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    • 74. 发明授权
    • Electrode array for hybrid cochlear stimulator
    • US06889094B1
    • 2005-05-03
    • US09979800
    • 2000-05-12
    • Janusz A. KuzmaWilliam Vanbrooks HarrisonThomas J. Balkany
    • Janusz A. KuzmaWilliam Vanbrooks HarrisonThomas J. Balkany
    • A61N1/05
    • A61N1/0541
    • A cochlear electrode array is adapted for implantation within the basal end of the scala tympani duct of a human cochlea. A first embodiment of the cochlear electrode array (10) comprises a skinny, elongate carrier (12) of from 6-8 mm in length. Four to eight spaced-apart electrode contacts (14) reside along one of the flat sides of the carrier, each of which is connected to a respective wire (22) embedded within the carrier. The wires exit a proximal end of the carrier via a wire bundle. The wire bundle, in turn, is connectable to an implantable cochlear stimulator (ICS) or equivalent pulse generator. The electrode array (10) is inserted into the relatively straight portion of the basal end of the scala tympani duct of the cochlea through a small slit (42) made in the round window membrane that separates the cochlea from the middle ear. The slit is oriented so as to place the electrode contacts facing the modiolar wall (32). The proximal end of the carrier may include flexible flaps (16) or tines that maintain the electrode array in its desired position within the basal end of the cochlea. Such tines or flaps further help seal the carrier against the slit opening to present fluids from escaping the cochlea. The cochlea thus remains filled with fluid which can activate hair cells as fluid waves are established through motion of the round window membrane. In use, electrical stimulation is provided only to the basal end of the cochlea through the electrode array to supplement hearing of high frequency sounds. Normal hearing (activation of hair cells through fluid motion) occurs at the apex and middle regions of the cochlea for sensing lower frequency sounds. A second embodiment of the cochlear electrode (100) is made by forming a small (120) of about 0.4 mm diameter on the end of a very fine flexible platinum/iridium (Pt/Ir) wire (140). At a proximal end of the wire, a suitable connector (540) allows the wire to be detachably connected to a pulse generator (500).
    • 76. 发明授权
    • Wideband low-noise implantable microphone assembly
    • 宽带低噪声植入式麦克风组件
    • US06736771B2
    • 2004-05-18
    • US10324183
    • 2002-12-20
    • W. Gary SokolichJanusz A. Kuzma
    • W. Gary SokolichJanusz A. Kuzma
    • H04R2500
    • H04R25/606H04R2225/67H04R2410/00
    • An implantable microphone assembly for use with a hearing prosthesis, such as a fully implantable cochlear stimulation system, includes a diaphragm mounted to an outside surface of an hermetically sealed case. The mounting is made, in one of various embodiments, by way of an hermetic weld around the diaphragm circumference. A gap is created on the underside of the diaphragm when the diaphragm is lifted with internal pressure. An acoustic channel or groove is formed in the wall of the hermetic case to which the diaphragm is mounted. A first end of the channel or groove opens into the gap at a location that is at or near the center of the underside of the diaphragm. A second end of the channel or groove opens to the interior of the hermetic case at a location that is near the periphery of the diaphragm. An acoustic transducer is placed inside the hermetic case and coupled to the second end of the acoustic channel or groove so as to sense variations in pressure that occur in the gap due to deflections of the diaphragm caused, e.g., by external sound pressure. The interior space inside of the hermetic case directly underneath the diaphragm may be used to house and mount other components, such as a battery. The interior of the hermetic case, which interior includes the gap and acoustic channel, is pressurized in order to lift the diaphragm to form the gap and enable the diaphragm to move in response to external forces, such as forces created by sound impinging the skin above the area where the implantable microphone is implanted.
    • 用于与诸如完全植入式耳蜗刺激系统之类的听觉假体的可植入麦克风组件包括安装在密封的壳体的外表面上的隔膜。 在各种实施例之一中,通过围绕隔膜圆周的密封焊接来制造安装件。 当隔膜用内压提升时,在隔膜的下侧产生间隙。 在安装隔膜的密封箱的壁中形成声通道或凹槽。 通道或凹槽的第一端在位于隔膜下侧中心附近的位置处开口到间隙中。 通道或凹槽的第二端在靠近隔膜周边的位置处通向密封壳体的内部。 声换能器放置在密封壳体的内部并且耦合到声通道或凹槽的第二端,以便感测由于例如由外部声压导致的隔膜的偏转而在间隙中发生的压力变化。 直接在隔膜下方的密封箱内部的内部空间可以用于容纳和安装诸如电池的其它部件。 密封壳体的内部包括间隙和声通道,其被加压以提升隔膜以形成间隙,并且使得隔膜能够响应外部力而移动,例如由声音撞击皮肤所产生的力 植入式麦克风植入的区域。
    • 77. 发明授权
    • Minimally-invasive access into the cochlea for electrode insertion and fluid delivery
    • US06628991B2
    • 2003-09-30
    • US09844024
    • 2001-04-27
    • Janusz A. KuzmaThomas J. BalkanyThomas H. R. Lenarz
    • Janusz A. KuzmaThomas J. BalkanyThomas H. R. Lenarz
    • A61N105
    • A61N1/0541A61B17/1679A61F11/004
    • A threaded grommet, having an axial passageway therethrough, and made from a biocompatible material, such as titanium, is screwed into a cochleostomy made in the bony tissue adjacent the round window in order to provide a minimally-invasive access port into the cochlea. The threads included on the outside of the grommet engage the bony tissue and form a tight seal that holds the grommet securely in position. Such tight seal prevents cochlear fluids from escaping from inside of the cochlea. The axial passageway through the center of the grommet provides an opening, i.e., mechanical access, into the base end (the end of the cochlea nearest the round window) of the cochlea. Drugs, steroids, tissue-growth-inhibiting fluids, and the like, may be controllably delivered through the access hole into the cochlea, which access hole may be plugged when not needed. Additionally, an electrode array, e.g., a relatively short electrode array may, be inserted into the cochlea through the access hole. A preferred electrode array has from four to eight electrode contacts spaced apart along a flexible carrier. The flexible carrier is about 6-8 mm in length. The electrode contacts may be connected, in conventional manner, to suitable implantable cochlear stimulator (ICS), or equivalent pulse generator. Neither the grommet nor the short electrode array interfere with the normal hearing processes within the cochlea. Hence, both electrical stimulation and normal hearing processes may occur simultaneously within the cochlea.
    • 78. 发明授权
    • Blade electrode array for insertion under soft tissue of lateral wall of cochlea
    • 用于插入耳蜗侧壁软组织下的刀片电极阵列
    • US06549814B1
    • 2003-04-15
    • US09876882
    • 2001-06-07
    • Juergen StrutzJanusz A. Kuzma
    • Juergen StrutzJanusz A. Kuzma
    • A61N105
    • A61N1/0541A61N1/36036
    • A cochlear electrode array is adapted for use with a hybrid hearing aid system. The cochlear electrode array has a carrier on which spaced-apart electrode contacts are carried, and in one embodiment is formed in the shape of a blade, being flat in one direction and thin in another direction. In another embodiment, side fins extend out from opposing sides of the carrier on which the electrode contacts are carried. The blade electrode array, or electrode array with side fins, is adapted for minimally-invasive insertion into the inner ear. More particularly, the blade or finned electrode is designed to be inserted through a soft cochleostomy so as to reside between the spiral ligament membrane and the cochlear bony tissue along a lateral side of the cochlea, near the basal end of the cochlea. As such, the blade electrode does not penetrate into the scala tympani or other ducts of the cochlea, and the cochlea remains free to perform its normal hearing functions to the extent that such normal hearing functions can be performed.
    • 耳蜗电极阵列适用于混合式助听器系统。 耳蜗电极阵列具有承载间隔开的电极触点的载体,并且在一个实施例中形成为叶片的形状,在一个方向上是平坦的并且在另一个方向上是薄的。 在另一个实施例中,侧翼从承载电极接触的载体的相对侧延伸出来。 刀片电极阵列或具有侧翼的电极阵列适于微创地插入内耳。 更具体地,叶片或翅片电极被设计成通过软的耳蜗切开术插入,以便在耳蜗的基端附近沿着耳蜗的侧面位于螺旋状韧带膜和耳蜗骨组织之间。 因此,刀片电极不会渗透到耳蜗的鼓膜鼓或其他导管中,并且耳蜗保持自由以执行其正常听力功能至可以执行这种正常听力功能的程度。
    • 79. 发明授权
    • Spiral shield for a flexible high-Q implantable inductively coupled device
    • 螺旋屏蔽用于灵活的高Q可植入电感耦合器件
    • US06542777B1
    • 2003-04-01
    • US09766290
    • 2001-01-19
    • Glen A. GriffithJanusz A. KuzmaTae W. Hahn
    • Glen A. GriffithJanusz A. KuzmaTae W. Hahn
    • A61N140
    • A61N1/37229
    • A spiral shield for an implantable secondary coil confines the electrical field of the coil, and thus prevents capacitive coupling of the coil through surrounding dielectrics (such as human tissue.) Known implantable devices receive power inductively, through a secondary coil, from a primary coil in an external device. Efficient power reception requires that the coils be tuned to the same resonant frequency. Use of the spiral shield results in predictable electrical behavior of the secondary coil and permits the secondary coil to be accurately tuned to the same resonate frequency as the primary coil. To further improve performance, spacers made from SILBIONE®LSR 70 reside between turns of the coil to reduce turn to turn and turn to shield capacitances. Reducing the capacitances prevents excessive reduction of the self resonant frequency of the coil. The coil is imbedded in SILBIONE®LSR 70, allowing for a thin and flexible coil.
    • 用于可植入次级线圈的螺旋屏蔽限制线圈的电场,从而防止线圈通过周围电介质(例如人体组织)的电容耦合。已知的可植入装置通过次级线圈感应地从初级线圈 在外部设备。 有效的功率接收要求将线圈调谐到相同的谐振频率。 螺旋屏蔽的使用导致次级线圈的可预测的电气行为,并允许将次级线圈精确地调谐到与初级线圈相同的谐振频率。 为了进一步提高性能,SILBIONE(R)LSR 70制成的间隔件位于线圈的转弯之间,以减少转向并转向屏蔽电容。 降低电容可以防止线圈的自谐振频率的过度降低。 线圈镶嵌在SILBIONE(R)LSR 70中,允许薄而柔性的线圈。
    • 80. 发明授权
    • Apex to base cochlear implant electrode
    • Apex到耳蜗植入电极
    • US06498954B1
    • 2002-12-24
    • US09758104
    • 2001-01-10
    • Janusz A. KuzmaThomas H. R. Lenarz
    • Janusz A. KuzmaThomas H. R. Lenarz
    • A61N105
    • A61N1/0541
    • An implantable electrode assembly includes a leading section attached to the distal end of an electrode array. The electrode array has electrodes spaced along its length. Cochleostomies are drilled at both the base and apex of the cochlea. The leading section is inserted through the basal cochleostomy and promoted to the apical cochleostomy. A forward end of the leading section is then pulled through the apical cochleostomy, which causes the electrode array to be pulled into the cochlea. A depth marker on the electrode array indicates complete insertion. The leading section is detached from the electrode array and the electrode array is placed in tension by gently pulling both ends, which tension causes the electrode array to hug the modiolar wall of the cochlea. Wedges may be inserted at both cochleostomies to maintain the electrode array in tension.
    • 可植入电极组件包括附接到电极阵列的远端的引导部分。 电极阵列具有沿其长度间隔开的电极。 在耳蜗的基部和顶点都钻有耳蜗。 引导部分穿过基底耳蜗切开术,并推广到顶端耳蜗造口术。 然后将引导部分的前端拉过顶端耳蜗切开术,使得电极阵列被拉入耳蜗。 电极阵列上的深度标记表示完全插入。 引导部分与电极阵列分离,并且电极阵列通过轻轻拉动两端而放置在张力中,该张力使电极阵列拥抱耳蜗的模块壁。 楔子可以插入两个耳蜗,以保持电极阵列的张力。