JP2019170519A - Artificial hearing aid - Google Patents
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Abstract
【課題】蝸牛内への埋植時に、圧電体層を含む音波共振部に割れやひび等の破損の発生することのない、信頼性の高い埋め込み型の人工聴覚器を提供する。【解決手段】本開示の人工聴覚器は、分離可能な、蝸牛埋植部１および音波共振部２を備え、蝸牛埋植部１は、聴神経刺激用の電極（導電体層１３）と、電極を支持する第１基体１１と、第１基体１１の一端部に配設される第１端子部１０とを含み、音波共振部２は、固有の振動数を有する第２基体２２と、第２基体２２の振動を電気信号に変換する変換部２１と、変換部２１と電気的に接続されるとともに第１端子部１０と係合可能な第２端子部２０とを含み、蝸牛埋植部１は蝸牛の内壁に埋植され、音波共振部２は、第２端子部２０を第１端子部１０に係合させて蝸牛の内部の鼓室階に配設されている。【選択図】図１Provided is a highly reliable implantable artificial hearing device that does not cause breakage such as cracking or cracking in a sound wave resonator including a piezoelectric layer when implanted in a cochlea. An artificial hearing device according to the present disclosure includes a separable cochlear implant 1 and a sound wave resonator 2, wherein the cochlear implant 1 includes an electrode (a conductor layer 13) for acoustic nerve stimulation and an electrode. And a first terminal portion 10 disposed at one end of the first base 11, and the acoustic resonance portion 2 includes a second base 22 having a unique frequency, a second base 22, and a second base 22. The cochlear implant 1 includes a conversion unit 21 that converts vibration of the base 22 into an electric signal, and a second terminal unit 20 that is electrically connected to the conversion unit 21 and engageable with the first terminal unit 10. Is implanted in the inner wall of the cochlea, and the acoustic wave resonator 2 is disposed on the tympanic floor inside the cochlea with the second terminal 20 engaged with the first terminal 10. [Selection diagram] Fig. 1
Description
本発明は、蝸牛内に配設される人工聴覚器に関する。 The present invention relates to an artificial hearing instrument disposed in a cochlea.
内耳の一部を構成する蝸牛内に埋め込んで使用する人工聴覚器が提案されている。この人工聴覚器は、内耳に到達した音波を、蝸牛内に配設した圧電膜により電気信号に変換し、この圧電膜上に設置した複数の微小電極によって、発生した電気信号を、蝸牛内の聴神経に、電気的な刺激として直接伝えるように構成されている（特許文献１を参照）。 Artificial hearing devices have been proposed which are used by being embedded in a cochlea that constitutes a part of the inner ear. This artificial hearing instrument converts sound waves that reach the inner ear into electrical signals by means of a piezoelectric film disposed in the cochlea, and the electrical signals generated by a plurality of microelectrodes installed on the piezoelectric film It is configured to transmit directly to the auditory nerve as an electrical stimulus (see Patent Document 1).
ところで、人工聴覚器を蝸牛内に配置して、微小な形状の電極である聴神経刺激用電極を蝸牛または蝸牛管に埋植しようとする際、音波を電気信号に変換する膜状の圧電体層およびその周辺の構造が非常に薄いものであるため、これが電極押し込みの圧力と荷重によって、破損してしまう場合があった。 By the way, when an artificial hearing instrument is placed in the cochlea and an acoustic nerve stimulation electrode, which is a minute electrode, is to be implanted in the cochlea or cochlea duct, a film-like piezoelectric layer that converts sound waves into an electrical signal In addition, since the surrounding structure is very thin, it may be damaged by the pressure and load of the electrode pressing.
本発明の目的は、蝸牛内への埋植時に、圧電体層を含む音波共振部に割れやひび等の破損の発生することのない、信頼性の高い埋め込み型の人工聴覚器を提供することである。 It is an object of the present invention to provide a highly reliable implantable artificial hearing instrument that does not cause breakage such as cracks or cracks in the acoustic resonance part including the piezoelectric layer when implanted in the cochlea. It is.
本開示の人工聴覚器は、内耳の蝸牛内に到達した音波を電気信号に変換して聴神経に伝達する人工聴覚器であって、
分離可能な、蝸牛埋植部および音波共振部を備え、
前記蝸牛埋植部は、聴神経刺激用の電極と、前記電極を支持する第１基体と、該第１基体の一端部に配設され、前記電極と電気的に接続される第１端子部と、を含み、
前記音波共振部は、予め決められた固有の振動数を有する第２基体と、前記第２基体の振動を電気信号に変換する変換部と、該変換部と電気的に接続されるとともに前記第１端子部と係合可能な第２端子部と、を含み、
前記蝸牛埋植部は、前記第１端子部が蝸牛の内部（鼓室階）に向けて突出するよう、蝸牛の内壁に埋植され、
前記音波共振部は、前記第２端子部を前記第１端子部に係合させて、蝸牛の内部（鼓室階）に配設されることを特徴とする。
The artificial hearing device of the present disclosure is an artificial hearing device that converts sound waves that have reached the cochlea of the inner ear into electrical signals and transmits them to the auditory nerve,
Separable, cochlear implant and sonic resonator
The cochlear implant includes an acoustic nerve stimulation electrode, a first base that supports the electrode, a first terminal that is disposed at one end of the first base and is electrically connected to the electrode. Including,
The sound wave resonance unit is electrically connected to the second base having a predetermined natural frequency, a conversion unit for converting the vibration of the second base into an electric signal, and the first base unit. A second terminal part engageable with one terminal part,
The cochlear implantation part is implanted on the inner wall of the cochlea so that the first terminal part protrudes toward the interior of the cochlea (the trumpet floor),
The sound wave resonance part is disposed inside the cochlea (the trumpet floor) with the second terminal part engaged with the first terminal part.
本開示によれば、蝸牛内への埋植時にも、音波の変換部や音波共振部に破損の発生することのない、信頼性の高い人工聴覚器とすることができる。 According to the present disclosure, it is possible to provide a highly reliable artificial hearing instrument that does not cause damage to the sound wave conversion unit and the sound wave resonance unit even when implanted in the cochlea.
本実施形態で説明する人工聴覚器の基本的な構成は、図１（ａ），図１（ｂ）の連結前の図および図１（ｃ），図１（ｄ）の連結後の図に示すように、２つのブロック、すなわち２つの部または分画を組み合わせて構成されている。すなわち、本実施形態の人工聴覚器は、聴神経刺激用の電極部位の一例である蝸牛埋植部１と、種々の形状の、音波を電気信号に変換する音波共振部２との組み合わせを、選択可能であるとともに、これら蝸牛埋植部１と音波共振部２との間が、係合自在および着脱自在に、あるいは交換自在に連結されていることを特徴とする。なお、後記の音波共振部２の各層も含め、図における蝸牛埋植部１を構成する各層は、その厚みを強調して描いている。 The basic configuration of the artificial hearing device described in the present embodiment is shown in FIGS. 1 (a) and 1 (b) before connection and in FIGS. 1 (c) and 1 (d) after connection. As shown, two blocks, ie, two parts or fractions are combined. That is, the artificial hearing device of this embodiment selects a combination of a cochlear implant part 1 that is an example of an electrode part for auditory nerve stimulation and a sound wave resonance part 2 of various shapes that converts sound waves into electrical signals. In addition, the cochlear implant 1 and the sonic resonator 2 are connected to each other so as to be engageable and detachable or exchangeable. In addition, each layer which comprises the cochlear implantation part 1 in a figure including each layer of the acoustic wave resonance part 2 of the postscript is drawn emphasizing the thickness.
蝸牛埋植部１は、図１に示すように、基板もしくは基盤を兼用する第１基体１１と、聴神経刺激用の電極である導電体層１３と、第１基体１１と導電体層１３との間に配設された絶縁体層１２と、第１基体１１の一端部、すなわち図示では右方でかつ蝸牛内部側に配設され、電極である前記導電体層１３と繋がる第１端子部１０と、を含む。なお、上記のような蝸牛埋植部の構成は、本開示における一例であって、導電体層および絶縁体層の一方もしくは両方を兼用する第１基体としてもよい。たとえば、第１基体を導電体で構成すれば、絶縁体層は設ける必要がなく、この第１基体が基体と電極とを兼任する。 As shown in FIG. 1, the cochlear implant 1 includes a first base 11 that also serves as a substrate or a base, a conductor layer 13 that is an electrode for stimulating the auditory nerve, and a first base 11 and a conductor layer 13. The insulating layer 12 disposed between the first terminal portion 10 and the one end portion of the first base 11, that is, on the right side in the figure and on the inner side of the cochlea, and connected to the conductor layer 13 that is an electrode. And including. Note that the configuration of the cochlear implant as described above is an example in the present disclosure, and may be a first base that also serves as one or both of a conductor layer and an insulator layer. For example, if the first substrate is made of a conductor, there is no need to provide an insulator layer, and the first substrate serves as both the substrate and the electrode.
第１基体１１は、図に示すように、たとえば平面視で先端が細くなったくさび形状であり、蝸牛壁面への押し込みおよび埋植に耐える厚みと剛性とを有する。第１基体１１は、尖った形状の先端部１１ａと、先端部１１ａとは軸方向または長手方向反対側の、くさびが広がった基端部１１ｂとを含み、先端部１１ａ側から、蝸牛の内壁に押し込んで、埋植される。 As shown in the figure, the first base 11 has a wedge shape with a thin tip in plan view, for example, and has a thickness and rigidity that can withstand pushing into a cochlea wall and implantation. The first base 11 includes a pointed tip portion 11a and a base end portion 11b having a wedge extending on the opposite side of the tip portion 11a in the axial direction or the longitudinal direction, and from the tip portion 11a side, the inner wall of the cochlea It is pushed into and is buried.
第１基体１１の構成材料としては、金属、無機物または樹脂等のうち、前述の剛性を有するものが、好適に使用される。たとえば、金属であれば、金（Ａｕ）または白金（Ｐｔ）等があげられる。無機物であれば、シリコン（Ｓｉ）、酸化シリコン（ＳｉＯ２）、ＳＯＩ（Ｓｉｌｉｃｏｎ ｏｎ Ｉｎｓｕｌａｔｏｒ）、ガラスまたはセラミックス等が使用できる。樹脂としては、アクリル樹脂、フッ素樹脂、ポリイミド樹脂、エポキシ樹脂、ポリパラキシレン樹脂、または、ポリフェニレンサルファイド（ＰＰＳ）樹脂、アクリロニトリル−ブタジエン−スチレン（ＡＢＳ）樹脂等の樹脂が使用できる。図１の第１基体１１は、シリコン（Ｓｉ）を用いて構成されている。 As a constituent material of the first base 11, a material having the above-described rigidity among metals, inorganic substances, resins, and the like is preferably used. For example, in the case of a metal, gold (Au) or platinum (Pt) can be used. As an inorganic material, silicon (Si), silicon oxide (SiO 2 ), SOI (Silicon on Insulator), glass, ceramics, or the like can be used. As the resin, resins such as acrylic resin, fluorine resin, polyimide resin, epoxy resin, polyparaxylene resin, polyphenylene sulfide (PPS) resin, acrylonitrile-butadiene-styrene (ABS) resin can be used. The first base 11 in FIG. 1 is configured using silicon (Si).
導電体層１３は、聴神経刺激用の電極であり、絶縁体層１２の表面に蒸着等により形成された、金（Ａｕ）または白金（Ｐｔ）等の金属膜からなる。 The conductor layer 13 is an electrode for auditory nerve stimulation, and is made of a metal film such as gold (Au) or platinum (Pt) formed on the surface of the insulator layer 12 by vapor deposition or the like.
また、絶縁体層１２は、第１基体１１と、電極を構成する導電体層１３との間を電気的に絶縁するものであり、ＣＶＤ法等により形成された、酸化シリコン（ＳｉＯ２）を含む酸化膜、または、窒化シリコン（ＳｉＮ）を含む窒化膜等の絶縁膜からなる。 The insulator layer 12 electrically insulates between the first base 11 and the conductor layer 13 constituting the electrode, and is formed of silicon oxide (SiO 2 ) formed by a CVD method or the like. It is made of an insulating film such as an oxide film containing silicon nitride or a nitride film containing silicon nitride (SiN).
第１端子部１０は、第１基体１１と一体に設けられている。その形状は、第１基体１１の、くさび状に広がった基端部１１ｂから、図示右方であり蝸牛の内部側の外方に向けて突出する、角柱，円柱等の柱状または筒状に形成されている。そして、第１端子部１０は、後記する音波共振部２および第２基体２２に設けられた凹状の被係合部である第２端子部２０に嵌め入れて係合可能な形状に、形成されている。 The first terminal portion 10 is provided integrally with the first base body 11. The shape of the first base 11 is formed in a columnar shape such as a rectangular column or a cylinder or a cylindrical shape protruding from the base end portion 11b spreading in a wedge shape to the right side in the drawing and outward toward the inner side of the cochlea. Has been. The first terminal portion 10 is formed in a shape that can be fitted into and engaged with a second terminal portion 20 that is a concave engaged portion provided in the sound wave resonance portion 2 and the second base 22 described later. ing.
また、第１端子部１０は、図１（ｂ）の断面図のように、蝸牛埋植部１と同様、支持部材である第１基体１１と、端子電極となる導電体層１３と、第１基体１１と導電体層１３との間に配設された絶縁体層１２と、からなる。そのうち、導電体層１３は、蝸牛の内壁側の図示左側の第１基体１１側の導電体層１３に繋がっているとともに、蝸牛の内部側である図示右側の端面と、それに続く下面である端子部裏面１０ａにまで延設されている。 Moreover, the 1st terminal part 10 is like the cochlear implant part 1 like the cross section of FIG.1 (b), The 1st base | substrate 11 which is a supporting member, The conductor layer 13 used as a terminal electrode, And an insulator layer 12 disposed between the substrate 11 and the conductor layer 13. Among them, the conductor layer 13 is connected to the conductor layer 13 on the first base 11 side on the left side of the cochlea on the inner wall side of the cochlea, and on the right end surface in the figure which is the inner side of the cochlea, and the terminal which is the lower surface following it. It extends to the part back surface 10a.
これにより、図１（ｄ）のように、第１端子部１０が音波共振部２および第２基体２２に設けられた、凹状の係合部である第２端子部２０に嵌め入れて係合または嵌合した場合、前記凹状の第２端子部２０内にまで延設された、音波共振部２側の端子電極である表面電極層２７と、電気的に接続される。 As a result, as shown in FIG. 1 (d), the first terminal portion 10 is fitted into and engaged with the second terminal portion 20, which is a concave engaging portion, provided on the sound wave resonance portion 2 and the second base 22. Alternatively, when fitted, it is electrically connected to the surface electrode layer 27 that is a terminal electrode on the sound wave resonance unit 2 side that extends into the concave second terminal unit 20.
音波共振部２は、予め決められた固有の振動数を有する第２基体２２と、第２基体２２の振動を電気信号に変換する変換部２１と、変換部２１と電気的に接続されるとともに先に述べた第１端子部１０と係合可能な第２端子部２０と、第２基体２２の下側に配設された共振周波数調整用の調節錘部２１ａと、から構成されている。 The acoustic wave resonator 2 is electrically connected to the second base 22 having a predetermined natural frequency, the converter 21 that converts the vibration of the second base 22 into an electrical signal, and the converter 21. The second terminal portion 20 that can be engaged with the first terminal portion 10 described above and the adjustment weight portion 21a for adjusting the resonance frequency disposed below the second base 22 are configured.
なお、部材個々の固有振動数または固有周波数に対して、音波に共鳴・共振する、音波共振部２全体としての振動数を「共振周波数」と呼んでいる。また、上記のような音波共振部および後記の圧電体層のような各層の構成は、本開示における一例であって、各構成に２つ以上の機能を兼任させることにより、その構成を省略して簡素に構成することもできる。たとえば、圧電体に水晶等を用いれば、第２基体、変換部および第２端子部の少なくとも２つ以上を１つの部材で兼用することも可能である。 Note that the frequency of the sound wave resonating unit 2 as a whole that resonates and resonates with the sound wave with respect to the natural frequency or the natural frequency of each member is called a “resonance frequency”. In addition, the configuration of each layer such as the above-described acoustic wave resonator and the piezoelectric layer described later is an example in the present disclosure, and the configuration is omitted by having each configuration serve two or more functions. It can also be configured simply. For example, if quartz or the like is used for the piezoelectric body, at least two of the second base, the conversion unit, and the second terminal unit can be used as a single member.
変換部２１は、平板状の第２基体２２を基板または基盤として、その上に、複数の機能層を積層して形成されている。すなわち、変換部２１は、図１（ｂ），図１（ｄ）の断面図に示すように、第２基体２２の図示上面側である表面上に、酸化膜層２３、絶縁体層２４、裏面電極層２５、圧電体層２６および表面電極層２７を、順次積層して形成されている。 The conversion unit 21 is formed by laminating a plurality of functional layers on a flat plate-like second base 22 as a substrate or a base. That is, as shown in the cross-sectional views of FIG. 1B and FIG. 1D, the conversion unit 21 has an oxide film layer 23, an insulator layer 24, The back electrode layer 25, the piezoelectric layer 26, and the surface electrode layer 27 are sequentially laminated.
第２基体２２は、図に示すような平板状であり、第１基体１１と同様、金属、無機物または樹脂等のうち、剛性を有するものを構成材料として構成されている。構成材料は、たとえば、金属であれば金（Ａｕ）または白金（Ｐｔ）等、無機物であればシリコン（Ｓｉ）、酸化シリコン（ＳｉＯ２）、ＳＯＩ（Ｓｉｌｉｃｏｎ ｏｎ Ｉｎｓｕｌａｔｏｒ）、ガラスまたはセラミックス等、樹脂であれば、アクリル樹脂、フッ素樹脂、ポリイミド樹脂、エポキシ樹脂、ポリパラキシレン樹脂、または、ポリフェニレンサルファイド（ＰＰＳ）樹脂、アクリロニトリル−ブタジエン−スチレン（ＡＢＳ）樹脂等を用いることができる。図１の第２基体２２は、シリコン（Ｓｉ）を用いて構成されている。 The second substrate 22 has a flat plate shape as shown in the figure, and is composed of a rigid material among metals, inorganic substances, resins, and the like, as with the first substrate 11. The constituent material is, for example, gold (Au) or platinum (Pt) if it is a metal, silicon (Si), silicon oxide (SiO 2 ), SOI (Silicon on Insulator), glass, ceramics, etc. if it is inorganic. If so, acrylic resin, fluorine resin, polyimide resin, epoxy resin, polyparaxylene resin, polyphenylene sulfide (PPS) resin, acrylonitrile-butadiene-styrene (ABS) resin, or the like can be used. The second base 22 in FIG. 1 is configured using silicon (Si).
酸化膜層２３は、第２基体２２を加熱処理することにより形成されている酸化物層であり、図示上面側である第２基体２２の表面側に形成されている。第２基体２２の表面側の酸化膜層２３は、裏面電極層２５と第２基体２２とを電気的に絶縁する絶縁層として機能するものである。このように、酸化膜層２３は、第２基体２２がシリコン（Ｓｉ）製の場合、第２基体２２を加熱処理することにより形成される酸化シリコン（ＳｉＯ２）からなる。 The oxide film layer 23 is an oxide layer formed by heat-treating the second substrate 22, and is formed on the surface side of the second substrate 22 that is the upper surface side in the drawing. The oxide film layer 23 on the front surface side of the second substrate 22 functions as an insulating layer that electrically insulates the back electrode layer 25 and the second substrate 22. Thus, the oxide film layer 23 is made of silicon oxide (SiO 2 ) formed by heat-treating the second substrate 22 when the second substrate 22 is made of silicon (Si).
なお、酸化膜層２３は、図示下面側である第２基体２２の裏面側にも形成されている。第２基体２２の裏面側の酸化膜層２３は、第２基体２２を形成する際のエッチング用マスク（エッチングのストップ層）として機能するものである。 The oxide film layer 23 is also formed on the back surface side of the second base 22 which is the lower surface side in the figure. The oxide film layer 23 on the back side of the second base 22 functions as an etching mask (etching stop layer) when the second base 22 is formed.
絶縁体層２４は、第２基体２２と後記の圧電体層２６との間を電気的に絶縁するものであり、前述の絶縁体層１２と同様、ＣＶＤ法等により形成された、酸化シリコン（ＳｉＯ２）を含む酸化膜、または、窒化シリコン（ＳｉＮ）を含む窒化膜等の絶縁膜からなる。なお、絶縁体層２４は、後記の圧電体層２６を挟んで、左右に形成されている。 The insulator layer 24 electrically insulates between the second substrate 22 and a piezoelectric layer 26 described later. Like the insulator layer 12 described above, a silicon oxide ( It is made of an insulating film such as an oxide film containing SiO 2 ) or a nitride film containing silicon nitride (SiN). The insulator layer 24 is formed on the left and right with a piezoelectric layer 26 described later interposed therebetween.
裏面電極層２５および表面電極層２７は、後記の圧電体層２６を上下に挟むように配設されており、前述の導電体層１３と同様、蒸着等により形成された、金（Ａｕ）または白金（Ｐｔ）等の金属膜からなる。そのうち、変換部２１の最表面の上面に位置する表面電極層２７は、図示左側でかつ蝸牛の内壁側の第２端子部２０およびその中に形成された凹状の係合部である凹部２０ａの内側まで、延設されている。 The back electrode layer 25 and the front electrode layer 27 are disposed so as to sandwich a piezoelectric layer 26, which will be described later, in the same manner as the conductor layer 13 described above. It consists of a metal film such as platinum (Pt). Among them, the surface electrode layer 27 located on the uppermost surface of the conversion portion 21 has a second terminal portion 20 on the left side of the figure and on the inner wall side of the cochlea and a concave portion 20a which is a concave engaging portion formed therein. It extends to the inside.
圧電体層２６は、湾曲した際に圧電効果によって電荷を生じる圧電材料からなる膜状の層である。圧電材料としては、チタン酸バリウム、チタン酸ジルコン酸鉛またはポリフッ化ビニリデン等が用いられる。 The piezoelectric layer 26 is a film-like layer made of a piezoelectric material that generates an electric charge by a piezoelectric effect when it is bent. As the piezoelectric material, barium titanate, lead zirconate titanate, polyvinylidene fluoride, or the like is used.
以上の構成の変換部２１は、蝸牛内に到来した音波と共鳴・共振する、予め決められた共振周波数を有する。 The conversion unit 21 having the above configuration has a predetermined resonance frequency that resonates and resonates with the sound wave that has entered the cochlea.
そして、第２基体２２の下側に配設された調節錘部２１ａは、上述の変換部２１の共振周波数を調節するために設けられているものである。調節錘部２１ａは、シリコン（Ｓｉ）、ガラス、セラミックス等を用いて、たとえば中実の直方体等に形成されている。第２端子部２０および調節錘部２１ａは同じ材料であってもよいし、それぞれが異なる材料であっても良い。第２端子部２０と調節錘部２１ａが同じ材料、たとえばシリコン（Ｓｉ）で同じ厚みであれば、Ｓｉ深掘加工（ドライエッチング）により一度に形成することができ、加工プロセスが簡単になる。 And the adjustment weight part 21a arrange | positioned under the 2nd base | substrate 22 is provided in order to adjust the resonant frequency of the above-mentioned conversion part 21. FIG. The adjustment weight portion 21a is formed in, for example, a solid rectangular parallelepiped using silicon (Si), glass, ceramics, or the like. The second terminal portion 20 and the adjustment weight portion 21a may be made of the same material or different materials. If the second terminal portion 20 and the adjustment weight portion 21a are made of the same material, for example, silicon (Si) and have the same thickness, the second terminal portion 20 and the adjustment weight portion 21a can be formed at a time by Si deep digging (dry etching), thereby simplifying the machining process.
なお、調節錘部２１ａの形状・大きさや質量等は、目標とする共振周波数に対応して適宜設定される。また、調節錘部２１ａは、設けなくてもよい。 In addition, the shape, size, mass, and the like of the adjustment weight portion 21a are appropriately set according to the target resonance frequency. Moreover, the adjustment weight part 21a does not need to be provided.
つぎに、第２端子部２０は、先にも述べたように、前記蝸牛埋植部１の第１端子部１０と係合する凹部２０ａを含むものである。第２端子部２０は、第１基体１１および第２基体２２と同様、金属、無機物または樹脂等のうち、剛性を有するものを構成材料として構成されている。図１の第２端子部２０は、シリコン（Ｓｉ）を用いて構成されている。 Next, the 2nd terminal part 20 contains the recessed part 20a engaged with the 1st terminal part 10 of the said cochlear implant part 1 as mentioned above. Similar to the first base 11 and the second base 22, the second terminal portion 20 is configured with a rigid material among metals, inorganic substances, resins, and the like. The second terminal portion 20 in FIG. 1 is configured using silicon (Si).
第２端子部２０の基端側、すなわち図示左側でかつ蝸牛の内壁側に設けられた溝状の凹部２０ａは、図２（ａ），図２（ｂ）の断面図に示すように、その凹部底面２０ｃには、先に述べた表面電極層２７の延設部位が配設されている。また、凹部２０ａの内壁面２０ｂには、第１端子部１０の側面に設けられた端子部段部１０ｂ（図２参照）に係合可能な、凹部内凸部である係合用凸部２０ｄが形成されている。 As shown in the cross-sectional views of FIGS. 2 (a) and 2 (b), the groove-shaped recess 20a provided on the proximal end side of the second terminal portion 20, that is, on the left side in the drawing and on the inner wall side of the cochlea, The extension portion of the surface electrode layer 27 described above is disposed on the recess bottom surface 20c. Further, on the inner wall surface 20b of the concave portion 20a, an engaging convex portion 20d that is an concave convex portion that can be engaged with the terminal portion step portion 10b (see FIG. 2) provided on the side surface of the first terminal portion 10 is provided. Is formed.
これにより、図１（ｄ）および図２（ｂ）のように、蝸牛埋植部１の第１端子部１０が、音波共振部２の第２端子部２０の凹部２０ａに嵌め入れられた場合、先に述べた係合用凸部２０ｄが端子部段部１０ｂ部位に係合して、この第１端子部１０をしっかりと固定することができる。また、上記係合により、第１端子部１０の端子部裏面１０ａに配設された、一方の端子電極である導電体層１３が、第２端子部２０の凹部底面２０ｃに設けられた、他方の端子電極である表面電極層２７の延設部位に当接して押し付けられるため、これらの間の電気的な導通を、確実なものとすることができる。 Thereby, when the 1st terminal part 10 of the cochlear implantation part 1 is inserted in the recessed part 20a of the 2nd terminal part 20 of the acoustic resonance part 2, like FIG.1 (d) and FIG.2 (b). The engaging convex portion 20d described above engages with the terminal portion step portion 10b, so that the first terminal portion 10 can be firmly fixed. In addition, due to the above engagement, the conductor layer 13, which is one terminal electrode, disposed on the terminal portion back surface 10 a of the first terminal portion 10 is provided on the concave bottom surface 20 c of the second terminal portion 20. Since the surface electrode layer 27, which is the terminal electrode, is pressed against the extended portion of the surface electrode layer 27, electrical conduction between them can be ensured.
なお、第２端子部２０の係合用の凹部２０ａの溝形状やその断面形状は、図１，図２の形状に特に限定されるものではない。また、係合用の凹部２０ａに係合する被係合側の、蝸牛埋植部１の第１端子部１０の外形形状も、係合用の凹部２０ａの形状に合わせて、適宜変更すればよい。さらに、凹部凸部を、逆側に形成してもよい、すなわち、第１端子部１０側に係合用の凹部を、第２端子部２０側に被係合用の凸部を形成することもできる。 The groove shape and the cross-sectional shape of the engaging recess 20a of the second terminal portion 20 are not particularly limited to the shapes shown in FIGS. Moreover, what is necessary is just to change suitably the external shape of the 1st terminal part 10 of the cochlear implantation part 1 of the to-be-engaged side engaged with the recessed part 20a for engagement according to the shape of the recessed part 20a for engagement. Further, the concave convex portion may be formed on the opposite side, that is, the engaging concave portion may be formed on the first terminal portion 10 side, and the engaged convex portion may be formed on the second terminal portion 20 side. .
たとえば、図３に示すような、係合用の凹部２０ａの溝形状の中に、その全体が納まるような大きさの第１端子部１０’としてもよい。この第１端子部１０’の形状によっても、先の例と同様、第１端子部１０’と第２端子部２０との係合により、端子部裏面１０ａの導電体層１３が、凹部底面２０ｃの表面電極層２７に押し付けられるため、確実な電気的導通を確保することができる。 For example, as shown in FIG. 3, the first terminal portion 10 ′ having such a size that the whole can be accommodated in the groove shape of the recess 20 a for engagement may be used. Also according to the shape of the first terminal portion 10 ′, the conductor layer 13 on the back surface 10a of the terminal portion becomes the bottom surface 20c of the recess due to the engagement between the first terminal portion 10 ′ and the second terminal portion 20 as in the previous example. Since it is pressed against the surface electrode layer 27, reliable electrical conduction can be ensured.
また、たとえば、図４の係合用の溝形状の凹部２０ａの上面図に示すように、この凹部２０ａの第１端子部１０側の開口縁部、すなわち図示左側でかつ蝸牛の内壁側を、大きく開口するテーパー状としてもよい。これにより、第１端子部１０の、第２端子部２０’への嵌め入れを容易とすることができる。その結果、第１端子部１０と第２端子部２０’との間の、確実な電気的導通を確保することができる。 Further, for example, as shown in the top view of the groove-shaped recess 20a for engagement shown in FIG. 4, the opening edge of the recess 20a on the first terminal portion 10 side, that is, the left side in the figure and the inner wall side of the cochlea is greatly enlarged. It is good also as the taper shape which opens. Thereby, the insertion of the first terminal portion 10 into the second terminal portion 20 ′ can be facilitated. As a result, reliable electrical continuity between the first terminal portion 10 and the second terminal portion 20 ′ can be ensured.
つぎに、前述の蝸牛埋植部１および音波共振部２からなる、実施形態の人工聴覚器を、蝸牛内に埋植・配設する方法について説明する。 Next, a method for implanting / arranging the artificial hearing instrument of the embodiment including the cochlear implanting unit 1 and the sound wave resonance unit 2 in the cochlea will be described.
まず、人工聴覚器を配設する耳の基本構造を図９（ａ）に、内耳の蝸牛の基本構造を図９（ｂ）に示す。なお、これら基本的な耳の構造は、各部位の名称に符号を付して、各構成の詳細な説明は省略する。 First, FIG. 9 (a) shows the basic structure of the ear on which the artificial hearing device is disposed, and FIG. 9 (b) shows the basic structure of the cochlea of the inner ear. Note that, in these basic ear structures, reference numerals are given to the names of the respective parts, and detailed descriptions of the respective structures are omitted.
図９（ａ）において、聴覚を司る感覚器である耳は、外耳１００、中耳２００および内耳３００に分けられる。耳の外で発生した音波は、外耳道１０１から鼓膜１０２に導かれ、鼓膜１０２を振動させ、その音波振動は、耳小骨２０１を通じて、蝸牛３０１の内部へ伝えられる。 In FIG. 9A, the ear that is a sensory organ that controls hearing is divided into an outer ear 100, a middle ear 200, and an inner ear 300. A sound wave generated outside the ear is guided from the ear canal 101 to the eardrum 102 and vibrates the eardrum 102, and the sound wave vibration is transmitted to the inside of the cochlea 301 through the ear ossicle 201.
蝸牛３０１は約２回転半巻の管状である。その内部は、図９（ｂ）に示すように、前庭階３０２、中央階３０３および鼓室階３０４の３つの領域に分けられ、各領域は、リンパ液で満たされている。前庭階３０２と中央階３０３とは、ライスネル膜３０５により仕切られ、中央階３０３と鼓室階３０４とは、基底膜３０６により仕切られている。 The cochlea 301 has a tubular shape of about two and a half turns. As shown in FIG. 9B, the interior is divided into three areas, a front yard floor 302, a central floor 303, and a tympanic floor 304, and each area is filled with lymph. The vestibular floor 302 and the central floor 303 are partitioned by the Ricenell film 305, and the central floor 303 and the tympanic floor 304 are partitioned by the basement film 306.
基底膜３０６は、伝播した音波によって振動し、その振動を受けて、基底膜３０６上にある内有毛細胞３０７が屈曲する。内有毛細胞３０７は、蓋膜３０８との相対的な運動により変形して、電位変動を生ずる。蝸牛３０１の各部分で、電位変動である刺激を受けた聴神経節であるラセン神経節細胞３０９の束は、蝸牛３０１において生じた電気信号を脳へ伝え、大脳皮質に至った際には、様々な周波数成分を有する複合音として認識される。 The basement membrane 306 is vibrated by the propagated sound wave, and the inner hair cells 307 on the basement membrane 306 are bent by receiving the vibration. The inner hair cell 307 is deformed by a relative movement with the cap membrane 308 to generate a potential fluctuation. In each part of the cochlea 301, a bundle of spiral ganglion cells 309, which are auditory ganglia that have been stimulated by potential fluctuations, transmit electrical signals generated in the cochlea 301 to the brain, and when they reach the cerebral cortex, It is recognized as a complex sound having a large frequency component.
図５は、前述の構成の人工聴覚器を蝸牛３０１内に、基底膜３０６に平行に設置した例を示す図であり、図６は、前述の構成の人工聴覚器を蝸牛３０１内に、基底膜３０６および鼓室階３０４断面に垂直に設置した例を示す図である。 FIG. 5 is a diagram illustrating an example in which the artificial hearing device having the above-described configuration is installed in the cochlea 301 in parallel with the basement membrane 306. FIG. 6 illustrates the artificial hearing device having the above-described configuration in the cochlea 301. It is a figure which shows the example installed perpendicularly | vertically to the film | membrane 306 and the tympanic floor 304 cross section.
これら図５，図６に示すように、実施形態の人工聴覚器を蝸牛３０１の鼓室階３０４内に設置する場合は、いずれの場合もまず、蝸牛３０１の外部において、人工聴覚器を、蝸牛埋植部１と音波共振部２とに分離する。そのうち、蝸牛埋植部１を蝸牛３０１内に挿入し、鼓室階３０４の内部から、くさび状の蝸牛埋植部１の尖った先端部１１ａを、蝸牛３０１の内壁を通して、ラセン神経節細胞３０９の束である聴神経節に向けて挿入し、蝸牛埋植部１を、その基端部１１ｂ近傍まで埋め込んで埋植する。この際、埋め込みの程度は、図５（ａ），図６（ａ）に示す状態、すなわち蝸牛埋植部１の第１端子部１０が、蝸牛３０１の内壁より蝸牛３０１内に突出する程度とする。 As shown in FIGS. 5 and 6, when the artificial hearing instrument of the embodiment is installed in the trumpet floor 304 of the cochlea 301, in any case, the artificial hearing instrument is first placed outside the cochlea 301. The planting part 1 and the acoustic wave resonance part 2 are separated. Among them, the cochlear implant 1 is inserted into the cochlea 301, and the sharp tip 11 a of the wedge-shaped cochlear implant 1 is passed through the inner wall of the cochlea 301 from the inside of the trumpet floor 304, and the spiral ganglion cell 309. It is inserted toward the auditory ganglion that is a bundle, and the cochlear implant 1 is embedded up to the vicinity of the proximal end portion 11b. At this time, the degree of embedding is the state shown in FIGS. 5A and 6A, that is, the first terminal portion 10 of the cochlear implant portion 1 protrudes into the cochlea 301 from the inner wall of the cochlea 301. To do.
ついで、音波共振部２を、同じ蝸牛３０１内に挿入し、先に埋植済みの蝸牛埋植部１の第１端子部１０に、この音波共振部２の第２端子部２０の凹部２０ａを接近させて嵌め合わせ、第１端子部１０の端子部段部１０ｂと、凹部２０ａ内部の係合用凸部２０ｄとを係合させることにより、蝸牛３０１内における、蝸牛埋植部１と音波共振部２との、電気的導通が確保された設置を完了することができる。 Next, the acoustic resonance unit 2 is inserted into the same cochlea 301, and the concave portion 20a of the second terminal unit 20 of the acoustic resonance unit 2 is formed on the first terminal unit 10 of the cochlear implantation unit 1 that has already been implanted. The cochlear implant part 1 and the sonic resonance part in the cochlea 301 by engaging and fitting the terminal step part 10b of the first terminal part 10 and the engaging convex part 20d inside the concave part 20a. The installation with electrical continuity with 2 can be completed.
ところで、従来、同様の人工聴覚器を蝸牛内に配設しようとする際は、人工聴覚器が、蝸牛埋植部と音波共振部が不可分で分離不能の一体型であったため、蝸牛埋植部の埋植時に、音波共振部にも、電極押し込みに伴う不要な圧力と荷重とが加わり、この音波共振部が、割れたり曲ったり、破損してしまう場合があった。 By the way, when trying to arrange a similar artificial hearing instrument in the cochlea conventionally, the cochlear implant part is an integral type in which the cochlear implant part and the sound wave resonance part are inseparable and cannot be separated. At the time of implantation, unnecessary pressure and load accompanying the pressing of the electrode are also applied to the sonic resonance part, and this sonic resonance part may be cracked, bent or broken.
これに対して、本実施形態の人工聴覚器は、蝸牛埋植部１と音波共振部２とが分離可能であるため、荷重のかかる蝸牛埋植部１の押し込み時に、音波共振部２を蝸牛埋植部１から取り外しておくことで、この音波共振部２に余計な力が加わらず、その破損を防止することができる。したがって、本実施形態の人工聴覚器は、蝸牛内への埋植時にも、音波の変換部２１や音波共振部２に破損の発生することのない、信頼性の高い人工聴覚器とすることができる。 On the other hand, since the cochlear implant part 1 and the sonic resonance part 2 are separable in the artificial hearing instrument of this embodiment, the sonic resonance part 2 is used as the cochlea when the cochlear implant part 1 is loaded. By removing from the embedded portion 1, an excessive force is not applied to the sound wave resonance portion 2, and the damage can be prevented. Therefore, the artificial hearing instrument of this embodiment is a highly reliable artificial hearing instrument that does not cause damage to the sound wave conversion unit 21 or the sound wave resonance unit 2 even when implanted in the cochlea. it can.
なお、前述の、蝸牛３０１の鼓室階３０４内における音波共振部２の蝸牛埋植部１への取り付けを容易にするために、蝸牛埋植部１および音波共振部２の少なくとも一方に、第２端子部２０の第１端子部１０への接近を案内するガイド部を設けてもよい。あるいは、第２端子部２０の第１端子部１０への接近を案内するガイド部材を配設してもよい。 In addition, in order to facilitate the attachment of the acoustic resonance unit 2 to the cochlear implantation unit 1 in the trumpet floor 304 of the cochlea 301, at least one of the cochlear implantation unit 1 and the acoustic resonance unit 2 is second. You may provide the guide part which guides the approach to the 1st terminal part 10 of the terminal part 20. FIG. Or you may arrange | position the guide member which guides the approach to the 1st terminal part 10 of the 2nd terminal part 20. FIG.
図７にガイド部の構成の一例を、図８にガイド部材の構成の一例を示す。 FIG. 7 shows an example of the configuration of the guide portion, and FIG. 8 shows an example of the configuration of the guide member.
図７に示す人工聴覚器は、第１端子部１０の近傍に、蝸牛埋植部１から延設されたガイド部１４を備える。このガイド部１４は、第１基体１１の一部を、第１端子部１０の突出方向と同じ方向に延設して形成されており、図のように、音波共振部２の一端をガイド部１４に突き当てることにより、この音波共振部２の位置決めを行えるようになっている。この構成により、蝸牛の鼓室階内等、スペースに余裕がない場所においても、音波共振部２の蝸牛埋植部１への取り付けを、容易に行うことができる。 The artificial hearing instrument shown in FIG. 7 includes a guide portion 14 extending from the cochlear implant portion 1 in the vicinity of the first terminal portion 10. The guide portion 14 is formed by extending a part of the first base 11 in the same direction as the protruding direction of the first terminal portion 10, and as shown in FIG. 14, the sound wave resonance unit 2 can be positioned. With this configuration, it is possible to easily attach the acoustic resonance unit 2 to the cochlear implant unit 1 even in a place where there is not enough space, such as in the cochlea trumpet floor.
図８に示す人工聴覚器は、蝸牛内に埋植後の蝸牛埋植部１に予め、ガイド部材３０が取り付けられている。また、音波共振部２には、ガイドリング３１が取り付けられており、このガイドリング３１を、ガイド部材３０の棒状部分に挿通することにより、音波共振部２のガイド部材３０に沿った移動を可能としている。なお、音波共振部２における第２端子部２０’の係合用凹部２０ａの溝形状は、図４で示したような、第１端子部１０’側が大きく開口するテーパー状となっている。また、蝸牛埋植部１の第１端子部１０’も、図３で示したような、厚みの薄い形状となっている。 In the artificial hearing instrument shown in FIG. 8, a guide member 30 is attached in advance to the cochlear implantation part 1 after implantation in the cochlea. Further, a guide ring 31 is attached to the sonic resonance unit 2, and the guide ring 31 can be moved along the guide member 30 of the sonic resonance unit 2 by inserting the guide ring 31 into a bar-shaped portion of the guide member 30. It is said. In addition, the groove shape of the engaging recess 20a of the second terminal portion 20 'in the sound wave resonance portion 2 is a tapered shape having a large opening on the first terminal portion 10' side as shown in FIG. Further, the first terminal portion 10 ′ of the cochlear implant portion 1 has a thin shape as shown in FIG. 3.
この構成によっても、蝸牛の鼓室階内等、スペースに余裕がない場所において、第２端子部２０’の第１端子部１０’への接近と嵌め入れ、すなわち音波共振部２の蝸牛埋植部１への取り付けを、容易に行うことができる。 Even in this configuration, in the place where there is not enough space, such as in the trumpet floor of the cochlea, the approach and fitting of the second terminal part 20 ′ to the first terminal part 10 ′, that is, the cochlear implant part of the acoustic resonance part 2 Attachment to 1 can be performed easily.
なお、以上の実施形態で示した蝸牛埋植部１および音波共振部２の大きさや形状、特に平面形状は、一例にすぎず、対象あるいは受信しようとする音波の周波数に合わせて、他のどのような形状にでも変更することができる。また、蝸牛内における人工聴覚器の配設角度や方向等も、図７，図８の例に限らず、適宜に設定することができる。 The size and shape of the cochlear implant part 1 and the acoustic wave resonance part 2 shown in the above embodiment, in particular, the planar shape are merely examples, and any other one is selected according to the frequency of the target or the acoustic wave to be received. Even the shape can be changed. Moreover, the arrangement | positioning angle, direction, etc. of the artificial hearing device in a cochlea are not restricted to the example of FIG. 7, FIG. 8, but can be set suitably.
また、本発明は上述の実施の形態に限定されるものではなく、本発明の要旨を逸脱しない範囲内において、種々の変更、改良等が可能である。 The present invention is not limited to the above-described embodiments, and various changes and improvements can be made without departing from the scope of the present invention.
１ 蝸牛埋植部
１０，１０’ 第１端子部
１１ 第１基体
１３ 導電体層（神経刺激用電極）
１４ ガイド部
２ 音波共振部
２０，２０’ 第２端子部
２０ａ 凹部
２１ 変換部
２１ａ 調節錘部
２２ 第２基体
２６ 圧電体層
３０ ガイド部材
３１ ガイドリング
DESCRIPTION OF SYMBOLS 1 Cochlear implant part 10,10 '1st terminal part 11 1st base | substrate 13 Conductor layer (electrode for nerve stimulation)
DESCRIPTION OF SYMBOLS 14 Guide part 2 Sound wave resonance part 20,20 '2nd terminal part 20a Recessed part 21 Conversion part 21a Adjustment weight part 22 2nd base | substrate 26 Piezoelectric layer 30 Guide member 31 Guide ring
Claims (4)
分離可能な、蝸牛埋植部および音波共振部を備え、
前記蝸牛埋植部は、聴神経刺激用の電極と、前記電極を支持する第１基体と、該第１基体の一端部に配設され、前記電極と電気的に接続される第１端子部と、を含み、
前記音波共振部は、固有の振動数を有する第２基体と、前記第２基体の振動を電気信号に変換する変換部と、該変換部と電気的に接続されるとともに前記第１端子部と係合可能な第２端子部と、を含み、
前記蝸牛埋植部は、前記第１端子部が蝸牛の内部に向けて突出するよう、蝸牛の内壁に埋植され、
前記音波共振部は、前記第２端子部を前記第１端子部に係合させて、蝸牛の内部に配設される、人工聴覚器。 An artificial hearing device that converts sound waves that reach the cochlea of the inner ear into electrical signals and transmits them to the auditory nerve,
Separable, cochlear implant and sonic resonator
The cochlear implant includes an acoustic nerve stimulation electrode, a first base that supports the electrode, a first terminal that is disposed at one end of the first base and is electrically connected to the electrode. Including,
The sound wave resonance unit includes a second base having a specific frequency, a conversion unit that converts the vibration of the second base into an electric signal, and the first terminal unit that is electrically connected to the conversion unit. An engaging second terminal portion,
The cochlear implantation part is implanted on the inner wall of the cochlea so that the first terminal part protrudes toward the inside of the cochlea,
The sound wave resonance unit is an artificial hearing instrument that is disposed inside a cochlea with the second terminal unit engaged with the first terminal unit.
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| US5061282A (en) * | 1989-10-10 | 1991-10-29 | Jacobs Jared J | Cochlear implant auditory prosthesis |
| JP2014045937A (en) * | 2012-08-31 | 2014-03-17 | Osaka Univ | Artificial sensory epithelium |
| JP2018033826A (en) * | 2016-09-02 | 2018-03-08 | 京セラ株式会社 | Cochlear implant |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5061282A (en) * | 1989-10-10 | 1991-10-29 | Jacobs Jared J | Cochlear implant auditory prosthesis |
| JP2014045937A (en) * | 2012-08-31 | 2014-03-17 | Osaka Univ | Artificial sensory epithelium |
| JP2018033826A (en) * | 2016-09-02 | 2018-03-08 | 京セラ株式会社 | Cochlear implant |
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| JPWO2020121997A1 (en) * | 2018-12-12 | 2020-06-18 | ||
| WO2020121997A1 (en) * | 2018-12-12 | 2020-06-18 | 京セラ株式会社 | Artificial auditory organ and implantation-type piezoelectric device |
| JP7093957B2 (en) | 2018-12-12 | 2022-07-01 | 京セラ株式会社 | Artificial hearing devices and piercing piezoelectric devices |
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