JPH0236882A - Medical appliance and manufacture thereof - Google Patents
Medical appliance and manufacture thereofInfo
- Publication number
- JPH0236882A JPH0236882A JP63186888A JP18688888A JPH0236882A JP H0236882 A JPH0236882 A JP H0236882A JP 63186888 A JP63186888 A JP 63186888A JP 18688888 A JP18688888 A JP 18688888A JP H0236882 A JPH0236882 A JP H0236882A
- Authority
- JP
- Japan
- Prior art keywords
- sliding member
- cylindrical body
- copolymer
- medical device
- gasket
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000004519 manufacturing process Methods 0.000 title claims description 8
- 229920005989 resin Polymers 0.000 claims abstract description 33
- 239000011347 resin Substances 0.000 claims abstract description 33
- -1 acrylic ester Chemical class 0.000 claims abstract description 18
- 229920001577 copolymer Polymers 0.000 claims abstract description 18
- 229920001971 elastomer Polymers 0.000 claims abstract description 13
- 229920000642 polymer Polymers 0.000 claims abstract description 6
- 239000002033 PVDF binder Substances 0.000 claims description 37
- 229920002981 polyvinylidene fluoride Polymers 0.000 claims description 37
- 229920002725 thermoplastic elastomer Polymers 0.000 claims description 15
- 239000000463 material Substances 0.000 claims description 14
- 229920006244 ethylene-ethyl acrylate Polymers 0.000 claims description 12
- 238000000034 method Methods 0.000 claims description 11
- 229920000459 Nitrile rubber Polymers 0.000 claims description 9
- 229920005992 thermoplastic resin Polymers 0.000 claims description 9
- JHPBZFOKBAGZBL-UHFFFAOYSA-N (3-hydroxy-2,2,4-trimethylpentyl) 2-methylprop-2-enoate Chemical compound CC(C)C(O)C(C)(C)COC(=O)C(C)=C JHPBZFOKBAGZBL-UHFFFAOYSA-N 0.000 claims description 8
- NLHHRLWOUZZQLW-UHFFFAOYSA-N Acrylonitrile Chemical compound C=CC#N NLHHRLWOUZZQLW-UHFFFAOYSA-N 0.000 claims description 8
- 239000005042 ethylene-ethyl acrylate Substances 0.000 claims description 6
- 239000005060 rubber Substances 0.000 claims description 6
- 229920002239 polyacrylonitrile Polymers 0.000 claims description 5
- 229920003229 poly(methyl methacrylate) Polymers 0.000 claims description 4
- 239000004926 polymethyl methacrylate Substances 0.000 claims description 4
- 229920000468 styrene butadiene styrene block copolymer Polymers 0.000 claims description 4
- 229920001400 block copolymer Polymers 0.000 claims description 3
- 229920006242 ethylene acrylic acid copolymer Polymers 0.000 claims description 3
- 229920000120 polyethyl acrylate Polymers 0.000 claims description 3
- 229920005996 polystyrene-poly(ethylene-butylene)-polystyrene Polymers 0.000 claims description 3
- 229920000728 polyester Polymers 0.000 claims description 2
- 229920002635 polyurethane Polymers 0.000 claims description 2
- 239000004814 polyurethane Substances 0.000 claims description 2
- 239000004800 polyvinyl chloride Substances 0.000 claims description 2
- 229920000915 polyvinyl chloride Polymers 0.000 claims description 2
- 229920002319 Poly(methyl acrylate) Polymers 0.000 claims 1
- 125000002573 ethenylidene group Chemical group [*]=C=C([H])[H] 0.000 claims 1
- 125000005397 methacrylic acid ester group Chemical group 0.000 claims 1
- 239000010408 film Substances 0.000 abstract description 19
- 239000007788 liquid Substances 0.000 abstract description 13
- 239000010409 thin film Substances 0.000 abstract description 11
- 239000000806 elastomer Substances 0.000 abstract description 7
- 239000011248 coating agent Substances 0.000 abstract description 6
- 238000000576 coating method Methods 0.000 abstract description 6
- 238000001746 injection moulding Methods 0.000 abstract description 5
- 239000000203 mixture Substances 0.000 abstract description 4
- 229920001187 thermosetting polymer Polymers 0.000 abstract 6
- 229920000131 polyvinylidene Polymers 0.000 abstract 2
- 230000001050 lubricating effect Effects 0.000 description 13
- ZWEHNKRNPOVVGH-UHFFFAOYSA-N 2-Butanone Chemical compound CCC(C)=O ZWEHNKRNPOVVGH-UHFFFAOYSA-N 0.000 description 12
- ZMXDDKWLCZADIW-UHFFFAOYSA-N N,N-Dimethylformamide Chemical compound CN(C)C=O ZMXDDKWLCZADIW-UHFFFAOYSA-N 0.000 description 9
- CSCPPACGZOOCGX-UHFFFAOYSA-N Acetone Chemical compound CC(C)=O CSCPPACGZOOCGX-UHFFFAOYSA-N 0.000 description 6
- 241000282472 Canis lupus familiaris Species 0.000 description 6
- 230000000052 comparative effect Effects 0.000 description 5
- 230000006835 compression Effects 0.000 description 5
- 238000007906 compression Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 5
- BQCIDUSAKPWEOX-UHFFFAOYSA-N 1,1-Difluoroethene Chemical compound FC(F)=C BQCIDUSAKPWEOX-UHFFFAOYSA-N 0.000 description 4
- IAZDPXIOMUYVGZ-UHFFFAOYSA-N Dimethylsulphoxide Chemical compound CS(C)=O IAZDPXIOMUYVGZ-UHFFFAOYSA-N 0.000 description 4
- 239000004743 Polypropylene Substances 0.000 description 4
- 238000010253 intravenous injection Methods 0.000 description 4
- 239000010687 lubricating oil Substances 0.000 description 4
- 229920001155 polypropylene Polymers 0.000 description 4
- 239000000243 solution Substances 0.000 description 4
- 239000002904 solvent Substances 0.000 description 4
- XEKOWRVHYACXOJ-UHFFFAOYSA-N Ethyl acetate Chemical compound CCOC(C)=O XEKOWRVHYACXOJ-UHFFFAOYSA-N 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 238000007598 dipping method Methods 0.000 description 3
- 238000001035 drying Methods 0.000 description 3
- 238000000465 moulding Methods 0.000 description 3
- 229920003002 synthetic resin Polymers 0.000 description 3
- 239000000057 synthetic resin Substances 0.000 description 3
- BAPJBEWLBFYGME-UHFFFAOYSA-N Methyl acrylate Chemical compound COC(=O)C=C BAPJBEWLBFYGME-UHFFFAOYSA-N 0.000 description 2
- NTIZESTWPVYFNL-UHFFFAOYSA-N Methyl isobutyl ketone Chemical compound CC(C)CC(C)=O NTIZESTWPVYFNL-UHFFFAOYSA-N 0.000 description 2
- UIHCLUNTQKBZGK-UHFFFAOYSA-N Methyl isobutyl ketone Natural products CCC(C)C(C)=O UIHCLUNTQKBZGK-UHFFFAOYSA-N 0.000 description 2
- FXHOOIRPVKKKFG-UHFFFAOYSA-N N,N-Dimethylacetamide Chemical compound CN(C)C(C)=O FXHOOIRPVKKKFG-UHFFFAOYSA-N 0.000 description 2
- 239000003963 antioxidant agent Substances 0.000 description 2
- 230000003078 antioxidant effect Effects 0.000 description 2
- 238000004898 kneading Methods 0.000 description 2
- 239000012046 mixed solvent Substances 0.000 description 2
- 229920002545 silicone oil Polymers 0.000 description 2
- 125000000391 vinyl group Chemical group [H]C([*])=C([H])[H] 0.000 description 2
- 229920002554 vinyl polymer Polymers 0.000 description 2
- RLRINNKRRPQIGW-UHFFFAOYSA-N 1-ethenyl-2-[4-(2-ethenylphenyl)butyl]benzene Chemical compound C=CC1=CC=CC=C1CCCCC1=CC=CC=C1C=C RLRINNKRRPQIGW-UHFFFAOYSA-N 0.000 description 1
- DKPFZGUDAPQIHT-UHFFFAOYSA-N Butyl acetate Natural products CCCCOC(C)=O DKPFZGUDAPQIHT-UHFFFAOYSA-N 0.000 description 1
- XDTMQSROBMDMFD-UHFFFAOYSA-N Cyclohexane Chemical compound C1CCCCC1 XDTMQSROBMDMFD-UHFFFAOYSA-N 0.000 description 1
- 241000282412 Homo Species 0.000 description 1
- 229920006370 Kynar Polymers 0.000 description 1
- 239000005062 Polybutadiene Substances 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 239000002253 acid Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 239000004840 adhesive resin Substances 0.000 description 1
- 229920006223 adhesive resin Polymers 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 229910017052 cobalt Inorganic materials 0.000 description 1
- 239000010941 cobalt Substances 0.000 description 1
- GUTLYIVDDKVIGB-UHFFFAOYSA-N cobalt atom Chemical compound [Co] GUTLYIVDDKVIGB-UHFFFAOYSA-N 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 238000003618 dip coating Methods 0.000 description 1
- BXOUVIIITJXIKB-UHFFFAOYSA-N ethene;styrene Chemical group C=C.C=CC1=CC=CC=C1 BXOUVIIITJXIKB-UHFFFAOYSA-N 0.000 description 1
- FUZZWVXGSFPDMH-UHFFFAOYSA-N hexanoic acid Chemical compound CCCCCC(O)=O FUZZWVXGSFPDMH-UHFFFAOYSA-N 0.000 description 1
- 229920005669 high impact polystyrene Polymers 0.000 description 1
- 239000004797 high-impact polystyrene Substances 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 238000005461 lubrication Methods 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 238000002156 mixing Methods 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 239000002504 physiological saline solution Substances 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 229920000306 polymethylpentene Polymers 0.000 description 1
- 229920002620 polyvinyl fluoride Polymers 0.000 description 1
- QQONPFPTGQHPMA-UHFFFAOYSA-N propylene Natural products CC=C QQONPFPTGQHPMA-UHFFFAOYSA-N 0.000 description 1
- 125000004805 propylene group Chemical group [H]C([H])([H])C([H])([*:1])C([H])([H])[*:2] 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 239000011780 sodium chloride Substances 0.000 description 1
- 230000001954 sterilising effect Effects 0.000 description 1
- 238000004659 sterilization and disinfection Methods 0.000 description 1
- 238000003860 storage Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 229920003051 synthetic elastomer Polymers 0.000 description 1
- 239000005061 synthetic rubber Substances 0.000 description 1
- 229920006027 ternary co-polymer Polymers 0.000 description 1
- BFKJFAAPBSQJPD-UHFFFAOYSA-N tetrafluoroethene Chemical group FC(F)=C(F)F BFKJFAAPBSQJPD-UHFFFAOYSA-N 0.000 description 1
- 238000005303 weighing Methods 0.000 description 1
Landscapes
- Infusion, Injection, And Reservoir Apparatuses (AREA)
Abstract
Description
【発明の詳細な説明】
［産業上の利用分野］
本発明は、注射器等の医療用器具およびその製法に関す
る。DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to medical instruments such as syringes and methods for manufacturing the same.
［従来の技術］
医療用器具として、筒状体と、該筒状体内壁面に密着し
て摺動する摺動部材とを具備してなるものがある。この
医療用器具にあっては、例えばディスポーザブル注射器
におけるように、シリンジ（筒状体）とガスケー、ト（
摺動部材）との％密性を維持するため、両者を隙間なく
強く密着する必要がある。このため、シリンジとガスケ
ットの接触部における摩擦抵抗はかなり大きくなり、そ
のままではガスケットが全く摺動できない、のみならず
、ガスケットをシリンジに挿入して両者を組立てること
すらきわめて困難となる。[Prior Art] Some medical instruments include a cylindrical body and a sliding member that slides in close contact with the inner wall surface of the cylindrical body. This medical device, for example in a disposable syringe, includes a syringe (cylindrical body), a gasket, and a tube (tube).
In order to maintain the percent density with the sliding member), it is necessary to tightly adhere the two without any gaps. For this reason, the frictional resistance at the contact portion between the syringe and the gasket becomes quite large, and if left as is, not only will the gasket not be able to slide at all, but it will also be extremely difficult to assemble the two by inserting the gasket into the syringe.
そこで従来の注射器にあっては、シリンジとガスケット
の接触部にシリコーンオイル等の潤滑油を用いることと
している。Therefore, in conventional syringes, a lubricating oil such as silicone oil is used in the contact area between the syringe and the gasket.
し発明が解決しようとする課題］
しかしながら、上述の如くの医療用器具において、筒状
体と摺動部材との接触部に潤滑油を設ける場合には、こ
の潤滑油が、筒状体の液体収容空間に装填された薬液等
の内容液中に溶は込むことがある。この時、上記内容液
を人間に投与することを考えると、この内容液中に潤滑
油が溶は込む如きは、安全性をより完全に確保する見地
からみて必ずしも好ましくない。[Problems to be Solved by the Invention] However, when lubricating oil is provided at the contact portion between the cylindrical body and the sliding member in the medical instrument as described above, this lubricating oil is It may dissolve into the contents of the liquid, such as a chemical liquid, loaded into the storage space. At this time, considering that the above-mentioned liquid content is to be administered to humans, it is not necessarily preferable for lubricating oil to dissolve into the liquid content from the standpoint of ensuring more complete safety.
そこで、本出願人は、すでに特願昭Ｈ−１２８８４１号
により、摺動部材本体の表面のうち、筒状体内壁面と接
触する位置に、ポリフッ化ビニリデン系樹脂層を被覆す
ることを提案している。このポリフッ化ビニリデン系樹
脂層は潤滑性被膜を構成し、かつ筒状体に装填された内
容液中に溶は込むことがないため、安全性をより安全に
確保できる。Therefore, the present applicant has already proposed, in Japanese Patent Application No. 128841, to coat the surface of the sliding member main body with a polyvinylidene fluoride resin layer at the position that contacts the inner wall surface of the cylindrical body. There is. This polyvinylidene fluoride resin layer constitutes a lubricating coating and does not dissolve into the liquid contained in the cylindrical body, so safety can be more safely ensured.
ところが、本発明者の研究によると、上記ポリフッ化ビ
ニリデン系樹脂層を摺動部材本体の表面に被覆する方法
においては、ポリフッ化ビニリデン系樹脂層と摺動部材
本体との接着性が完全といえず、摺動部材を筒状体に対
し何度も繰り返し摺動させると、ポリフッ化ビニリデン
系樹脂層の一部が剥離する。すなわち、ポリフッ化ビニ
リデン系樹脂層を摺動部材本体により完全に接着するこ
との必要を認めた。However, according to the research of the present inventor, in the method of coating the surface of the sliding member body with the polyvinylidene fluoride resin layer, the adhesiveness between the polyvinylidene fluoride resin layer and the sliding member body can be said to be perfect. First, when the sliding member is repeatedly slid against the cylindrical body, a portion of the polyvinylidene fluoride resin layer peels off. That is, it was recognized that it was necessary to completely adhere the polyvinylidene fluoride resin layer to the sliding member body.
大発明は、筒状体と摺動部材とからなる医療用器具にお
いて、摺動部材の表面に潤滑性被膜を形成するに際し、
この潤滑性被膜が筒状体に装填した内容液中に溶は込ん
だり、剥離することがなく、より完全な安全性を確保で
きる医療用器具を提供することを目的とする。The great invention is a medical instrument consisting of a cylindrical body and a sliding member, in which a lubricating film is formed on the surface of the sliding member.
It is an object of the present invention to provide a medical instrument in which this lubricating coating does not dissolve into the liquid contained in the cylindrical body or peel off, thereby ensuring more complete safety.
［課題を解決するための手段１
本発明の医療用器具は、筒状体と、該筒状体内壁面に密
着して摺動する摺動部材とを具備してなる医療用器具で
あって、前記摺動部材は、基材に、アクリル酸エステル
、メタクリル酸エステル、またはアクリロニトリル、の
各重合体もしくはそれらのうち少なくとも２種からなる
共重合体のうち、少なくとも一種類を含む熱可塑性樹脂
を配合してなる熱可塑性エラストマーからなる摺動部材
本体と、該摺動部材本体の表面のうち、少なくとも前記
筒状体内壁面と接触する位置に被覆されたポリフッ化ビ
ニリデン系樹脂層と、からなるようにしたものである。[Means for Solving the Problems 1] The medical instrument of the present invention is a medical instrument comprising a cylindrical body and a sliding member that slides in close contact with the wall surface of the cylindrical body, The sliding member has a base material blended with a thermoplastic resin containing at least one of acrylic ester, methacrylic ester, or acrylonitrile, or a copolymer consisting of at least two of them. a sliding member body made of a thermoplastic elastomer; and a polyvinylidene fluoride resin layer coated on at least a portion of the surface of the sliding member body that contacts the wall surface of the cylindrical body. This is what I did.
未発明の医療用器具の製法は、筒状体と、該筒状体内壁
面に密着して摺動する摺動部材とを具備してなる医療用
器具の製法であって、前記摺動部材の本体を、基材に、
アクリル酸エステル、メタクリル酸エステル、またはア
クリロニトリル、の各重合体もしくはそれらのうち少な
くとも２種からなる共重合体のうち、少なくとも一種類
を含む熱可塑性樹脂を配合してなる熱可塑性エラストマ
ーにて構成し、該摺動部材本体の表面のうち少なくとも
前記筒状体内壁面と接触する位置にポリフッ化ビニリデ
ン系樹脂層を被覆するようにしたものである。An uninvented method for manufacturing a medical device is a method for manufacturing a medical device comprising a cylindrical body and a sliding member that slides in close contact with the wall surface of the cylindrical body, the method comprising: The main body as a base material,
Consisting of a thermoplastic elastomer blended with a thermoplastic resin containing at least one of acrylic ester, methacrylic ester, or acrylonitrile, or a copolymer consisting of at least two of them. A polyvinylidene fluoride resin layer is coated on at least the surface of the sliding member main body at a position that contacts the inner wall surface of the cylindrical body.
［作用コ
本発明の医療用器具およびその製法によれば、以下の作
用効果がある。[Function] The medical device of the present invention and its manufacturing method have the following effects.
■摺動部材の表面がポリフッ化ビニリデン系樹脂からな
る潤滑性被膜で覆われるから、筒状体に対する摺動部材
の摺動性が良好となる。(2) Since the surface of the sliding member is covered with a lubricating film made of polyvinylidene fluoride resin, the slidability of the sliding member with respect to the cylindrical body is improved.
■摺動部材本体がポリフッ化ビニリデン系樹脂層と接着
性を更に示す樹脂をブレンドされて構成されたから、摺
動部材の繰り返し摺動時に、ポリフッ化ビニリデン系樹
脂層が筒状体に装填した内容液中に溶は込むことはもち
ろん剥離することもない。よって、内容液を人体に投与
するに際しより完全な安全性を確保できる。■The main body of the sliding member is composed of a blend of a polyvinylidene fluoride resin layer and a resin that exhibits adhesive properties, so when the sliding member repeatedly slides, the polyvinylidene fluoride resin layer is loaded into the cylindrical body. It does not dissolve into the liquid and does not peel off. Therefore, more complete safety can be ensured when administering the content liquid to the human body.
■なお、筒状体の内径と摺動部材の外径の径差が大きく
なっても（もちろん筒状体の内径の方が小さい）、ポリ
フッ化ビニリデン系樹脂層の剥離がないから、」二重各
径成形時における寸法精度を緩和できる。■Even if the difference between the inner diameter of the cylindrical body and the outer diameter of the sliding member becomes large (of course, the inner diameter of the cylindrical body is smaller), the polyvinylidene fluoride resin layer will not peel off. Dimensional accuracy during molding of various diameters can be relaxed.
［実施例］
第１図は本発明が適用された注射器を示す模式図、第２
図はガスケットを示す要部断面図、第３図はガスケット
の他の例を示す要部断面図である。[Example] Figure 1 is a schematic diagram showing a syringe to which the present invention is applied, Figure 2 is a schematic diagram showing a syringe to which the present invention is applied;
The figure is a sectional view of a main part showing a gasket, and FIG. 3 is a sectional view of a main part showing another example of a gasket.
第１図において、１は合成樹脂製のシリンジである。シ
リンジ１の先端にはノズル２が形成されており、使用時
には該ノズル２に注射針が嵌着される。シリンジ１の後
端は開放されており、該開放端の周縁部にはフランジ３
が形成されている。In FIG. 1, 1 is a syringe made of synthetic resin. A nozzle 2 is formed at the tip of the syringe 1, and an injection needle is fitted into the nozzle 2 during use. The rear end of the syringe 1 is open, and a flange 3 is attached to the peripheral edge of the open end.
is formed.
シリンジｌの後端開放部からは、合成樹脂製の押子４が
内部に挿入されており、該押子４の先端にはガスケット
５が設けられている。ガスケット５はシリンジ１の内表
面に密着し、気密性が保たれている。また、ガスケット
５の表面には、後述する如くポリフッ化ビニリデン系樹
脂からなる潤滑性薄膜が被覆されている。この潤滑性薄
膜によって、シリンジ１の内表面上でのガスケット５の
良好な滑り性が付与され、押子４の摺動が可能になって
いる。個々の部分の詳細は次の通りである。A synthetic resin pusher 4 is inserted into the open rear end of the syringe l, and a gasket 5 is provided at the tip of the pusher 4. The gasket 5 is in close contact with the inner surface of the syringe 1 to maintain airtightness. Further, the surface of the gasket 5 is coated with a lubricating thin film made of polyvinylidene fluoride resin, as will be described later. This lubricating thin film provides good sliding properties of the gasket 5 on the inner surface of the syringe 1, allowing the pusher 4 to slide. Details of the individual parts are as follows.
シリンジ１及び押子４の材質としては透明性成形性に優
れ、且つ耐衝撃強度の大きいものが良い。このような望
ましい合成樹脂としては、例えばポリプロピレン、ポリ
（４−メチルペンテンｌ）、耐衝撃性ポリスチレン、ポ
リカーボネート等が挙げられる。更に好ましいものとし
ては、ポリプロピレンまたはポリ（４−メチルペンテン
１）が挙げられる。The syringe 1 and the pusher 4 are preferably made of materials that are transparent, have excellent moldability, and have high impact resistance. Examples of such desirable synthetic resins include polypropylene, poly(4-methylpentene), high-impact polystyrene, and polycarbonate. More preferred are polypropylene or poly(4-methylpentene 1).
第２図は、ガスケント５を一部断面で拡大して示してい
る。同図において、６はガスケット本体である。図示の
ように、ガスケット本体は茸成の外形を有し、押子４の
先端を収容して結合するための凹孔を有している。そし
て、その表面にはポリフッ化ビニリデン系樹脂からなる
■滑性薄膜７が被着されている。なお、ポリフッ化ビニ
リデン系樹脂からなる１１！ｌ滑性薄膜７は必ずしもガ
スヶ・ント本体６の全表面に施す必要はない。例えば第
３図に示したように、シリンジ１の内表面と接触する部
分にのみ被覆してあれば充分である。ただし、薬液等を
人体に投与する場合の安全性を考えると、内容液と接す
る部分全てにポリフッ化ビニリデン系樹脂皮膜を設けた
方が良い。FIG. 2 shows a partially enlarged cross-sectional view of the Gaskent 5. In the figure, 6 is a gasket body. As shown in the figure, the gasket body has a fungiform outer shape and has a recessed hole for accommodating and coupling the tip of the pusher 4. A slippery thin film 7 made of polyvinylidene fluoride resin is adhered to its surface. Note that 11! is made of polyvinylidene fluoride resin. l The slippery thin film 7 does not necessarily need to be applied to the entire surface of the gas container body 6. For example, as shown in FIG. 3, it is sufficient to coat only the portion that contacts the inner surface of the syringe 1. However, considering the safety when administering medicinal solutions to the human body, it is better to provide a polyvinylidene fluoride resin coating on all parts that come into contact with the liquid contents.
ガスケット本体６の基材としては、熱可塑性エラストマ
ーを射出成形して製造したものを用いることができる。As the base material of the gasket body 6, one manufactured by injection molding a thermoplastic elastomer can be used.
この熱可塑性エラストマーとしては、スチレン−ブタジ
エン−スチレンブロック共重合体（ＳＢＳ）Ａ、スチレ
ン−エチレン・ブチレン−スチレンブロック共ｆｆｉ合
体（ＳＥＢＳ）系、エチレン−プロピレン共重合体（Ｅ
Ｐ）系ポリ塩化ビニル系、ポリエステル系、ボリウ１
／タン系のうちの少なくとも１つを用いることができる
。好ましくは、スチレン−ブタジェン−メチ１／ンブロ
ツク共重合体（Ｓ Ｂ Ｓ）系、スチレン−エチレン・
ブチレン−スチレンブロー、り共重合体（ＳＥＢＳ）系
、エチレン−プロピレン共重合体（Ｅ Ｐ）系、ポリ増
化ビニル系のうちの少なくとも１つを用いる。Examples of this thermoplastic elastomer include styrene-butadiene-styrene block copolymer (SBS) A, styrene-ethylene/butylene-styrene block coffi polymer (SEBS), and ethylene-propylene copolymer (E
P) type polyvinyl chloride type, polyester type, polyurethane 1
/tan type can be used. Preferably, styrene-butadiene-methylene block copolymer (S B S) system, styrene-ethylene.
At least one of a butylene-styrene blown copolymer (SEBS) system, an ethylene-propylene copolymer (EP) system, and a polyenhanced vinyl system is used.
ガスケット本体６の圧縮永久歪み（ＪＩＳ Ｋｅ３０１
）は、７０°Ｃ１２２時間の条件で８０％以下とする。Compression set of gasket body 6 (JIS Ke301
) shall be 80% or less at 70°C for 122 hours.
好ましくは５０％以下であることが望ましい。圧縮永久
歪みが８０％以」二であると、経時的にガスケットの径
が外筒内径と等しくなる様に変形が進み、ガスケットを
摺動させた時にピーク部分が外筒から離れて気密性が保
てなくなるからである。Preferably it is 50% or less. If the compression set is 80% or more, the deformation progresses over time so that the diameter of the gasket becomes equal to the inner diameter of the outer cylinder, and when the gasket is slid, the peak part separates from the outer cylinder, resulting in poor airtightness. This is because it will not be possible to maintain it.
また、ガスケット本体６に用いる材料のゴム硬度（ＪＩ
Ｓ Ｋｆ１３０１ ）は、ＪＩＳ−Ａで３５度〜８５度
が望ましい。８５度より大きいとシリンジの組立てが困
難となり、３５度より小さいと摺動時に変形して摺動さ
せにくくなるからである。更に望ましいゴム硬度は４０
度〜７０度である。ガスケラ１本体６の材料に用いる熱
可塑性エラストマ〜としては、上記の圧縮永久歪み及び
ゴム硬度を持つＳＢＳ系、５ＥＢＳ系、ＥＰ系、ポリ増
化ビこル系のコポリマーのうちの少なくとも一種類であ
ることが望ましい。In addition, the rubber hardness (JI
SKf1301) is preferably 35 degrees to 85 degrees according to JIS-A. This is because if the angle is larger than 85 degrees, it will be difficult to assemble the syringe, and if it is smaller than 35 degrees, it will deform during sliding and become difficult to slide. More desirable rubber hardness is 40
It is between 70 degrees and 70 degrees. The thermoplastic elastomer used for the material of the main body 6 of the Gaskera 1 is at least one of the SBS-based, 5EBS-based, EP-based, and polyenhanced vinyl-based copolymers having the compression set and rubber hardness mentioned above. It is desirable that there be.
ポリフッ化ビニリデン系樹脂からなる潤滑性薄膜７は、
ポリフッ化ビニリデン系樹脂を溶剤に溶解させたものに
ガスケット本体６をディッピングし、さらに溶剤を乾燥
除去させることにて形成される。この時、ポリフッ化ビ
こリデン系樹脂からなる潤滑性薄膜７の膜厚が厚すぎる
と、被覆された部分の硬度が高くなり、シリンジ内の気
密が保ちにくくなる。従って潤滑性薄膜の膜厚は １０
０ｇｍ以下、好ましくは３０ｇｍ以下、更に好ましくは
１０ルｍ以下とする。なお、この膜厚はディッピング溶
液組成を変えることにより容易に制御できる。The lubricating thin film 7 made of polyvinylidene fluoride resin is
It is formed by dipping the gasket body 6 in a solution of polyvinylidene fluoride resin in a solvent, and then drying and removing the solvent. At this time, if the lubricating thin film 7 made of polyvinylidene fluoride resin is too thick, the hardness of the covered portion will increase, making it difficult to maintain airtightness within the syringe. Therefore, the thickness of the lubricating thin film is 10
0 gm or less, preferably 30 gm or less, more preferably 10 gm or less. Note that this film thickness can be easily controlled by changing the composition of the dipping solution.
しかして、本発明にあっては、ポリフッ化ビニリデン系
樹脂皮膜とガスケット本体表面との接着を完全化するた
めに、ガスケット本体の基材を構成する熱可塑性エラス
トマーに、アクリル酸エステル、メタクリル酸エステル
、アクリロニトリル、の重合体もしくは共重合体のうち
少なくとも一種類を含む熱可塑性樹脂を加える。Therefore, in the present invention, in order to perfect the adhesion between the polyvinylidene fluoride resin film and the surface of the gasket body, acrylic ester and methacrylic ester are added to the thermoplastic elastomer that constitutes the base material of the gasket body. , acrylonitrile, or a thermoplastic resin containing at least one type of polymer or copolymer.
ここで、アクリル酸エステル、メタクリル酸エステル、
アクリロニトリルの重合体もしくは共重合体のうち少な
くとも一種類を含む熱可塑性樹脂とは、エチレン−アク
リル酸エチル共重合体（ＥＥＡ）、エチレン−アクリル
酸共重合体（ＦＡＡ）、ポリアクリル酸エチル、ポリア
クリル酸メチル、ポリメタクリル酸メチル（ＰＭＭＡ）
、ポリアクリロニトリル（ＰＡＮ）、未加硫のアクリロ
ニ）・リルブタジエンゴム（未加硫ＮＢＲ） 等であっ
てもよい。更に好ましくは、エチレン−アクリル酸エチ
ル共重合体（ＥＥＡ）、未加硫のアクリロニトリルブタ
ジェンゴム（未加硫ＮＢＲ）−ｃ■？
ある。Here, acrylic ester, methacrylic ester,
Thermoplastic resins containing at least one type of acrylonitrile polymer or copolymer include ethylene-ethyl acrylate copolymer (EEA), ethylene-acrylic acid copolymer (FAA), polyethyl acrylate, and polyethyl acrylate. Methyl acrylate, polymethyl methacrylate (PMMA)
, polyacrylonitrile (PAN), unvulcanized acrylonitrile), lylbutadiene rubber (unvulcanized NBR), and the like. More preferably, ethylene-ethyl acrylate copolymer (EEA), unvulcanized acrylonitrile butadiene rubber (unvulcanized NBR)-c? be.
また、アクリル酸エステル、メタクリル酸エステル、ア
クリロニＩ・リルの重合体もしくは共重合体のうち少な
くとも一種類を含む熱可塑性樹脂の配合量は、ガスケッ
ト本体の基材を構成する熱可塑性エラストマー １００
重量部に対して １〜８０重量、部が適当である。８０
重量部よりも多いとガスケット本体の基材に求められる
物性、すなわち、ゴム硬度、圧縮永久歪、メルトフロー
インデックス等あるいは成形後の表面状態が適さないも
のになってしまう。また、１重量部よりも小さいとその
効果が発揮されない。更に好ましくは、 ５〜５０重量
部である。In addition, the blending amount of the thermoplastic resin containing at least one of acrylic ester, methacrylic ester, and acryloni I/Ryl polymer or copolymer is 100% of the thermoplastic elastomer constituting the base material of the gasket body.
1 to 80 parts by weight is suitable. 80
If the amount exceeds the weight part, the physical properties required for the base material of the gasket body, such as rubber hardness, compression set, melt flow index, etc., or the surface condition after molding will become unsuitable. Moreover, if it is less than 1 part by weight, the effect will not be exhibited. More preferably, it is 5 to 50 parts by weight.
なお、ポリフッ化ビニリデン系樹脂とはホモのポリフッ
化ビニリデン、フッ化ビニリデンＱ六フッ化プロピレン
共重合体、フッ化ビニリデン・四フフ化エチレン共重合
体、フッ化ビニリデン・四フッ化エチレン・六フッ化プ
ロピレン３元共重合体であり、それぞれｌ’ｅｎｎｗａ
Ｉ を社のＫｙｎａｒ９３０１Ｆ、＃ ２８０１．
＃ ７２０１．＃ ９３０１として入手することができ
、それぞれ溶剤に対する溶解度、ディッピングコート後
の皮膜の硬度、接着性に若干の違いがみられ、シリンジ
のサイズ及びガスケット本体の材質、シリンジの内径と
ガスケット本体の外径の差等により使いわけることがで
きる。また、該ポリフッ化ビニリデン系樹脂を溶かす溶
剤にはジメチルホルムアミド（ＤＭＦ）、ジメチルアセ
トアミド（ＤＭＡＣ）、ジメチルスルホキシド（ＤＭＳ
Ｏ）、アセトン、メチルエチルケト７（ＭＥＫ）、メチ
ルイソブチルケトン（ＭＩＢＫ）、シクロヘキサン、酢
酸エチル、酢酸ブチルのうちの少なくとも一種類を用い
ることができる。また、２種類以」二の混合溶媒を用い
てもよい。更に好ましくは、ジメチルホルムアミド（Ｄ
ＭＦ） 、アセトン、メチルエチルケトン（ＭＥＫ）で
ある。Polyvinylidene fluoride resins include homologous polyvinylidene fluoride, vinylidene fluoride Q hexafluoropropylene copolymer, vinylidene fluoride/tetrafluoroethylene copolymer, vinylidene fluoride/tetrafluoroethylene/hexafluoride is a propylene ternary copolymer, each with l'ennwa
Kynar9301F, #2801.
#7201. #9301, and there are slight differences in solubility in solvents, hardness of the film after dipping coating, and adhesion, and differences in syringe size, gasket body material, syringe inner diameter and gasket body outer diameter. It can be used depending on the difference etc. In addition, solvents for dissolving the polyvinylidene fluoride resin include dimethylformamide (DMF), dimethylacetamide (DMAC), and dimethyl sulfoxide (DMS).
At least one of O), acetone, methyl ethyl ketone (MEK), methyl isobutyl ketone (MIBK), cyclohexane, ethyl acetate, and butyl acetate can be used. Furthermore, a mixed solvent of two or more types may be used. More preferably, dimethylformamide (D
MF), acetone, and methyl ethyl ketone (MEK).
次に、上記実施例の作用について説明する。Next, the operation of the above embodiment will be explained.
上記実施例によれば、以下の作用効果がある。According to the above embodiment, there are the following effects.
■ガスケット本体の表面がポリフッ化ビニル系樹脂から
なる潤滑性薄膜７で覆われるから、シリンジ１に対する
ガスケラｌ−５の摺動性が良好となる。(2) Since the surface of the gasket body is covered with the lubricating thin film 7 made of polyvinyl fluoride resin, the sliding properties of the Gaskera 1-5 with respect to the syringe 1 are improved.
■ガスケット本体６がポリフッ化ビニリデン系樹脂層と
接着性を示す樹脂をブレンドされて構成されたから、ガ
スケット５の繰り返し摺動時にポリフッ化ビニリデン系
樹脂層がシリンジ］に装填された内容液中に溶は込むこ
とはもちろん剥離することもない。よって、内容液を人
体に投与するに際し、より完全な安全性を確保できる。■Since the gasket body 6 is composed of a blend of a polyvinylidene fluoride resin layer and an adhesive resin, when the gasket 5 is repeatedly slid, the polyvinylidene fluoride resin layer dissolves into the liquid contained in the syringe. Not only will it not fit in, but it will not peel off. Therefore, more complete safety can be ensured when administering the content liquid to the human body.
■なお、シリンジ１の内径とガスケット５の外径の径差
が大きくなっても（もぢろんシリンジ１の内径の方が小
さい）、ポリフッ化ビニリデン系樹脂層の剥離がないか
ら、」−記各径成形時における寸法精度を緩和できる。■Even if the difference between the inner diameter of the syringe 1 and the outer diameter of the gasket 5 becomes large (the inner diameter of the syringe 1 is smaller), the polyvinylidene fluoride resin layer will not peel off. Dimensional accuracy during molding of each diameter can be relaxed.
なお、本発明は、注射器にかぎらず、血液ガス測定用採
捕キット等の筒状体ど摺動部材とを具備してなる医療用
器具及びその製法に広く適用できる。The present invention is not limited to syringes, but can be widely applied to medical instruments including a cylindrical body and a sliding member, such as collection kits for blood gas measurement, and methods for manufacturing the same.
以下本発明の具体的な実施例および比較例を挙げ、本発
明の効果を具体的に説明する。EXAMPLES The effects of the present invention will be specifically explained below by giving specific examples and comparative examples of the present invention.
実施例 １
スチレン−エチレン・ブチレン−スチレンブロック共重
合体（ＳＥＢＳ）系熱可塑性エラストマー、アロン化成
（株）酸エラストマーＡＲ−８０４，１００重量部に対
し、エチレン−アクリル酸エチル共重合体（ＥＥＡ）、
８本ユニカー（株）製ＨＵＧ６５７０を１０重量部トラ
イブレンドし、射出成形機でガスケット形状に成形して
ピーク径１３．２ｍｍの５ｍ文シリンジ用ガスケットを
得た。そのガスケット表面に、Ｐｅｎｗａｌｔ社のポリ
フッ化ビニリデンＫｙｎａｒ ＃ ３０１Ｆをアセトン
：ジメチルポルムアミド＝４：１．（重量比）ｉ合溶媒
ニ１５ｗｔ％溶カシタ溶液でディッピングコートし、室
温で半日乾燥させたのち、８０°０． １時間乾燥させ
て、ポリフッ化ビニリデン皮膜を具備したガスケットを
得た。これに三菱油化（株）製ポリプロピレンＮＧ−３
１］を射出成形して得た押子を設け、更に同じポリプロ
ピレンを射出成形して得た内径１３．０ｍｍの５ｍ文シ
リンジ用外筒に、潤滑用シリコーンオイルなしに組立て
た。Example 1 Styrene-ethylene/butylene-styrene block copolymer (SEBS) thermoplastic elastomer, Aron Kasei Co., Ltd. Acid Elastomer AR-804, 100 parts by weight, ethylene-ethyl acrylate copolymer (EEA) ,
10 parts by weight of HUG6570 manufactured by Unicar Co., Ltd. was triblended and molded into a gasket shape using an injection molding machine to obtain a gasket for a 5 m syringe with a peak diameter of 13.2 mm. On the surface of the gasket, polyvinylidene fluoride Kynar #301F from Penwalt was applied in an acetone:dimethylpolamide ratio of 4:1. (Weight ratio) Dip coating with a 15 wt% Kasita solution in the mixed solvent and drying at room temperature for half a day, followed by 80°0. After drying for 1 hour, a gasket having a polyvinylidene fluoride film was obtained. Polypropylene NG-3 manufactured by Mitsubishi Yuka Co., Ltd.
A pusher obtained by injection molding 1] was provided, and it was assembled into an outer cylinder for a 5 m syringe with an inner diameter of 13.0 mm obtained by injection molding the same polypropylene without silicone oil for lubrication.
また、上記ポリフッ化ビニリデン皮膜のあるガスケット
を切断して、走査型電子顕微鏡（８本電子（株）製ＪＳ
Ｍ−８４０）で皮膜の膜厚を測定したところ３０〜３５
ｇｍであった。この組立てたディスポーサブル注射器を
原子量８０のコバルトを線源として２、ＯＭｒａｄのγ
線で滅菌した後、２２Ｇの針を装着して生理食塩水（テ
ルモ（株）テルモ生食）を吸弓し、犬（雑種成犬、体重
１０ｋｇ）に５ｍ文静脈注射したが、通常の使用が可能
であり、ポリフッ化ビニリデン皮膜の剥離も認められず
問題なかった。In addition, the gasket with the polyvinylidene fluoride film was cut, and a scanning electron microscope (8 parts, manufactured by JS Denshi Co., Ltd.)
When the film thickness of the film was measured using M-840), it was 30 to 35.
It was gm. This assembled disposable syringe was used as a radiation source with cobalt having an atomic weight of 80, and γ of OMrad.
After sterilization with a wire, a 22G needle was attached and physiological saline (Terumo saline, manufactured by Terumo Corporation) was injected intravenously into a dog (an adult mongrel dog, weighing 10 kg). This was possible, and no peeling of the polyvinylidene fluoride film was observed, so there was no problem.
更に１０回はどガスケットを外筒内で摺動させたがポリ
フッ化ビニリデン皮膜の剥離は認められなかった。Although the gasket was slid inside the outer cylinder 10 more times, no peeling of the polyvinylidene fluoride film was observed.
実施例 ２
エラストマー ＡＲ−８０４とＮＵＣ−Ｅｔ５７０テ射
出成形したガスケットのピーク径を１３．４ｍｍにした
以外は実施例１と同様にした結果、実施例１と同様に問
題なかった。更に１０回はどガスケットを外筒内で摺動
させたがポリフッ化ビニリデン皮膜の剥離は認められな
かった。Example 2 Elastomer AR-804 and NUC-Et570 The same procedure as Example 1 was performed except that the peak diameter of the injection-molded gasket was 13.4 mm. As a result, there were no problems as in Example 1. Although the gasket was slid inside the outer cylinder 10 more times, no peeling of the polyvinylidene fluoride film was observed.
実施例 ３
エチレン−プロピレン共重合体（Ｅ Ｐ）系熱可塑性エ
ラストマー、三井石油化学工業（株）製エラストマー＃
５５１０．１００重量部に対して粉体状アクリロニト
リルブタジェンゴム（未加硫ＮＢＲ）、日本合成ゴム（
株）製ＰＮ−２０ＨＡを４０重量部、酸化防止剤ＢＨＴ
、川口化学（株）製アンテージＢＨＴ０．５重量部を
１８０ ’Ｃ！に加熱した混練ロールで混練し、シート
ペレタイザーにてベレット化した後、射出成形機にてガ
スケット形状に成形し、ピーク径１３．２ｍｍの５＋ｍ
Ｑ用シリンジガスケットを得た。これを実施例１と同様
に用いたところ、特に問題はなかった。更に１０回程ガ
スケットを外筒内で摺動させたがポリフッ化ビニリデン
皮膜の剥離は認められなかった。Example 3 Ethylene-propylene copolymer (EP) thermoplastic elastomer, elastomer # manufactured by Mitsui Petrochemical Industries, Ltd.
5510. Powdered acrylonitrile butadiene rubber (unvulcanized NBR), Japan Synthetic Rubber (
40 parts by weight of PN-20HA manufactured by Co., Ltd., and antioxidant BHT.
, 0.5 parts by weight of Antage BHT manufactured by Kawaguchi Chemical Co., Ltd.
180'C! After kneading with a kneading roll heated to
A syringe gasket for Q was obtained. When this was used in the same manner as in Example 1, there were no particular problems. The gasket was further slid in the outer cylinder about 10 times, but no peeling of the polyvinylidene fluoride film was observed.
比較例 １
エチレン−アクリル酸エチル共重合体（ＥＥＡ）を配合
しない点以外は実施例１と同様にした結果、通常の犬へ
の静脈注射については問題なかったが、その後ガスケッ
トを外筒内で摺動させたところ５回目でガスヶ・ント表
面のポリフッ化ビニリデン皮膜の剥離が認められた。Comparative Example 1 The same procedure as Example 1 was carried out except that ethylene-ethyl acrylate copolymer (EEA) was not blended. As a result, there was no problem with intravenous injection to normal dogs, but after that, the gasket was inserted into the outer cylinder. When it was slid for the fifth time, peeling of the polyvinylidene fluoride film on the surface of the gas cap was observed.
比較例 ２
エチレン−アクリル酸エチル共重合体（ＥＥＡ）を配合
しない点以外は実施例２と同様にした結果、犬への静脈
注射には問題なかった。しかし、更にガスケットを外筒
内で摺動させると３回目にポリフッ化ビニリデン皮膜の
剥離が認められた。Comparative Example 2 The same procedure as Example 2 was carried out except that the ethylene-ethyl acrylate copolymer (EEA) was not blended. As a result, there was no problem in intravenous injection to dogs. However, when the gasket was further slid inside the outer cylinder, peeling of the polyvinylidene fluoride film was observed the third time.
比較例 ３
アクリロニトリルブタジェンゴム（来、１１０１ａ Ｎ
ＢＲ）と酸化防止剤ＢＨＴを配合しない点以外は実施
例３と同様にして犬への静脈注射を行なったところ特に
問題はなかった。しかし、更にガスケットを外筒内で摺
動させると５回目でガスケット表面のポリフッ化ビニリ
デン皮膜の剥離が認められた。Comparative Example 3 Acrylonitrile butadiene rubber (1101a N
Intravenous injection into dogs was carried out in the same manner as in Example 3, except that BR) and the antioxidant BHT were not mixed, and there were no particular problems. However, when the gasket was further slid inside the outer cylinder, peeling of the polyvinylidene fluoride film on the gasket surface was observed at the fifth time.
比較例 ４
粉体状アクリロニトリルブタジェンゴム（未加硫Ｎ’Ｂ
Ｒ）の配合量を８０重量％にした以外は実施例３と同様
にして犬への静脈注射を行なったところ、成形物表面が
荒れてしまったために滑らかに摺動させることができな
かった。また圧縮永久歪（ＪＩＳ ＫＩ３３０１．７０
℃、２２時間条件）が５２％であり、室温で３ケ月放置
しておくと、ガスケ−／ トピーク径が外筒径に等しく
なるように変形が進み、摺動時にリークが起きてしまっ
た。Comparative Example 4 Powdered acrylonitrile butadiene rubber (unvulcanized N'B
When intravenous injection was performed into a dog in the same manner as in Example 3 except that the amount of R) was 80% by weight, the surface of the molded product was rough and could not be slid smoothly. Also, compression set (JIS KI3301.70
℃, 22 hours condition) was 52%, and when left at room temperature for 3 months, deformation progressed so that the gasket/toe peak diameter became equal to the outer cylinder diameter, and leakage occurred during sliding.
［発明の効果］
以上のように本発明によれば、筒状体と摺動部材とから
なる医療用器具において、摺動部材の表面に潤滑性被膜
を形成するに際し、この潤滑性被膜が筒状体に装填した
内容液中に溶は込んだり、剥離することがなく、より完
全な安全性を確保できる。[Effects of the Invention] As described above, according to the present invention, when forming a lubricating film on the surface of the sliding member in a medical instrument consisting of a cylindrical body and a sliding member, the lubricating film is It does not dissolve into the liquid contained in the body or peel off, ensuring more complete safety.
第１図は本発明が適用された注射器を示す模式図、第２
図はガスケットを示す要部断面図、第３図はガスケット
の他の例を示す要部断面図である。
１・・・シリンジ（筒状体）
５・・・ガスケット（摺動部材）
６・・・ガスケット本体、
７・・・潤滑性薄膜。FIG. 1 is a schematic diagram showing a syringe to which the present invention is applied, and FIG.
The figure is a sectional view of a main part showing a gasket, and FIG. 3 is a sectional view of a main part showing another example of a gasket. 1... Syringe (cylindrical body) 5... Gasket (sliding member) 6... Gasket body, 7... Lubricating thin film.
Claims (6)
動部材とを具備してなる医療用器具であって、前記摺動
部材は、基材に、アクリル酸エステル、メタクリル酸エ
ステル、またはアクリロニトリル、の各重合体もしくは
それらのうち少なくとも２種からなる共重合体のうち、
少なくとも一種類を含む熱可塑性樹脂を配合してなる熱
可塑性エラストマーからなる摺動部材本体と、該摺動部
材本体の表面のうち、少なくとも前記筒状体内壁面と接
触する位置に被覆されたポリフッ化ビニリデン系樹脂層
と、からなることを特徴とする、医療用器具。(1) A medical instrument comprising a cylindrical body and a sliding member that slides in close contact with the wall surface of the cylindrical body, the sliding member including an acrylic ester as a base material, Of each polymer of methacrylic acid ester or acrylonitrile, or a copolymer consisting of at least two thereof,
A sliding member body made of a thermoplastic elastomer blended with at least one type of thermoplastic resin, and a polyfluoride coated on the surface of the sliding member body at least at a position in contact with the wall surface of the cylindrical body. A medical device characterized by comprising a vinylidene resin layer.
スチレン−ブタジエン−スチレンブロック共重合体（Ｓ
ＢＳ）系、スチレン−エチレン・ブチレン−スチレンブ
ロック共重合体（ＳＥＢＳ）系、エチレン−プロピレン
共重合体（ＥＰ）系、ポリエステル系、ポリウレタン系
、またはポリ塩化ビニル系の熱可塑性エラストマーであ
る請求項１に記載の医療用器具。(2) The thermoplastic elastomer of the base material of the sliding member is
Styrene-butadiene-styrene block copolymer (S
BS) type, styrene-ethylene/butylene-styrene block copolymer (SEBS) type, ethylene-propylene copolymer (EP) type, polyester type, polyurethane type, or polyvinyl chloride type thermoplastic elastomer. 1. The medical device according to 1.
マーのゴム硬度（ＪＩＳＫ６３０１、ＪＩＳ−Ａ）が８
５度以下である請求項１または２に記載の医療用器具。(3) The rubber hardness (JISK6301, JIS-A) of the thermoplastic elastomer constituting the base material of the sliding member is 8.
The medical device according to claim 1 or 2, which has an angle of 5 degrees or less.
、アクリロニトリル、の各重合体もしくはそれらのうち
少なくとも２種からなる共重合体のうち、少なくとも一
種類を含む熱可塑性樹脂が、エチレン−アクリル酸エチ
ル共重合体（ＥＥＡ）、エチレン−アクリル酸共重合体
（ＥＡＡ）、ポリアクリル酸エチル、ポリアクリル酸メ
チル、ポリメタクリル酸メチル（ＰＭＭＡ）、ポリアク
リロニトリル（ＰＡＮ）、または未加硫のアクリロニト
リルブタジエンゴム（未加硫ＮＢＲ）、である請求項１
〜３のいずれかに記載の医療用器具。(4) The thermoplastic resin containing at least one of the above-mentioned acrylic ester, methacrylic ester, acrylonitrile, or a copolymer consisting of at least two of them is an ethylene-ethyl acrylate copolymer. (EEA), ethylene-acrylic acid copolymer (EAA), polyethyl acrylate, polymethyl acrylate, polymethyl methacrylate (PMMA), polyacrylonitrile (PAN), or unvulcanized acrylonitrile butadiene rubber (uncured). Claim 1: Vulcanized NBR)
3. The medical device according to any one of 3 to 3.
、アクリロニトリル、の重合体もしくは共重合体のうち
、少なくとも一種類を含む熱可塑性樹脂の配合量が、前
記摺動部材の基材の熱可塑性エラストマー１００重量部
に対して、１〜８０重量部である請求項１〜４のいずれ
かに記載の医療用器具。(5) The amount of the thermoplastic resin containing at least one of the polymers or copolymers of acrylic ester, methacrylic ester, and acrylonitrile is 100% by weight of the thermoplastic elastomer of the base material of the sliding member. 5. The medical device according to claim 1, wherein the amount is 1 to 80 parts by weight.
動部材とを具備してなる医療用器具の製法であって、前
記摺動部材の本体を、基材に、アクリル酸エステル、メ
タクリル酸エステル、またはアクリロニトリル、の各重
合体もしくはそれらのうち少なくとも２種からなる共重
合体のうち、少なくとも一種類を含む熱可塑性樹脂を配
合してなる熱可塑性エラストマーにて構成し、該摺動部
材本体の表面のうち、少なくとも前記筒状体内壁面と接
触する位置にポリフッ化ビニリデン系樹脂層を被覆する
ことを特徴とする医療用器具の製法。(6) A method for manufacturing a medical device comprising a cylindrical body and a sliding member that slides in close contact with the wall surface of the cylindrical body, the main body of the sliding member being a base material, Consisting of a thermoplastic elastomer blended with a thermoplastic resin containing at least one of acrylic ester, methacrylic ester, or acrylonitrile, or a copolymer consisting of at least two of them. . A method for manufacturing a medical device, characterized in that a polyvinylidene fluoride resin layer is coated on the surface of the sliding member main body at least at a position that contacts the inner wall surface of the cylindrical body.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP63186888A JPH0236882A (en) | 1988-07-28 | 1988-07-28 | Medical appliance and manufacture thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP63186888A JPH0236882A (en) | 1988-07-28 | 1988-07-28 | Medical appliance and manufacture thereof |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH0236882A true JPH0236882A (en) | 1990-02-06 |
Family
ID=16196442
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP63186888A Pending JPH0236882A (en) | 1988-07-28 | 1988-07-28 | Medical appliance and manufacture thereof |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0236882A (en) |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0499945U (en) * | 1991-02-12 | 1992-08-28 | ||
| JPH04263750A (en) * | 1991-01-21 | 1992-09-18 | Mitsubishi Electric Corp | Refrigerator |
| GB2320028A (en) * | 1996-12-06 | 1998-06-10 | Shofu Kabushiki Kaisha | Dental elastic restorative material |
| WO2003004244A1 (en) * | 2001-07-03 | 2003-01-16 | Kabushiki Kaisha Top | Method of manufacturing outer tube of injector |
| US9623215B2 (en) | 2012-06-01 | 2017-04-18 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US9827401B2 (en) | 2012-06-01 | 2017-11-28 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US11628466B2 (en) | 2018-11-29 | 2023-04-18 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US11819590B2 (en) | 2019-05-13 | 2023-11-21 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
-
1988
- 1988-07-28 JP JP63186888A patent/JPH0236882A/en active Pending
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH04263750A (en) * | 1991-01-21 | 1992-09-18 | Mitsubishi Electric Corp | Refrigerator |
| JPH0499945U (en) * | 1991-02-12 | 1992-08-28 | ||
| GB2320028A (en) * | 1996-12-06 | 1998-06-10 | Shofu Kabushiki Kaisha | Dental elastic restorative material |
| GB2320028B (en) * | 1996-12-06 | 2000-10-11 | Shofu Kabushiki Kaisha | Dental elastic restorative material and method for production of dental prosthetic material using the same |
| WO2003004244A1 (en) * | 2001-07-03 | 2003-01-16 | Kabushiki Kaisha Top | Method of manufacturing outer tube of injector |
| US7229276B2 (en) | 2001-07-03 | 2007-06-12 | Kabushiki Kaisha Top | Apparatus for manufacturing outer tube of injector |
| US9623215B2 (en) | 2012-06-01 | 2017-04-18 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US9827401B2 (en) | 2012-06-01 | 2017-11-28 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US10099041B2 (en) | 2012-06-01 | 2018-10-16 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US10507309B2 (en) | 2012-06-01 | 2019-12-17 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US11628466B2 (en) | 2018-11-29 | 2023-04-18 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
| US11819590B2 (en) | 2019-05-13 | 2023-11-21 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
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