即独立于因人而异和因左右耳而异的复杂耳道三维生理结构， 能自适应耳道生 理结构变形和稳定置放于深耳道内， 听力传导装置的两级大弯曲分别适合于耳 ,道第一弯道和第二弯道， 而且更易于在水平面方向弯曲变形， 使受话器更靠近 人体耳膜， 减少增益损失。 附图说明
图 1是文献报道人体耳道的生理解剖结构示意图；
图 2是本发明深耳道自适应变形听力装置一较佳实施例的结构示意图； 图 3是本发明深耳道自适应变形听力装置分解示意图；
图 4是本发明耳模实施例的使用状态结构示意图；
图 5是本发明机体内件装配图； 图 6是本发明深耳道自适应变形听力装置内部结构示意图；
图 7是本发明弹性可变形结构应用之一的结构示意图；
图 8是本发明弹性可变形结构应用之二的结构示意图；
图 9是本发明弹性可变形结构应用之三的结构示意图；
图中的标记为：1为听力装置， 2为耳道， 11为机体， 12为听力传导装置， 13为机体硬塑料壳， 14为机体软壳， 15为听力管， 16为受话器， 17为软耳模, 18为弹性可变形结构， 21为短耳道， 22为中耳道， 23为长耳道， 24为深耳道, al为第一弯道， a2为第二弯道， 111为麦克风， 112为芯片， 113为电池， 114 为电路支架， 115保护框， 116为电池门， 117为按钮开关， 118为编程接口， 119为拉杆。 具体实施方式
下面结合附图对本发明的较佳实施例进行详细阐述， 以使本发明的优点和 特征能更易于被本领域技术人员理解， 从而对本发明的保护范围做出更为清楚 明确的界定。
请参阅图 2，图 2示意了本发明一种深耳道自适应变形听力装置一较佳实施 例的结构示意图， 该深耳道自适应变形听力装置 1主要包括机体 11和听力传导 装置 12两大部分， 机体 11和听力传导装置 12连接， 为整体式或者可拆卸式软 连接》
请参阅图 3, 图 3为本发明深耳道自适应变形听力装置分解示意图，听力传 导装置 12包括听力管 15以及固定于听力管 15内部的受话器 16。其中， 听力管 15是由适用于耳道生理结构两道弯的两级三维弯曲变形的软体材料制得， 听力 管的单极单边弯曲角度小于或等于 75度， 本发明中的听力管 I 5是采用硅胶材 料制成的， 听力管 15头部外设有软耳模 17和听力管 15头部内置有防护网（图 未示）， 也可以没有软耳模 17， 听力管 15头部外径小于听力管 15中部外径， 受 话器 16置于听力管 15中部内壁， 听力管 15头部是弹性软体结构。
由于本发明中的机体 11和听力传导装置 12的连接可以是整体式软连接或 可拆卸式软连接， 听力管 15是由硅胶材料制得， 受话器 16置于听力管 15中部 内壁， 因此在听力管 I 5弯曲变形段， 机体 11内电子元件与听力管 15内端部的 受话器 16连接的电路外套有一节保护软管， 以保护导线在听力管 15多次大弯 曲变形时不会断裂或疲劳损坏。
参考图 3， 机体 11包括内部的机 ^^更塑料壳 13和外部的机体软壳 14， 内 部的机体硬塑料壳 13便于固定和保护内部零部件和电路， 机体软壳 14套在机 体硬塑料壳 13的外表面。 本发明中的机体软壳 14是由软体材料制得， 机体软 壳 14的软表面与耳道皮肤弹性接触并可以随耳道肌肉运动， 易于长期佩戴而且 不易滑出耳道。
上述中机体硬塑料壳 13的材料可以为硬塑料 ABS (Acrylonitrile Butadiene Styrene)、 PP(polypropylen), PE (polyethylen )、 PC (Polycarbonate)或者 PC/ABS 聚合物中的一种或者多种的组合物；所述的机体軟壳 14的材料为硅橡胶 ( silicone rubber ， Nusil Med 4930)、 聚氨酯（polyurethane )、 热弹塑性聚氨酯橡胶（TPU rubber).热塑性弹性体（TPE)或者硅胶与聚氨酯的聚合物中的一种或者多种的 组合物。 在本实施例中， 所述的机体软壳 14的材料采用硅胶制成。
本发明中的听力装置 1通用性体积小： 机体 11小于等于 15mm (高） X 10mm (宽） x 8mm (厚）； 听力管 I5外表面尺寸： 最大直径小于等于 6麵， 轴向长度 在 10mm - 25隱之间； 听力管 15头部外径比中部外径小 0. lmm以上， 头部变径 段长度在 0. 2麵 -5. 0mm之间； 适合不同生理结构形状和尺寸的人体耳道， 而且 不分左右耳， 能自适应耳道生理结构变形， 其整个听力装置 1置放于深耳道 24 , 完全隐蔽。
本发明中的整个听力装置 1可以稳定固定在耳道 2内， 其固定主要由端部 软耳模 17提供，机体 11只是提供辅助性支撑，机体 11与耳道 2部分弹性接触， 不仅增加了机体 11适合人体耳道 2大小形状和随耳道 2肌肉运动而滑动的通用 性， 而且让耳道 2更透气。 此外， 软耳模 17与深耳道 24壁紧密弹性接触起到 固定作用。 软耳模 17主要包括开放式和密闭式两类， 开放式耳模适用于中度和 轻度听力补偿， 密闭式耳模适用于重度以上听力补偿。
软耳模 17的结构可以为单级、 多极蘑菇型、 伞状或者螺旋状， 其材料可以 是硅橡胶、 聚氨酯、 热弹塑性聚氨酯橡胶、 热塑性弹性体以及硅胶与聚氨酯的 聚合物等。 软耳模 17可以为可拆式或者与听力管 15形成整体制造， 即软耳模 17可与听力管 15整体注模制造， 也可以分体制造后再组装。 软耳模 17有分开 放式和密闭式两类， 軟耳模 Π同时起到支撑固定作用； 防护网为分休制造再组 装， 可拆卸便于清除脏物。
机体 11和听力传导装置 12外表面的软体材料可以增加听力装置长期配戴 的舒适性， 机体 11和听力管 15外部软体硅胶可以部分或全部二次注模与机体 11紧密套装， 或分体制造再组装（过盈配合套装或胶合组装）。 机体 11外层的 机体软壳 14可以是一次注塑， 也可以与内层的机体硬塑料壳 13—起进行二次 注塑或嵌件成型。 内层的机体硬塑料壳 13可以是一次注塑、 注射成型或由三维 打印机快速打印成型； 外层的机体软壳 14可以部分或全部覆盖内层的机体硬塑 料壳 13， 可以通过过盈套装、 胶粘、 二次注塑或注射成型等方法将外层软体与 内层硬壳紧密帖合在一起。
请参阅图 4 , 图 4是本发明耳模实施例的使用状态结构示意图， 深耳道自适 应变形听力装置 1 的特殊外形和结构设计使其适用于不同生理结构形状和尺寸 的人体耳道 2 , 并且不分左右耳； 亦即独立于因人而异和因左右耳而异的复杂耳 道三维生理结构， 能自适应耳道 2的生理结构变形和稳定置放于深耳道 24内； 听力传导装置 12的两级大弯曲分别适合于耳道第一弯道 al和第二弯道 a2， 而 且更易于在水平面方向弯曲变形，使受话器 16更靠近人体耳膜，减少增益损失。
本发明中的听力管 15的横截面可以为圆形、 椭圓形、 长方型、 正方形、 多 变形、 对称或者非对称等， 通过结构和材料设计和制造， 使听力管 15与机体 11 连接部的结构弯曲刚度在平面方向小于立体方向， 从而在听力管 15头部受到沿 听力管 15长轴方向的压力时（即深耳道自适应变形听力装置 1推入深耳道 24 时， 在耳道 2拐弯处， 听力管 15头部与耳道壁接触产生反作用力）， 听力管 15 更容易在水平面方向产生弯曲， 与耳道 2水平面弯道相一致。 听力管 15头部的 软耳模 17可以在耳道 2的第二弯道 a2处产生水平面弯曲变形， 由于听力管 15 头部内置有一软衬管和防护网， 耳模 Π和听力管 15弯曲时不会产生屈曲或折 叠， 亦即不会诸塞受话器 16与人体耳膜之间的空气传导通道.
请参阅图 5, 图 5为本发明机体 11内件装配图，机体 11内的功能组件主要 包括麦克风 111、 芯片 112、 电池 113、 电路支架 114、 保护框 115、 电池门 116 及^^开关 117。 组装时， 麦克风 111置于电路支架 114内， 电池 113置于电池 门 116内； 然后把电池门 116穿插于保护框 115中再与电路支架 114相连接， 使其连接形成一个支架； 按钮开关 117的尾端通过插入电池门 116到达电路支 架 1 "的麦克风 111的尾端， 使得按钮开关 117与麦克风 111相连接， 用按钮 开关 117或声控来控制麦克风 111的音质和设置的聆听环境等；最后把芯片 112 与支架连接， 置于电池 113 的上方。 通过上述的功能组件实现了助听器的开启 与关闭、 音频信号的接收、 放大、 滤波、 功率调节等功能。
请参阅图 6， 图 6是本发明深耳道自适应变形听力装置内部结构示意图。本 发明中的深耳道自适应变形听力装置 1还包括电池门 116、 编程接口 118、 声压 开关（图未示）和麦克风 111声音入口， 其编程接口 118 , 深耳道自适应变形听 力装置 1外部的编程接口 118、 按钮开关 117或声压开关（图未示）和麦克风 111声音入口都设置于电池门 116上。声压开关指的是通过轻拍耳部产生的声震 动或声波转换的电讯号对深耳道自适应变形听力装置 1 进行控制。 本发明中的 深耳道自适应变形听力装置 1还设置有拉杆 120, 拉杆 120可以是粘贴在机体 11末端、 即电池门 116附近的机体 11内外层之间或外层表面，也可以是与深耳 道自适应变形听力装置 1外层整体注模制造。
参考图 7， 作为应用之一， 机体软壳 14的外表面全部或局部有弹性可变形 结构 18， 就是说机体软壳 14外表面有连体或非连体弹性可变形结构 18 , 比如 单个或多个突出钉状、 柱状、 管状、 片状体等， 这些结构可以是径向放射型排 列， 也可以是纵向型排列， 可以是对称排列， 也可以是非对称排列， 这些弹性 变形结构 18的径向长度在 0. 5mm - 4. Omm范围。 如图 8和图 9， 分别为机体软 外壳 14外表面上的弹性可变形结构 18—-局部非对称倒钩；机体软外壳 14外表 面上的弹性变形结构 18—-局部对称倒钩。
本发明揭露的深耳道自适应变形听力装置 1，整体听力装置稳定固定在耳道 2内，机体 11与耳道 2部分弹性接触， 不仅增加了机体 11适合人体耳道 2大小 形状和随耳道 2肌肉运动而滑动的通用性， 而且让耳道 2更透气； 听力传导装 置 12包括适用于耳道生理结构两道弯的两级三维弯曲变形听力管 15以及固定 于听力管 15 内部的受话器 16组成的， 使其适用于不同生理结构形状和尺寸的 人体耳道 2， 并且不分左右耳， 亦即独立于因人而异和因左右耳而异的复杂耳道 三维生理结构， 能自适应耳道 2生理结构变形和稳定置放于深耳道 24内， 听力 传导装置 12的两级大弯曲分别适合于耳道第一弯道 al和第二弯道 a2, 而且更 易于在水平面方向弯曲变形， 使受话器 16更靠近人体耳膜， 减少增益损失； 软 耳模 17包括开放式和密闭式两类， 开放式耳模适用于中度和轻度听力补偿， 密 闭式耳模适用于重度以上听力补偿； 听力传导装置 12和机体 11外表面的软体 材料提高了听力装置长期配戴的舒适性。
以上所述， 仅为本发明的较佳实施方式， 但本发明的保护范围并不局限于 此， 任何熟悉本领域的技术人员在本发明所揭露的技术范围内， 可不经过创造 性劳动想到的变化或替换， 都应涵盖在本发明的保护范围之内。 因此， 本发明 的保护范围应该以权利要求书所限定的保护范围为准。

Claims

权 利 要 求 书
1. 一种深耳道自适应变形听力装置， 包括机体和听力传导装置， 所述的机 体和听力传导装置连接， 其特征在于， 所述的听力传导装置包括听力管以及固 定于听力管内部的受话器， 其中， 所述的听力管由适用于耳道生理结构两道弯 的两级三维弯曲变形的软体材料制得， 所述的听力管的单极单边弯曲角度小于 或等于 75度。
2. 根据权利要求 1所述的深耳道自适应变形听力装置， 其特征在于， 所述 的机体和听力传导装置连接为整体式或者可拆卸式軟连接， 所述的机体包括内 部的机体硬塑料壳和外部的机体软壳， 机体软壳套在机体硬塑料壳的外表面， 机体软壳是由软体材料制得。
3. 根据权利要求 2所述的深耳道自适应变形听力装置， 其特征在于， 所述 的机体硬塑料壳的材料为硬塑料 ABS ( Aciylonitrile Butadiene Styrene )、 PP ( polypropylen )、 PE ( polyethylen )、 PC ( Polycarbonate )或者 PC/ABS聚合物 中的一种或多种； 所述的机体软壳的材料为硅橡胶（silicone rubber, Nusil Med 4930 )、 聚氨酯（polyurethane )、 热弹塑性聚氨酯橡胶（TPU rubber )、 热塑性弹 性体（TPE )或者硅胶与聚氨酯的聚合物中的的一种或多种。
4. 根据权利要求 2所述的深耳道自适应变形听力装置， 其特征在于， 所述 的机体和听力管的外部软体材料部分或全部二次注模 ( overraolding )或嵌件成 型（insert molding )与机体紧密套装， 或分体制造再组装。
5. 根据权利要求 1所述的深耳道自适应变形听力装置， 其特征在于， 所述 的听力管的横截面为圆形、 椭圆形、 长方型、 正方形、 多边形、 对称或者非对 称。
6. 根据权利要求 5所述的深耳道自适应变形听力装置， 其特征在于， 所述 的听力管头部外设有軟耳模和听力管头部内置有防护网，所述的听力管头部外 径小于听力管中部外径， 受话器置于听力管中部内壁， 听力管头部是弹性软体 结构， 所述的防护网和听力管为分体制造再组装。
7. 根据权利要求 6所述的深耳道自适应变形听力装置， 其特征在于， 所述 的软耳模的结构为单级、 多级蘑菇型、 伞状或者螺旋状， 其中， 软耳模的的材 料为硅橡胶（silicone rubber, Nusil Med 4930 ), 聚氨酯（ polyurethane )、 热弹塑 性聚氨酯橡胶 ( TPU rubber )、 热塑性弹性体（TPE )或者硅胶与聚氨酯的聚合 物中的的一种或多种， 軟耳模与听力管整体注模制造， 或分体制造后再组装。
8.根据权利要求 6所述的深耳道自适应变形听力装置， 其特征在于， 听力 管内安装有受话器和气导管， 所述气导管一端与受话器连接， 另一端与防护网 连接， 所述气导管的壁厚为 0.01至 1.5mm,材料是硬度在 20 至 80之间的单一 或混合高分子聚合物， 所述聚合物为硅橡胶、 聚氨酯、 氯酊橡胶或塑料， 所述 防护网是一多孔网状结构， 其材料为硅橡胶、 聚氨酯、 氯酊橡胶或塑料。
9.根据权利要求 2所述的深耳道自适应变形听力装置， 其特征在于， 所述 的机体软壳的外表面全部或局部有弹性可变形结构。
10. 根据权利要求 1 所述的深耳道自适应变形听力装置， 其特征在于， 所 述的深耳道自适应变形听力装置还设置有拉杆， 拉杆粘贴在机体末端或者与深 耳道自适应变形听力装置外层整体注模制造； 深耳道自适应变形听力装置还包 括电池门、 编程接口、 声压开关和麦克风声音入口， 所述的编程接口、 声压开 关和麦克风声音入口都设置于电池门上，所述的声压开关通过轻拍耳部产生的 声震动或声波转换的电讯号对深耳道自适应变形听力装置进行控制。
PCT/CN2011/001084 2011-06-02 2011-07-01 一种深耳道自适应变形听力装置 WO2012162859A1 (zh)

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Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102413410A (zh) * 2011-12-16 2012-04-11 江苏贝泰福医疗科技有限公司 数字式助听器
JP6003671B2 (ja) 2013-01-22 2016-10-05 株式会社典雅 マッサージ器、その製造方法、及び製造装置
GB201306369D0 (en) * 2013-04-09 2013-05-22 Photocure As Irradiation device
EP2922312B1 (en) * 2014-03-17 2017-01-04 Oticon A/s A device for inserting or withdrawing a hearing aid
CN104967961A (zh) * 2015-06-17 2015-10-07 厦门鹭宏声科技发展有限公司 耳内式助听器的制造方法
CN104967962A (zh) * 2015-06-17 2015-10-07 厦门鹭宏声科技发展有限公司 耳内式助听器
CN113132841B (zh) * 2019-12-31 2022-09-09 华为技术有限公司 降低耳机闭塞效应的方法及相关装置

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050117765A1 (en) * 2003-12-01 2005-06-02 Meyer John A. Hearing aid assembly
CN2842953Y (zh) * 2005-07-18 2006-11-29 唐武益 一种软体耳内式助听器
CN201557255U (zh) * 2009-10-29 2010-08-18 厦门新声科技有限公司 一种耳道机
CN201830442U (zh) * 2010-07-13 2011-05-11 江苏贝泰福医疗科技有限公司 一种通用型柔性耳内助听器

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN201450593U (zh) * 2009-05-14 2010-05-05 惠州三华工业有限公司 一种助听器
CN101867862A (zh) * 2010-07-07 2010-10-20 江苏贝泰福医疗科技有限公司 耳模及开放式耳内受话助听装置
CN102006543B (zh) * 2010-12-03 2015-04-29 江苏贝泰福医疗科技有限公司 一种新型耳内助听器

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050117765A1 (en) * 2003-12-01 2005-06-02 Meyer John A. Hearing aid assembly
CN2842953Y (zh) * 2005-07-18 2006-11-29 唐武益 一种软体耳内式助听器
CN201557255U (zh) * 2009-10-29 2010-08-18 厦门新声科技有限公司 一种耳道机
CN201830442U (zh) * 2010-07-13 2011-05-11 江苏贝泰福医疗科技有限公司 一种通用型柔性耳内助听器

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