JPS6055965A - Living body terminal for drug treating system - Google Patents

Abstract

(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

【発明の詳細な説明】 本発明はその要部がハイドロキシアパタイト等のアパタ
イト系材より成る生体端子に関する。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a bioterminal whose main part is made of an apatite material such as hydroxyapatite.

従来のｃａ旧＋ｕｌａ（挿管）といった生体用端子はそ
の一端が生体皮膚」二にあり細端か皮下に埋設されて、
その貫通孔を介して輸液、各種薬液等の注入又は人］−
腎臓透析等のための血流の取り出し・注入口等として使
用されるものであり、主としてシリコーンゴム、ふっ素
樹脂等の所謂生体不活性材より形成されたものが既に提
案されている。Conventional biomedical terminals such as ca old + ula (intubation) have one end on the living body's skin and are either narrow or buried subcutaneously.
Injection of infusions, various medicines, etc. or people through the through-hole]-
It is used as a blood flow extraction/injection port for kidney dialysis, etc., and those made mainly of so-called bioinert materials such as silicone rubber and fluororesin have already been proposed.

しかし乍らこれらは生体にとってはあくまでも異物に池
ならずその生体装置部位は一種の外傷を受けた状態に置
かれるものとなるので両者の間隙がらの細菌感染等によ
り長時間の使用には到底耐え得ないものであるのみなら
ず、生体固定性に劣るため例えば揺動による出血の心配
等、幾つかの問題を有するものであるため未だ充分に普
及し得ないものとなっている。However, these are not just foreign substances to the living body, and the parts of the living body are left in a state of trauma, so they cannot withstand long-term use due to bacterial infections between the two. Not only is it not possible to fix it in the body, but it also has several problems, such as concerns about bleeding due to shaking due to its inferior biofixability, so it has not yet been widely used.

例えば人工膵臓等の近時その発展か着るしい所謂薬物治
療（トラソゲ・デリバリ）システム（クラウス・ヘイル
マン著１薬物冶療システム」昭和５８年医菌薬出版発行
等、参照）にあっては、インスリン等の薬物の注入経路
の問題が未解決であり（医器学誌昭和５８年１５３巻第
２号第９０頁以下参照）、薬物注入口として半恒久的且
つ安全に使用し得る生体端子への希求は今日一段と高ま
っているものと云えよう。For example, in the so-called drug therapy delivery system (see Klaus Heilman, 1 Drug Therapy System, published by Ibakuyaku Publishing, 1980, etc.), which has recently been developed such as artificial pancreas, insulin The problem of the injection route for drugs such as the It can be said that the desire is even higher today.

池方、近時ハイドロキシアパタイト焼結体等のアバタイ
１系４・」の優れた生体親和性、更には骨誘導性が解明
されると共にその焼結体による人工歯根、人工骨への利
用が提案、実用されつつあるが、同焼結体の皮膚ｍ織と
の生理学的反応性については先行技術に於いて全熱未解
明である。Recently, the excellent biocompatibility and osteoinductivity of Avatai 1 series 4, such as sintered hydroxyapatite bodies, have been elucidated, and the use of the sintered bodies for artificial tooth roots and artificial bones has been proposed. Although it is being put into practical use, the physiological reactivity of the sintered body with skin tissue has not been completely elucidated in the prior art.

上記に鑑み本発明者らは鋭意研究の結果、驚くべ慇こと
にハイドロキシアパタイト焼結体等のアパタイト系材は
皮膚組織に対し単に親和性を有するのみならずこれら組
織と緊密且つ一体的に接合するという事実を知見し、本
発明に到達したものである。In view of the above, the present inventors conducted extensive research and surprisingly found that apatite-based materials such as sintered hydroxyapatite not only have an affinity for skin tissues, but also bond closely and integrally with these tissues. The present invention was developed based on this fact.

以下、本発明生体端子乃至栓或いは、導管につきその利
料組成及び製法、形状乃至構造、使用の態様等につ外詳
細に分脱する。Hereinafter, the bioterminal, plug, or conduit of the present invention will be described in detail, including its composition, manufacturing method, shape, structure, mode of use, etc.

材料組成・製法 本発明に於けるパアパタイト系材゛とはその化学組成が
Ｃａｌ。Material Composition/Manufacturing Method The paapatite material used in the present invention has a chemical composition of Cal.

（Ｐ○＜）６（ｏｒ−＋）４で表わされるハイドロキシ
アパタイトのみならず、ＯＨイオンのかわりに１〜１０
％のカーボネート（ＣＯ，）イオンや７ツソ、塩素イオ
ン或いはそのＣａの代わりにＭ８等を含むこともあるそ
の各種イオン置換体、或いはこれらを主成分とするも焼
結性、強度、細孔度等を向上すべくこれにＣａ５（Ｐ　
Ｏ’−）２゜Ｃａ４０（ＰＯ２）２１　ＭＨＯ＋　Ｎ！
１２０１　Ｋ２０＋ＣａＦ２ｔ　Ａｌ２Ｏ３゜ＳｉＯ２
，ＣａＯ９Ｆｅ２０３．ＭｎＯ，ＭｎＯ２，Ｚｌｌｏ、
Ｃ，ＳｒＯ。Not only hydroxyapatite represented by (P○<)6(or-+)4, but also 1 to 10 in place of OH ions.
% of carbonate (CO,) ions, chlorine ions, or their various ion substituted products that may contain M8 instead of Ca, or those containing these as the main components, have a high sinterability, strength, and porosity. In order to improve the
O'-)2゜Ca40(PO2)21 MHO+ N!
1201 K20+CaF2t Al2O3゜SiO2
, CaO9Fe203. MnO, MnO2, Zllo,
C, SrO.

ＰｂＯ１ＢａＯ９ＴｉＯ＝、ＺｒＯ２又は各種高分子材
等々の周知各種添加剤を添加混合したものをも包含する
。It also includes mixtures of various well-known additives such as PbO1BaO9TiO=, ZrO2, or various polymeric materials.

ここで、高分子との複合剤とする場合は、比較的毒性の
少ないポリエチレン、ポリプロピレン、ポリメ９ルメタ
クリレート、ポリウレタン、ポリエステル、ＡＢＳ樹脂
、フッ素樹脂、ポリカーボネート、ポリスルホン、エポ
キシ樹脂、シリコン樹脂、ジアリルフタレート樹脂、７
ラン樹脂等の樹脂を選ぶことができる。Here, when using a composite agent with a polymer, relatively less toxic polyethylene, polypropylene, polymethacrylate, polyurethane, polyester, ABS resin, fluororesin, polycarbonate, polysulfone, epoxy resin, silicone resin, diallyl phthalate are used. resin, 7
Resins such as orchid resin can be selected.

他方、その製造法としては単体或いは金属等の見料上で
の所謂焼結法を始めとして金属等の基材へのプラズマ溶
射法等を例示し得、例えばその単独焼結体は一般にハイ
ドロキシアパタイト粉末を金型又はラバープレス等にょ
ｌ）　５００〜３　＋　０００ｋＢ／ａ１ｆｉ２程度の
圧力下、所望の形状に圧縮成形し、次いでこれを７００
〜１．３００℃程度の温度で焼結処理して得られるもの
であるが、その池の製法及び組成を含めてより詳細は下
記公知技術が参照される。すなわち、特開昭５１−４０
４００、同５ｌ−Ｇ４１９９、同５２−８２８９３、同
５２−１４２７　ｏ　７、同５２−１４７６０６、同５
２−１４９８９５、同５３−２８９９７、同５３−７５
２０９、同５３＝１１１０００．同５３−１１８４１１
、同５３−１４４１９４、同５３−１１０９９９、同５
４　１．５８０９９、同５５−５１７５１、同５５−１
３０８５４、同５５−１４０７５６、同５６−４．５８
１４、同５　Ｇ　−Ｉ　Ｇ　６８　＋ｉ、　３、特公昭
５７−４０７マ６及び同５７−４０８（、）３号各公報
。On the other hand, examples of manufacturing methods include a so-called sintering method on a single body or a sample of metal, and a plasma spraying method on a base material such as metal.For example, the single sintered body is generally made of hydroxyapatite. The powder is compression molded into a desired shape under a pressure of about 500 to 3 + 000 kB/a1fi2 in a mold or rubber press, etc., and then this is
Although it is obtained by sintering at a temperature of about 1.300° C., the following known techniques are referred to for more details including the method and composition of the pond. That is, JP-A-51-40
400, 5l-G4199, 52-82893, 52-1427 o 7, 52-147606, 5
2-149895, 53-28997, 53-75
209, 53=111000. 53-118411
, 53-144194, 53-110999, 5
4 1.58099, 55-51751, 55-1
30854, 55-140756, 56-4.58
14, 5 G-I G 68 +i, 3, Japanese Patent Publications No. 57-407 Ma 6 and No. 57-408 (,) 3.

尚、皮膚組織との接合性という観点から本発明に於いて
特に有用な焼結体の相対密度（ハイドロキシアパタイト
単結晶の密度を基準）は、６０〜９９．５％、より好ま
しくは８５〜５〕５％程度である。In addition, the relative density (based on the density of hydroxyapatite single crystal) of the sintered body that is particularly useful in the present invention from the viewpoint of bondability with skin tissue is 60 to 99.5%, more preferably 85 to 5%. ] About 5%.

形状乃至構黛、 本発明生体端子形態は使Ｊ１月」的に応じて所望のもの
となし得るが、その典型例につき添付図面を参照して詳
説すれば次の通りである。The shape and structure of the bioterminal of the present invention can be made into any desired shape depending on the usage, and typical examples thereof will be explained in detail with reference to the accompanying drawings as follows.

すなわち、第１図は本発明生体端子の１例を示す断面図
であり、図中、薬物注入口として使用される生体端子ｌ
は共にハイドロキシアパタイト焼結体より成る端子頭部
２と同底部３とを一体的に又はシリコーン１邊ｊ脂製１
・ｊの合成樹脂製筒体５を装着して成るもので・あり、
その↓′１通孔６を介して所望薬物か生体内に注入され
る。That is, FIG. 1 is a sectional view showing one example of the bioterminal of the present invention, and in the figure, the bioterminal l used as a drug injection port is shown.
The terminal head part 2 and the bottom part 3, both made of sintered hydroxyapatite, are integrated or made of silicone resin.
・It is equipped with a synthetic resin cylinder 5 of j.
A desired drug is injected into the living body through the ↓'1 through hole 6.

他ノｊ、ハイドロキシアバタイＩ・焼結体（拐）等のア
バタイ）・系材は皮唐紙銖との接触部分１こ介在すれば
’ｉ”Ｊｉ定の目的を達成い）るのであるか呟生木端子
の要部のみを当該４＝４で形成し池を合成杉］脂等の異
種４・４で構成するようにしてもよく、或いはその要部
をアパタイト焼結被覆相（特開昭ｂ２’　８２８’９３
号、同５３−７５２０９号及び同５３　１１８４１１号
公報等、参照）で形成してもよい。Other materials such as hydroxyl avatars I, sintered bodies, etc. can achieve the specified purpose if there is only one contact area with the sintered material. Only the main part of the raw wood terminal may be formed with the 4=4, and the pond may be made of a different type of 4.4 such as synthetic cedar] fat, or the main part may be formed with an apatite sintered coating phase (Unexamined Japanese Patent Publication No. Showa b2'828'93
No. 53-75209 and No. 53-118411, etc.).

例えば微小金属管外周にハイドロキシアパタイト溶剤乃
至焼結層を形成して成る微小管を生体端子として使用し
得る。For example, a microtube formed by forming a hydroxyapatite solvent or sintered layer on the outer periphery of a micrometallic tube can be used as a bioterminal.

第２図は微小管状生体端子■の断面図であり、金管等の
金属管７の外周にハイドロキシアパタイト焼結被覆層乃
至溶射）ＶＩ８を形成し、フィルタ１０を有する除菌フ
ィルタ手段９を端部に連結して成るものであり、患者の
皮膚に単に埋設、固定して使用される。FIG. 2 is a cross-sectional view of a microtubular bioterminal (2), in which a hydroxyapatite sintered coating layer (or thermal spraying) VI8 is formed on the outer periphery of a metal tube 7 such as a brass tube, and a sterilization filter means 9 having a filter 10 is attached to the end thereof. It is connected to the patient's skin and is used by simply embedding and fixing it in the patient's skin.

以上から明らかなように、本発明生体端子は多様な形状
・構造及び寸法をと１）得るものであって特定形態【こ
限定されるものではない。As is clear from the above, the bioterminal of the present invention can have various shapes, structures, and dimensions (1) and is not limited to a specific form.

使用態様 前述の通り、本発明によりハイドロキシアバタイ１焼結
体等の７パタイト系拐による生体端子は生木適合性を有
するのみならず表皮、真皮等の皮ｒｆ′Ｉ組織と界面接
合し生体に安定的に固定されるものであることか明らか
にされたので、各種ＩＳラング・デリハ゛リシステムに
於ける薬物投入口として広汎な応用が可能であり、使用
に当っては皮膚にＪ用膜、固定（インブラント）された
生体端子に、マイクロ・ポンプ等で定量的に駆動された
薬液を送入するチュー７等を単に連絡すれば足りる。Mode of Use As mentioned above, according to the present invention, the bioterminal made of the 7patite system such as the sintered hydroxyabatai 1 is not only compatible with living wood, but also has interfacial bonding with skin rf'I tissues such as the epidermis and dermis, making it suitable for living organisms. Since it has been shown that it is stably fixed to the skin, it can be widely applied as a drug inlet in various IS lung delivery systems. It is sufficient to simply connect the fixed (implanted) biological terminal with a tube 7 or the like for quantitatively feeding a medicinal solution driven by a micro pump or the like.

ここで、本発明生体端子の特に有用な使用態様として、
薬物の駆動を電気化学的に行なう所謂イオントフオレー
ゼ（イオン導入療法）用注入口としての使用をあげ得る
。Here, as a particularly useful mode of use of the bioterminal of the present invention,
It can be used as an inlet for so-called iontophoresis (iontophoresis) in which drugs are driven electrochemically.

例えば従来人工膵臓に於けるインスリン司（Ｃ１の注入
は、微量定量注入ポンプ（前掲医器学誌参照）によりな
されるものであったか、これに代えて本発明インブラン
ト端子を単に直流電源の陽極に電気的に連結するのみで
インスリン・カチオンは極めて容易且つ安全に生体内に
導入され得るものとなる。For example, conventionally, injection of insulin (C1) in an artificial pancreas was performed using a micrometer injection pump (see above-mentioned medical journal). Insulin cations can be introduced into the body very easily and safely only by electrical connection.

なぜなら、通常のイオントフオレーゼは皮膚」二から施
術されるものであるが、その場合専ら皮膚角質層が電気
的並びに物理的バリヤ層となり、インスリン等の比較的
大分子の導入は困難であったが、本発明生体端子に依れ
ば皮膚角質層はもはやバリヤとなり得ないのでインピー
ダンス及び物理的抵抗の着るしい低下かもたさ」ｔ、し
かも電流値（通常、インスワンの場合直流乃至パルス直
；光で数μＡ−数＋ｎ　Ａの範囲内）をコントロールす
ることによりその定量的或いはグルコース・センサによ
るフィードバンク注入が容易に達１されるものであ机 すなわち、本発明生体端子をイオントフオレーゼに使用
する場合は、従来イオントフオレーゼに於ける薬液含浸
導子（一般にスポンジ、フントン等の保水祠或いは親水
性ゲル祠より成る）に代えて、インブラント生木端子に
薬液注入導管を連結して関導子とし、周知の各種生体電
極（例えば、特開昭５８１００６６又は特願昭５Ｃ１−
１０６９３５号公報、参照）より成る不関導子を皮膚の
他の箇所に貼着し、両者間に直流電流（イオン性薬剤が
カチオンならば関導子陽極、等）を通ずれば足りるもの
である。This is because conventional iontophoresis is performed from the skin, but in that case the stratum corneum serves as an electrical and physical barrier layer, making it difficult to introduce relatively large molecules such as insulin. However, with the bioterminal of the present invention, the stratum corneum of the skin can no longer act as a barrier, so impedance and physical resistance can be considerably reduced. Quantitative or feedbank injection using a glucose sensor can be easily achieved by controlling the amount of ions (within the range of several μA - several + nA). In other words, the bioterminal of the present invention can be used for iontophoresis. When using conventional iontophoresis, a chemical solution injection conduit can be connected to the implant's raw wood terminal instead of the chemical solution impregnated conductor (generally consisting of a water retaining hole such as a sponge or funton, or a hydrophilic gel hole). As a conductor, various well-known bioelectrodes (for example, Japanese Patent Application Laid-Open No. 5810066 or Japanese Patent Application No. 5C1-
It is sufficient to attach a non-conducting conductor made of 106935 (see Publication No. 106935) to other parts of the skin and passing a direct current between the two (if the ionic drug is a cation, use a non-conducting conductor anode, etc.). be.

尚、イオントフオレーゼ自体の詳細は前掲公報の記載が
参照される。For details of the iontophorase itself, refer to the description in the above-mentioned publication.

以下、本発明を実験例により詳細に説明する。Hereinafter, the present invention will be explained in detail using experimental examples.

実験例１ １、生体端子の製造 ハイドロキシアパタイト粉末は、０．５モル／β水酸カ
ルシウムと０．３モル／１リン酸溶液を徐々に滴下し、
３７℃で１日反応させて合成し、これを濾過乾燥して得
た。この合成粉末を金型に充填し、８００ｋＨ／ｃＩ０
２の圧力で圧縮成形し径２１１１１１１の貫通孔を有し
且つカサ密度１．６Ｈ／ｃ＋ｏコの圧粉体を得た。これ
を端子頭部形状（第１図参照）に旋盤及び歯利用ダイヤ
モンドバーで切削、加工した。同様に前記合成粉末を金
型に充填圧縮成形、切削加工して端子底部（第１図参照
）とした。次いで、側圧粉体の貫通孔を接合し、更に両
者間に予め水を加え乳鉢でよく練ったゲル状アパタイト
粉末を塗布し、接着した。これを１．　、２５０°Ｃで
１時間焼結処理して圧縮強度５　＋　０００　ｋｇ／ｃ
ｍ２、曲げ強度１　、２０　Ｃ１ｋｇ／ｃａｎ２、相対
密度９５％且つ接着部も均一に焼結した第１図に図示の
通りの生体端子を得た。Experimental Example 1 1. Production of bioterminal Hydroxyapatite powder was prepared by gradually dropping 0.5 mol/β calcium hydroxide and 0.3 mol/1 phosphoric acid solution.
The product was synthesized by reacting at 37° C. for one day, and the product was filtered and dried. This synthetic powder was filled into a mold and
Compression molding was performed at a pressure of 2 to obtain a green compact having through holes with a diameter of 2111111 and a bulk density of 1.6H/c+o. This was cut and processed into the shape of the terminal head (see Figure 1) using a lathe and a toothed diamond bur. Similarly, the synthetic powder was filled into a mold, compression molded, and cut to form a terminal bottom (see FIG. 1). Next, the through-holes of the side-pressed powder bodies were joined, and gel-like apatite powder, which had been thoroughly kneaded in a mortar with water added in advance, was applied between the two to bond them together. This is 1. , compressive strength 5 + 000 kg/c after sintering at 250°C for 1 hour
A bioterminal as shown in FIG. 1 was obtained, having a bending strength of 1.20 C1 kg/can2, a relative density of 95%, and a uniformly sintered adhesive portion.

ユニに於いて、端子底部は直径５　、４　ｎｕｎ、厚さ
２＋ｎ＋ｎ、端子頭一部首部分の径は４１ｎ１＾及び内
径２＋ｎｍである。In Uni, the terminal bottom has a diameter of 5.4 nm and a thickness of 2+n+n, and the terminal head and neck have a diameter of 41n1^ and an inner diameter of 2+nm.

尚、焼結温度を：１．．．１００°Ｃとした場合に得ら
れる焼結体にあっては、相対密度８５％、圧縮強度３　
、０００　ｋｇ／ｃａｎ２、曲げ強度７００　ｋｇ／ｃ
ｍ２であった。尚、最終的に、合成樹脂筒体に配設され
た除菌フィルタ手段を第１図の様に端子内に装着して試
供品とした。In addition, the sintering temperature is: 1. ．． ．． The sintered body obtained at 100°C has a relative density of 85% and a compressive strength of 3.
, 000 kg/can2, bending strength 700 kg/c
It was m2. Finally, a sterilizing filter means disposed in a synthetic resin cylinder was installed inside the terminal as shown in FIG. 1 to prepare a sample.

２、動物実吹 上記生体端子を雑種成人の側腹部皮膚に埋設し、経時観
察した結果、端子は底部及び負部分に於いて術後約２週
日で皮膚組織と強く結合接着して引っ張っても取れない
状態となり、１年経過後でも肉眼的には炎症反応などの
異常所見は何ら認められなかった。2. The above biological terminal was implanted in the skin of the flank of an adult mongrel, and observation over time revealed that the terminal was strongly bonded to the skin tissue at the bottom and negative part about 2 weeks after the surgery, and even when pulled. Even after one year, no abnormal findings such as an inflammatory reaction were observed with the naked eye.

また、通常の」ｔａ学的検索でも炎症！＋１１胞などは
認められなかった。In addition, even a normal ``ta'' search can lead to inflammation! +11 cells were not observed.

胆力、対照とした同形状のシリコーンゴム製端子にあっ
ては術後４週日でも皮膚との接着は全黙認められず既に
炎症性の発赤が認められた。又、２ケ月目には炎症か進
行し化膿し始め、３ケ月目には脱落した。Regarding the silicone rubber terminal of the same shape used as a control, no adhesion to the skin was observed even 4 weeks after the surgery, and inflammatory redness was already observed. Also, in the second month, the inflammation progressed and it began to suppurate, and in the third month, it fell off.

実験例■ 前記ハイドロキシアパタイト粉末に添加剤としてＣａ３
（ＰＯ４）２７％、ＭｇＯ００８％、Ｎａ２Ｏ１、’８
％、Ｋ　２０　１）　、　２％及びＣａＦｅ　Ｏ，２％
を添加した混合粉末を出発材料とした点を除き、池は前
記例と同様にして径１　ｎｕｎの金管を含む小円桂状焼
結体（外径３＋ｎｍ）を製造し、これを研摩拐で研摩処
理して添１・ｊ第２図に図示する形状の微小管状端子を
得た。Experimental example ■ Adding Ca3 as an additive to the hydroxyapatite powder
(PO4) 27%, MgO008%, Na2O1, '8
%, K20 1), 2% and CaFeO, 2%
Ike produced a small conical sintered body (outer diameter 3+nm) containing a brass tube with a diameter of 1 nm in the same manner as in the previous example, except that the starting material was a mixed powder containing After polishing, a microtubular terminal having the shape shown in Figure 2 in Appendix 1.j was obtained.

この端子の焼結体部分の長さは８ｍ＋ｎ、外径２ｍｍで
あった。The length of the sintered body part of this terminal was 8 m+n, and the outer diameter was 2 mm.

次にこれに除菌フィルタ手段を第２図のように連結した
後、成人胸部にその先端が皮下に位置するように刺通埋
設した処、約３週後には皮膚組織と完全に接合、固定さ
れた状態となった。Next, a sterilizing filter was connected to this as shown in Figure 2, and the filter was inserted into the chest of an adult so that its tip was located subcutaneously. After about 3 weeks, it was completely bonded and fixed to the skin tissue. It became a state.

そこで、端子端部を生理食塩水の充填された導管に接合
し、直流１．７にΩの値が得られた。角質層を介した皮
膚抵抗が通常１００にΩ程度であることと対比すると、
抵抗の着るしい低下が認められる。Therefore, the terminal end was joined to a conduit filled with physiological saline, and a DC value of 1.7 Ω was obtained. In contrast to the fact that the skin resistance through the stratum corneum is usually around 100Ω,
A noticeable decrease in resistance is observed.

【図面の簡単な説明】[Brief explanation of drawings]

添付第１乃至２図は本発明生体端子の模式断面図である
。 Ｉ、■・・・ｉ物治療システム用生体端子２・・・端子
頭部、３・・・端子底部、４．１０・・・除菌フィルタ
、５，９・・・筒体、６・・・貫通孔。 特許出願人　株式会社　アドバンス開発研究所手続補正
書（方式） 昭和５９年２月８日 特許庁長官　若、杉　和　夫　殿 １、事件の表示 昭和５８年特許願第１６２６４５号 ２、発明の名称 薬物治療システム用生体端子 ３、補正をする者 事件との関係　特許出願人 住所　〒１０３　東京都中央区日本橋小月町５番７号（
置、０３−６６７−１５５１） ４、補正命令の日刊 昭和５９年１月１１Ｌ１ （発送日　昭和５９年１月３１日） ５、補正の対象 明細書全文 ６、補正の内容 明細書の浄岩（内容に変更なし）Attached Figures 1 and 2 are schematic cross-sectional views of the bioterminal of the present invention. I, ■... Biomedical terminal for i-material treatment system 2... Terminal head, 3... Terminal bottom, 4.10... Sterilization filter, 5, 9... Cylindrical body, 6...・Through hole. Patent Applicant Advance Development Institute Co., Ltd. Procedural Amendment (Method) February 8, 1980 Director-General of the Patent Office Kazuo Sugi Waka 1, Indication of Case 1982 Patent Application No. 162645 2, Name of Invention Drug Bioterminal for treatment system 3, relationship with the case of person making correction Patent applicant address: 5-7 Kozuki-cho, Nihonbashi, Chuo-ku, Tokyo 103 (
03-667-1551) 4. Daily January 11, 1981 L1 of the amendment order (Date of dispatch: January 31, 1980) 5. Full text of the specification to be amended 6. Jogan ( (No change in content)

Claims (2)

【特許請求の範囲】[Claims] （１）少なくとも皮膚組織との接触部分かアパタイト系
材より成り、細菌防御用フィルタ：ｒ一段が内部乃至端
部に設けられており且つ薬液導通路を１１市えているこ
とを特徴とする経皮的治療システム用生本端子。(1) A transdermal device characterized by being made of an apatite-based material at least in the part that comes into contact with the skin tissue, having one stage of bacteria-protecting filters provided inside or at the end, and having 11 medicinal solution passages. Raw terminal for medical treatment system. （２）　イオン１７オレーゼ用端子であることを更に特
徴とする特許請求の範囲第（１）項に記載の前記生木端
子。(2) The green wood terminal according to claim (1), further characterized in that it is a terminal for ion 17 orese.