JPS5854962A - Injection and discharge pump - Google Patents
Injection and discharge pumpInfo
- Publication number
- JPS5854962A JPS5854962A JP56152715A JP15271581A JPS5854962A JP S5854962 A JPS5854962 A JP S5854962A JP 56152715 A JP56152715 A JP 56152715A JP 15271581 A JP15271581 A JP 15271581A JP S5854962 A JPS5854962 A JP S5854962A
- Authority
- JP
- Japan
- Prior art keywords
- filling chamber
- partition wall
- container
- solution
- hollow fiber
- 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.)
- Granted
Links
- 238000002347 injection Methods 0.000 title description 4
- 239000007924 injection Substances 0.000 title description 4
- 238000005192 partition Methods 0.000 claims description 45
- 239000012510 hollow fiber Substances 0.000 claims description 25
- 239000003814 drug Substances 0.000 claims description 18
- 239000007788 liquid Substances 0.000 claims description 18
- 239000002904 solvent Substances 0.000 claims description 11
- 239000000463 material Substances 0.000 claims description 10
- 239000000126 substance Substances 0.000 claims description 10
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 10
- 239000002202 Polyethylene glycol Substances 0.000 claims description 5
- 229920001223 polyethylene glycol Polymers 0.000 claims description 5
- 239000011148 porous material Substances 0.000 claims description 5
- 239000004627 regenerated cellulose Substances 0.000 claims description 5
- 239000000243 solution Substances 0.000 description 24
- 239000007864 aqueous solution Substances 0.000 description 9
- 229940079593 drug Drugs 0.000 description 9
- 230000003204 osmotic effect Effects 0.000 description 8
- 239000012528 membrane Substances 0.000 description 7
- 230000000694 effects Effects 0.000 description 3
- 210000001367 artery Anatomy 0.000 description 2
- 238000004891 communication Methods 0.000 description 2
- 239000000835 fiber Substances 0.000 description 2
- NOESYZHRGYRDHS-UHFFFAOYSA-N insulin Chemical compound N1C(=O)C(NC(=O)C(CCC(N)=O)NC(=O)C(CCC(O)=O)NC(=O)C(C(C)C)NC(=O)C(NC(=O)CN)C(C)CC)CSSCC(C(NC(CO)C(=O)NC(CC(C)C)C(=O)NC(CC=2C=CC(O)=CC=2)C(=O)NC(CCC(N)=O)C(=O)NC(CC(C)C)C(=O)NC(CCC(O)=O)C(=O)NC(CC(N)=O)C(=O)NC(CC=2C=CC(O)=CC=2)C(=O)NC(CSSCC(NC(=O)C(C(C)C)NC(=O)C(CC(C)C)NC(=O)C(CC=2C=CC(O)=CC=2)NC(=O)C(CC(C)C)NC(=O)C(C)NC(=O)C(CCC(O)=O)NC(=O)C(C(C)C)NC(=O)C(CC(C)C)NC(=O)C(CC=2NC=NC=2)NC(=O)C(CO)NC(=O)CNC2=O)C(=O)NCC(=O)NC(CCC(O)=O)C(=O)NC(CCCNC(N)=N)C(=O)NCC(=O)NC(CC=3C=CC=CC=3)C(=O)NC(CC=3C=CC=CC=3)C(=O)NC(CC=3C=CC(O)=CC=3)C(=O)NC(C(C)O)C(=O)N3C(CCC3)C(=O)NC(CCCCN)C(=O)NC(C)C(O)=O)C(=O)NC(CC(N)=O)C(O)=O)=O)NC(=O)C(C(C)CC)NC(=O)C(CO)NC(=O)C(C(C)O)NC(=O)C1CSSCC2NC(=O)C(CC(C)C)NC(=O)C(NC(=O)C(CCC(N)=O)NC(=O)C(CC(N)=O)NC(=O)C(NC(=O)C(N)CC=1C=CC=CC=1)C(C)C)CC1=CN=CN1 NOESYZHRGYRDHS-UHFFFAOYSA-N 0.000 description 2
- 238000001990 intravenous administration Methods 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 210000003462 vein Anatomy 0.000 description 2
- 102000004877 Insulin Human genes 0.000 description 1
- 108090001061 Insulin Proteins 0.000 description 1
- NNJVILVZKWQKPM-UHFFFAOYSA-N Lidocaine Chemical compound CCN(CC)CC(=O)NC1=C(C)C=CC=C1C NNJVILVZKWQKPM-UHFFFAOYSA-N 0.000 description 1
- 241000124033 Salix Species 0.000 description 1
- 239000002168 alkylating agent Substances 0.000 description 1
- 229940100198 alkylating agent Drugs 0.000 description 1
- 230000003288 anthiarrhythmic effect Effects 0.000 description 1
- 239000002246 antineoplastic agent Substances 0.000 description 1
- 229940041181 antineoplastic drug Drugs 0.000 description 1
- 230000000903 blocking effect Effects 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 230000036425 denaturation Effects 0.000 description 1
- 238000004925 denaturation Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000001647 drug administration Methods 0.000 description 1
- 239000013013 elastic material Substances 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 229940088597 hormone Drugs 0.000 description 1
- 239000005556 hormone Substances 0.000 description 1
- 238000001802 infusion Methods 0.000 description 1
- 229940125396 insulin Drugs 0.000 description 1
- 229960004194 lidocaine Drugs 0.000 description 1
- 230000007257 malfunction Effects 0.000 description 1
- 239000008155 medical solution Substances 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 230000001172 regenerating effect Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 229920003169 water-soluble polymer Polymers 0.000 description 1
Landscapes
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- External Artificial Organs (AREA)
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】
■ 発明の背景
技術分野
本発明は注出ポンプに関する。 更に詳しくは、種々の
薬液を長期間持続注出する浸透圧型の注出ポンプに関す
る。DETAILED DESCRIPTION OF THE INVENTION ■ BACKGROUND OF THE INVENTION Technical Field The present invention relates to dispensing pumps. More specifically, the present invention relates to an osmotic injection pump that continuously dispenses various medicinal solutions over a long period of time.
先行技術およびその問題点
棟々の薬液を患者等に持続注入するポンプが攬々開発さ
れているが、多くはベッドサイド用を前提としており、
患者が携行し、軽度の作業ができる小型、軽量のポンプ
の開発については十分とは言えず、また従来の多くのポ
ンプは、電気的動力源を必要とし、機構が複雑であり、
高価でもある。Prior Art and Its Problems Many pumps have been developed to continuously infuse various medicinal solutions into patients, but most of them are intended for bedside use.
The development of small, lightweight pumps that can be carried by patients and used for light work has not been sufficiently developed, and many conventional pumps require electrical power sources and have complicated mechanisms.
It's also expensive.
このような中で、小型、軽量化でき、また単純な機構と
することが可能なポンプとして、浸透圧型の注出ポンプ
が知られている。Under these circumstances, an osmotic pressure-type dispensing pump is known as a pump that can be made small and lightweight, and has a simple mechanism.
この浸透圧型の注出ポンプは、基本的には、半透膜を介
して形成される一方の充填室に水を、又他方の充填室に
所定の水溶液を満たし、浸透圧差に基づく水の水溶液側
への移動による水溶液側の体積増加を、投与すべき薬液
を充填した隔室に伝え、隔室から長時間持続して薬液を
注出させるものである。This osmotic pressure type dispensing pump basically fills one filling chamber formed through a semipermeable membrane with water and the other filling chamber with a predetermined aqueous solution, and then creates an aqueous solution of water based on the osmotic pressure difference. The volume increase on the aqueous solution side due to the sideward movement is transmitted to the compartment filled with the medicinal solution to be administered, and the medicinal solution is continuously poured out from the compartment for a long time.
しかし、従来の浸透圧型の注出ポンプは、動、静脈内持
続薬液投与用に用いる場合、患者が携行して、軽度の作
業ができるに十分なほど、小型、軽量でしかも簡易な構
造をもつに至ってはいない。However, when conventional osmotic infusion pumps are used for continuous intravenous or intravenous drug administration, they are small, lightweight, and simple enough to be carried by patients for light work. This has not yet been achieved.
また、半透膜として、平膜を用い、この平膜状半透膜を
、水および水溶液用の充填室間の隔壁としても機能させ
ているので、一旦ポンプサイズを決定すると、半透膜を
介しての水の移動速度の調節、すなわち薬液注出速度の
調節を、水溶液の濃度のみで調節しなければならず、薬
液注出速度の選択の自由度が少ない。このため、小型、
軽量としたとき、注出量を十分大きくすることができな
い。In addition, a flat membrane is used as the semipermeable membrane, and this flat semipermeable membrane also functions as a partition between filling chambers for water and aqueous solutions, so once the pump size is determined, the semipermeable membrane Adjustment of the moving speed of water through the liquid, that is, adjustment of the liquid medicine pouring rate, must be adjusted only by the concentration of the aqueous solution, and there is little freedom in selecting the liquid medicine pouring rate. For this reason, small size,
When it is lightweight, it is not possible to make the pouring amount sufficiently large.
加えて、注出速度の安定性、あるいは薬液注出口の負荷
圧に対する不感応性等において、実用に供しうる良好な
特性を示すには至っていない。In addition, it has not yet shown good characteristics suitable for practical use in terms of stability of pouring rate or insensitivity to load pressure at the drug pouring port.
夏 発明の目的
本発明は、このような実状に鑑みなされたものであって
、動・静脈内等への持続薬液投与用などとして用いると
き、患者が携行して軽度の作業ができる小型、軽量で、
しかも簡易な構造をもつ浸透圧型の注出ポンプを提供す
ることを第１の目的とする。Summer Purpose of the Invention The present invention has been made in view of the above-mentioned circumstances, and is a compact and lightweight device that can be carried by a patient and used for light work when used for continuous administration of drug solutions into arteries and veins. in,
Moreover, the first object is to provide an osmotic pressure type dispensing pump having a simple structure.
また、第２の目的は、ポンプサイズの大小に拘らず、薬
液注出速度を広範に選択設定できる浸透圧型の注出ポン
プを提供するにある。A second object is to provide an osmotic pressure-type dispensing pump that allows a wide range of drug solution dispensing speeds to be selected and set, regardless of the size of the pump.
第３の目的は、注出速度の安定性、負荷圧不感応性とも
実用に供しうる良好な特性を示す＆適圧型の注出ポンプ
を提供するにある。The third object is to provide an appropriate pressure type pouring pump that exhibits good characteristics in terms of stability of pouring speed and insensitivity to load pressure for practical use.
第４の目的は、ディスポーザブル化が可能な注出ポンプ
を提供するにある。 本発明のその他の目的は以下の記
載から自ずと明らかになるであろう。A fourth object is to provide a dispensing pump that can be made disposable. Other objects of the invention will become apparent from the description below.
本発明者は、このような目的につき鋭意研究を行い、本
発明をなすに至ったものである。The present inventor has conducted extensive research for this purpose and has come up with the present invention.
すなわち本発明は、一端に注出口部を具えた容器を有し
、当該容器の内壁間に、液密に摺動可能な弔１の隔壁を
設け、上記際注出口部を含む上記容器と当該第１の隔壁
とから内容積変化可能な薬液充填室を形成し、また上記
容器内の上記第１の隔壁の他端側には、上記容器に固着
して第２の隔壁を設け、当該第２の隔壁と上記容器とか
ら第１の充填室を形成し、当該第２の隔壁と上記第１の
隔壁と上記容器とから第２の充填室を形成し、上記第２
の隔壁に、中空内部が上記第１または第２の充填室内と
のみ連通するように、微細多孔を有するホローファイバ
ーを取りつけ、上記薬液充填室に薬液を充填し、上記第
２の充填室に、上記ホローファイバーの微細多孔を通過
しない物質を溶質とする溶液を充填し、上記第１の充填
室に上記溶液の溶媒を充填することにより、浸透圧差に
基づく上記ホローファイバーを介しての、上記第２の充
填室への溶媒の移動により、上記第２の充填室の溶液量
が増大して、上記第１の隔壁が上記注出口部端方向に摺
動し、上記薬液充填室の内容積を減少せしめ、上記注出
口部から上記薬液が持続注出されるように形成してなる
ことを特徴とする注出ポンプである。That is, the present invention has a container equipped with a spout at one end, and a partition wall 1 that can slide in a liquid-tight manner is provided between the inner walls of the container, and the container including the spout and the A liquid medicine filling chamber whose internal volume can be changed is formed from a first partition wall, and a second partition wall is provided on the other end side of the first partition wall in the container, and is fixed to the container. a first filling chamber is formed from the second partition wall and the container; a second filling chamber is formed from the second partition wall, the first partition wall, and the container;
A hollow fiber having fine pores is attached to the partition wall so that the hollow interior communicates only with the first or second filling chamber, the chemical liquid filling chamber is filled with a chemical liquid, and the second filling chamber is filled with a hollow fiber. By filling a solution containing a substance as a solute that does not pass through the micropores of the hollow fiber and filling the first filling chamber with the solvent of the solution, the As the solvent moves to the second filling chamber, the amount of solution in the second filling chamber increases, and the first partition wall slides toward the end of the spout, increasing the internal volume of the chemical liquid filling chamber. This is a dispensing pump characterized in that the medicinal solution is continuously dispensed from the dispensing port.
そして、本発明の実施態様には以下のものがある。The embodiments of the present invention include the following.
１）第１の隔壁を当該容器内にて容器軸方向に摺動する
ガスケットから形成した本発明の注出ポンプ。1) The dispensing pump of the present invention in which the first partition wall is formed from a gasket that slides in the axial direction of the container.
１１）第１の充填室の少なくとも一部をゴム等の柔軟な
材質から形成した本発明または上記ｉ）Ｋ記載の注出ポ
ンプ。11) The dispensing pump according to the present invention or i) K above, wherein at least a portion of the first filling chamber is made of a flexible material such as rubber.
リホローファイバーが再生セルロース製である本発明ま
たは上記ｉ）もしくはｉｉ）に記載の注出ポンプ。The dispensing pump according to the present invention or i) or ii) above, wherein the rehollow fiber is made of regenerated cellulose.
ｖｉ）溶液の溶媒が水で、かつ溶質がポリエチレングリ
コールである本発明または上記ｉ）ないしｉｉ）のいず
れかに記載の注出ポンプ。vi) The dispensing pump according to the present invention or any one of i) to ii) above, wherein the solvent of the solution is water and the solute is polyethylene glycol.
１ 発明の具体的構成
以下、本発明の具体的構成について、第１図に示される
実施例に従い詳細に説明する。1. Specific Structure of the Invention Below, the specific structure of the present invention will be explained in detail according to the embodiment shown in FIG.
本発明の注出ポンプｌは、第厚図にボされるように、一
端に注出口部３を具えた容器２を有する。The dispensing pump 1 of the present invention has a container 2 equipped with a dispensing spout 3 at one end, as shown in FIG.
容器２の形状、寸法等は任意のものとすることがる。
ただ、取扱いの容易さという点からは、容器２は、図示
のように、先端に注出口部３を有する円筒状とすること
が好ましい。The shape, dimensions, etc. of the container 2 may be arbitrary.
However, from the point of view of ease of handling, it is preferable that the container 2 has a cylindrical shape with a spout 3 at the tip, as shown in the figure.
また、容器２の材質としては、種々のものであってよい
。 ただ、容器２における、後述する第１の充填室７の
壁面を構成する部分のうちの少なくとも一部は、ゴム等
の柔軟な材質から形成し、第１の充填室７に充填する水
等の溶媒に常に一定の大気圧が加わるようにすることが
好ましい。Further, the material of the container 2 may be various. However, at least a part of the wall surface of the first filling chamber 7, which will be described later, in the container 2 is made of a flexible material such as rubber, and the water etc. to be filled in the first filling chamber 7 is It is preferable that a constant atmospheric pressure is always applied to the solvent.
又、容器２の注出口部３側は、剛性の材質から形成し、
容器としての形状を一定に保持し、取り扱いを容易にし
、また後述の第１の隔壁４の摺動を容易にすることが好
ましい。Further, the spout 3 side of the container 2 is made of a rigid material,
It is preferable to maintain a constant shape as a container, to facilitate handling, and to facilitate sliding of the first partition wall 4, which will be described later.
このため、第１図に示される例では、容器２は第２の隔
壁６で後端を封止された円筒状の剛性先端部と、その後
端部側に連接する後端ゴム製袋状部分とから形成されて
いる。Therefore, in the example shown in FIG. 1, the container 2 has a cylindrical rigid front end whose rear end is sealed with the second partition wall 6, and a rubber bag-shaped rear end portion connected to the rear end. It is formed from.
このような容器２の内壁間には、液密に摺動可能な第１
の隔壁４が設けられる。この第１の隔壁４は、容器２内
を液密に隔て、この第１の隔壁４と、注出口部３を含む
容器２の内壁とで、薬液充填室５を形成するものであり
、同時に容器２内にて液密に摺動して、薬液充填室５の
内容積を変化可能とするものである。 このような第１
の隔壁４としては、剛性の隔壁に０−リング等を付し、
との０−リング等により、容器内を液密に摺動可能と□
することもできるが、構造の簡易さ等からすると、第１
の隔壁４は、第１図に示されるように、弾性体からガス
ケットとして形成することが好ましい。なお、第１の隔
壁４は、摺動ではなく、変形可能なものとすることもで
きるが、変形量が限られるため、摺動可能に構成するこ
とが好ましい。Between the inner walls of such a container 2, there is a first
A partition wall 4 is provided. This first partition wall 4 liquid-tightly separates the inside of the container 2, and the first partition wall 4 and the inner wall of the container 2 including the spout portion 3 form a liquid medicine filling chamber 5. It slides in a liquid-tight manner within the container 2, thereby making it possible to change the internal volume of the chemical liquid filling chamber 5. The first one like this
As the partition wall 4, an O-ring or the like is attached to a rigid partition wall,
The 0-ring etc. allows for liquid-tight sliding inside the container.
However, considering the simplicity of the structure, the first option is
As shown in FIG. 1, the partition wall 4 is preferably formed from an elastic material as a gasket. Note that the first partition wall 4 may be deformable instead of sliding, but since the amount of deformation is limited, it is preferably configured to be slidable.
このような第１の隔壁４と、容器２の注出口部３側内壁
とで形成される薬液充填室５内には、薬液、％Ｋ、イン
シュリン、抗不整脈系、例えばリドカイン、制ガン剤、
アルキル化剤、ホルモン剤等の長時間に亘り、連続的に
微量注入を行うような薬液が充填される。In the drug solution filling chamber 5 formed by the first partition wall 4 and the inner wall on the side of the spout 3 of the container 2, a drug solution, %K, insulin, an antiarrhythmia drug such as lidocaine, an anticancer drug, etc.
It is filled with chemical solutions such as alkylating agents and hormones that are continuously injected in small amounts over a long period of time.
さらに、容器２内の第１の隔壁４の他端側には第２の隔
壁６が設けられる。この第２の隔壁６は、容器２に固着
して設けられる。 この場合、第２の隔壁６は、通常、
剛性とされ、その材質は種々のものとすることができる
。Further, a second partition wall 6 is provided on the other end side of the first partition wall 4 inside the container 2 . This second partition wall 6 is fixedly provided to the container 2. In this case, the second partition wall 6 is usually
It is assumed to be rigid and can be made of various materials.
このような第２の隔壁６により、容器２内には、容器２
内壁と第２の隔壁６とから第１の充填室７が、又容器２
内壁と、第１の隔壁４と、第２の隔壁６とから、内容積
変化可能な第２の充填室８が形成される。Due to such a second partition wall 6, there is no space inside the container 2.
From the inner wall and the second partition 6 a first filling chamber 7 is formed which also forms a container 2.
The inner wall, the first partition wall 4, and the second partition wall 6 form a second filling chamber 8 whose internal volume can be changed.
そして、この第２の充填室８内にて、第２の隔壁６に、
中空内部が第１の充填室のみと連通するように、微細多
孔を有するホローファイバー９が取りつけられる。Then, in this second filling chamber 8, on the second partition wall 6,
Hollow fibers 9 having fine pores are attached so that the hollow interior communicates only with the first filling chamber.
ホローファイバーの材質としては、ポリオレフィン、再
生セルロース等種々のものが可能であるが、特性上から
は再生セルロース製のものが好適である。 また、 ホ
ローファイバーの微細多孔の寸法としては、第２の充填
室に充填する溶液の溶質の分子寸法に応じ、それを透過
しない範囲で、種々変更可能であるが、溶媒として水を
用い、水に適した溶質を考慮すると、一般には、１０〜
２０Ａ程度の細孔径とするのが好適である。 なお、ホ
ローファイバーの内径、肉厚、長さ等は檀々変更である
。 さらに、その使用本数についても自由に変更でき、
このファイバ一本数をかえて設計することにより、ポン
プの薬液注出量を自由に変更することができる。The hollow fiber can be made of various materials such as polyolefin and regenerated cellulose, but from the viewpoint of characteristics, regenerated cellulose is preferable. The dimensions of the micropores in the hollow fiber can be varied depending on the molecular dimensions of the solute in the solution to be filled in the second filling chamber, as long as it does not pass through. Considering the solute suitable for
The pore diameter is preferably about 20A. Note that the inner diameter, wall thickness, length, etc. of the hollow fiber are subject to change. Furthermore, you can freely change the number of pieces used.
By changing the number of fibers in the design, the amount of liquid medicine dispensed by the pump can be freely changed.
さらに、上記した第２の充填室８内には、ホローファイ
バー９の微細多孔を通過しない柳質を溶質とする溶液を
充填する。 この場合、溶液としては、溶媒として水を
用い、溶質として水溶性高分子、例えば平均分子量１万
〜１０万程度、％に１万〜２万のポリエチレングリコー
ル等を用いると、水溶液の変性や取扱い等の点で有利で
ある。Further, the second filling chamber 8 described above is filled with a solution containing willow material as a solute that does not pass through the micropores of the hollow fibers 9. In this case, if water is used as the solvent and a water-soluble polymer, such as polyethylene glycol with an average molecular weight of about 10,000 to 100,000 and a percentage of 10,000 to 20,000, is used as the solute, the aqueous solution can be denatured and handled. It is advantageous in the following points.
なお、第１の充填室７内には、水等の前記第２の充填室
に充填される溶液の溶媒崇套充填される。Note that the first filling chamber 7 is filled with a solvent canister such as water for the solution to be filled in the second filling chamber.
このような構成により、浸透圧差に基づき、溶媒は、ホ
ローファイバー９の中空部から、第２の充填室８内へ移
動する。これにより、第２の充填室８内の溶液量が増大
し、第１の隔壁４が注出口部３端方向に摺動し、薬液が
持続注出される。With this configuration, the solvent moves from the hollow part of the hollow fiber 9 into the second filling chamber 8 based on the osmotic pressure difference. As a result, the amount of solution in the second filling chamber 8 increases, the first partition wall 4 slides toward the end of the spout 3, and the medicinal solution is continuously poured out.
なお、本発明において、ホローファイバー９を介して連
通ずる第１の充填ｆＬ７と第２の充填室８の連通を阻止
することにより、薬液注出速度をゼロとしたり、可変と
したりすることもできる。 この場合、連通を阻止する
には、例えば、容器外からホローファイバー９を挾さく
すればよい。In addition, in the present invention, by blocking communication between the first filling fL7 and the second filling chamber 8, which are communicated via the hollow fiber 9, the drug solution pouring speed can be made zero or variable. . In this case, communication can be prevented by, for example, pinching the hollow fiber 9 from outside the container.
さらに上記した実施例では、ホローファイバー９を、中
空内部が第１の充填室内のみと連通ずるように、第２の
隔壁６に取りつける例について説２の隔壁６に取りつけ
ることもできる。Furthermore, in the embodiment described above, the hollow fiber 9 can also be attached to the partition wall 6 of the second theory in which the hollow fiber 9 is attached to the second partition wall 6 so that the hollow inside communicates only with the first filling chamber.
■発明の具体的作用
以上詳述したような本発明の注出ポンプ１は、注出口部
３ｋ例えば穿刺針付チューブを接続し、これを患者の動
脈、静脈等に穿刺し、薬液を持続投与するために使用さ
れる。■Specific Function of the Invention The dispensing pump 1 of the present invention as described in detail above has the dispensing port 3k connected to, for example, a tube with a puncture needle, which is punctured into an artery, vein, etc. of a patient to continuously administer a drug solution. used to.
Ｖ 発明の具体的効果
本発明によれば、ポンプ全体はきわめて小型・軽量とす
ることができ、しかも構造も簡易であり、持続薬液投与
に際し、ポンプを携行し、しかも軽度の作業をすること
ができる。V. Specific Effects of the Invention According to the present invention, the pump as a whole can be made extremely small and lightweight, and has a simple structure, making it easy to carry the pump and perform light work when administering continuous drug solutions. can.
また、ポンプをディスポーザブル化することができ、電
気動力源を用いないため、機械音による患者の心理的負
担がなくなり、靜・動脈往時に、誤動作による空気の混
入もない。Furthermore, since the pump can be made disposable and does not use an electric power source, there is no psychological burden on the patient due to mechanical noise, and there is no chance of air being mixed in due to malfunction when the patient is in a quiet state.
さらに、半透膜をホローファイバーとするので、ホロー
ファイバーの長さ、細孔径のみでなく、その使用本数を
かえることにより、薬液注出速度は広範囲に所望のもの
に設定することができる。Furthermore, since the semipermeable membrane is a hollow fiber, the liquid injection rate can be set to a desired value over a wide range by changing not only the length and pore diameter of the hollow fibers but also the number of hollow fibers used.
加えて、薬液注出速度は安定であり、また薬液の注出口
部３端の負荷圧に対する不感応性も十分実用に供しうる
良好な特性を示す。In addition, the liquid medicine pouring rate is stable, and the insensitivity to the load pressure at the three ends of the liquid medicine spouting port exhibits good characteristics that can be put to practical use.
加えて、薬液注出速度をゼロないし可変とすることも可
能である。In addition, it is also possible to set the liquid medicine pouring speed to zero or variable.
本発明者は一本発明の効果を確認するため種々実験を行
った。以下にその１例を示す。The inventor conducted various experiments to confirm the effects of the present invention. An example is shown below.
なお、上記本発明の実施態様の効果を説明するならば、
上記実施態様ｉ）に従い、第１の隔壁４をガスケットか
ら形成すれば、薬液充填室５の内容積変化を大きくでき
、また構造が簡易となる。Incidentally, to explain the effects of the above embodiments of the present invention,
According to the embodiment i), if the first partition wall 4 is formed from a gasket, the change in the internal volume of the chemical liquid filling chamber 5 can be increased, and the structure can be simplified.
また、上記実施態様ｉｉ）に従い、第１の充填室７の側
壁を柔軟な材質から形成すれば、第１の充填室７に充填
する溶媒に常に大気圧が加わり、作動が良好となる。Further, according to the embodiment ii), if the side wall of the first filling chamber 7 is made of a flexible material, atmospheric pressure is always applied to the solvent filled in the first filling chamber 7, resulting in good operation.
さらＫ、上記実施態様ｉｉ）に従い、再生セルロース製
のホローファイバーを用いれば、注出速度等の精度が向
上する。Furthermore, according to the embodiment ii) above, if hollow fibers made of regenerated cellulose are used, the precision of the pouring speed and the like will be improved.
加えて、上記実施態様ｉｖ）に従い、溶液として、ポリ
エチレングリコールの水溶液を用いれば、注出速度等の
制御が容易となり、また溶液の変性や取扱い等の点で有
利である。In addition, according to the embodiment iv), if an aqueous solution of polyethylene glycol is used as the solution, the pouring rate etc. can be easily controlled and it is advantageous in terms of denaturation and handling of the solution.
実験例
３０φＸ１２０ｍ＋の第１図に示されるような注出ポン
プ１を作製した。Experimental Example 3 A pouring pump 1 as shown in FIG.
この場合、ホローファイバー９としては、再生として水
、溶質として平均分子量２０，０００のポリエチレング
リコールを用い、その濃度は１２ｆ／ｄｔとした。In this case, for the hollow fiber 9, water was used as the regenerating material, polyethylene glycol having an average molecular weight of 20,000 was used as the solute, and the concentration thereof was 12 f/dt.
ホローファイバーを５本用いたときの、注出口部３にお
ける注出流量と、縮性出量の時間変化を第２図に示す。FIG. 2 shows the time change in the flow rate and contractile output amount at the spout section 3 when five hollow fibers are used.
図中、実線は、使用ホローファイバーの半透膜特性と
水溶液濃度とから計算で求めた理論曲線である。In the figure, the solid line is a theoretical curve calculated from the semipermeable membrane characteristics of the hollow fiber used and the concentration of the aqueous solution.
第２図に示される結果から、注出流蓋はきわめて安定で
あり、注出流量、縮性出量とも、理論値の１０％以内の
誤差である。また、時間経過による、水溶液濃度の減少
に伴う注出量の減少もわずかであり、安定した長時間持
続注出が可能であることがわかる。From the results shown in FIG. 2, the pouring flow lid is extremely stable, and both the pouring flow rate and contractile output amount have errors within 10% of the theoretical values. Moreover, the decrease in the pouring amount due to the decrease in the concentration of the aqueous solution over time is slight, indicating that stable and continuous pouring for a long time is possible.
また、第３図には、上記ホローファイバーを１０本、２
０本および３０本使用したときの、注入口部端の負荷圧
と注出流量との関係が示される。In addition, FIG. 3 shows 10 hollow fibers and 2
The relationship between the load pressure at the end of the injection port and the pouring flow rate when 0 and 30 bottles are used is shown.
第３図に示される結果から、注出口部の負荷圧の増加に
伴い注出流量・は減少傾向を示すが、図中実線で示され
る理論曲線との差は１０％以下とわずかで、充分実用に
供しうる負荷圧不感応性を示すことがわかる。From the results shown in Figure 3, the pouring flow rate tends to decrease as the load pressure at the spout increases, but the difference from the theoretical curve shown by the solid line in the figure is small, less than 10%, and is sufficient. It can be seen that it exhibits load pressure insensitivity that can be used practically.
第】図は、本発明の詳細な説明するための模式断面図で
ある。 第２図および第３図は、それぞれ本発明の詳細
な説明するための線図であり、このうち第２図が注出流
量の時間特性であり、また第３図が注出流量の負Ｗ％性
である。
１・・・・・・・・・・・・注出ポンプ２・・・−・・
・・・・・・容 器
３・・・・・・・・・・・・注出口部
４・・・・・・・・・・・・第１の隔壁５・・・・・・
・・・・・・薬液充填室６・・・・・・・・−・・・第
２の隔壁７−・・・・・・・・・・・第１の充填室８・
・・・・・・・・・・・第２の充填室９・・・・・・・
・・・・・ホローファイノ（−特許出願人 テルモ株式
会社
代理人 弁理士 石 井 陽 −
！ｒ−１図
７ｆ：ｉ ８４’：＋
才２図
肯用（ｈｏｕｒ）
牙８図
洞術ル° ｍｍＨｇFIG. 1 is a schematic sectional view for explaining the present invention in detail. 2 and 3 are diagrams for explaining the present invention in detail, respectively. Of these, FIG. 2 shows the time characteristics of the pouring flow rate, and FIG. 3 shows the negative W of the pouring flow rate. It is % characteristic. 1・・・・・・・・・・・・Pour pump 2・・・・・・・・・
..... Container 3 ..... Spout section 4 ..... First partition wall 5 .....
......Medical solution filling chamber 6...Second partition wall 7-...First filling chamber 8.
......Second filling chamber 9...
・・・・・・Holofino (- Patent applicant Terumo Co., Ltd. agent Patent attorney Yo Ishii - !r-1 Figure 7f: i 84': + 2 hours) Fang 8 figures sinus surgery le ° mmHg
Claims (1)
壁間に、液密に摺動可能な第１の（１Ｍ壁を設け、上記
注出口部を含む上記容器と当該第１の隔壁とから内容積
変化可能な薬液充填室を形成し、また、上記容器内の上
記第１の隔壁の他端側には、上記容器に固着して第２の
隔壁を設け、当該第２の隔壁と上記容器とから第１の充
填室を形成し、当該第 ２の隔壁と上記第１の隔壁と上
記容器とから第２の充填室を形成し、上記第２の隔壁に
、中空内部が上記第１または第２の充填室内とのみ連通
するように、微細多孔を有するホローファイバーを取り
つけ、上記薬液充填室に薬液を充填し、上記第２の充填
室に、上記ホローファイバーの微細多孔を通過しない物
質を溶質とする溶液を充填し、上記第１の充填室に上記
溶液の溶媒を充填することにより、浸透圧差に基づく上
記ホローファイバーを介しての上記第２の充填室への上
記溶媒の移動忙より、上記第２の充填室の溶液量が増大
して、上記第１の隔壁が上記注出口部端方向に摺動し、
上記薬液充填室の内容積を減少せしめ、上記注出口部か
ら上記薬液が持続注出されるように形成してなることを
特徴とする注出ポンプ。 ２、 第１の隔壁を番棲容器内にて容器軸方向に摺動す
るガスケットから形成した特許請求の範囲第１項に記載
の注出ポンプ。 ３、 第１の充填室の少なくとも一部をゴム等の柔軟な
材質から形成した特許請求の範囲第１項または第２項に
記載の注出ポンプ。 ４、 ホローファイバーが再生セルロース製である特許
請求の範囲第１項ないし第３項のいずれかに記載の注出
ポンプ。 ５、溶液の溶媒が水で、かつ溶質がポリエチレングリコ
ールである特許請求の範囲第１項ないし第４項のいずれ
かに記載の注出ポンプ。[Claims] 1. A container having a spout section at one end, and a first (1M wall) which can slide liquid-tightly between the inner walls of the container, and which includes the spout section. The container and the first partition wall form a liquid medicine filling chamber whose internal volume can be changed, and a second partition wall fixed to the container is provided at the other end of the first partition wall in the container. a first filling chamber is formed from the second partition wall and the container; a second filling chamber is formed from the second partition wall, the first partition wall, and the container; A hollow fiber having fine pores is attached to the partition wall so that the hollow interior communicates only with the first or second filling chamber, the chemical liquid filling chamber is filled with a chemical liquid, and the second filling chamber is filled with a hollow fiber. By filling a solution containing a substance as a solute that does not pass through the micropores of the hollow fiber, and filling the first filling chamber with the solvent of the solution, the second Due to the busy movement of the solvent to the filling chamber, the amount of solution in the second filling chamber increases, and the first partition wall slides toward the end of the spout,
A dispensing pump characterized in that the internal volume of the medicinal solution filling chamber is reduced so that the medicinal solution is continuously dispensed from the spout portion. 2. The dispensing pump according to claim 1, wherein the first partition is formed of a gasket that slides in the axial direction of the container. 3. The dispensing pump according to claim 1 or 2, wherein at least a portion of the first filling chamber is made of a flexible material such as rubber. 4. The dispensing pump according to any one of claims 1 to 3, wherein the hollow fiber is made of regenerated cellulose. 5. The dispensing pump according to any one of claims 1 to 4, wherein the solvent of the solution is water and the solute is polyethylene glycol.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56152715A JPS5854962A (en) | 1981-09-27 | 1981-09-27 | Injection and discharge pump |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56152715A JPS5854962A (en) | 1981-09-27 | 1981-09-27 | Injection and discharge pump |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5854962A true JPS5854962A (en) | 1983-04-01 |
| JPS6259586B2 JPS6259586B2 (en) | 1987-12-11 |
Family
ID=15546567
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP56152715A Granted JPS5854962A (en) | 1981-09-27 | 1981-09-27 | Injection and discharge pump |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5854962A (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6081549U (en) * | 1983-11-09 | 1985-06-06 | 千寿製薬株式会社 | Automatic liquid supply device for continuous eye drops using osmotic pressure |
| JPH01126979A (en) * | 1987-11-11 | 1989-05-19 | Nikkiso Co Ltd | Instrument for discharging minute amount of liquid |
| JP2005533782A (en) * | 2002-06-17 | 2005-11-10 | アルザ コーポレイション | An osmotic delivery system having an engine with fast extruding force and zero order including an osmotic agent dispersed in a fluid vehicle |
| WO2009048144A1 (en) * | 2007-10-10 | 2009-04-16 | Olympus Corporation | Medicinal solution dispenser |
| WO2009060994A1 (en) * | 2007-11-09 | 2009-05-14 | Canon Kabushiki Kaisha | Liquid supply drive mechanism using osmotic pump and microchip having the liquid supply drive mechanism |
| JP2015213596A (en) * | 2014-05-09 | 2015-12-03 | ニプロ株式会社 | Water removal pump for portable blood dialysis |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR102295019B1 (en) | 2019-08-21 | 2021-08-30 | 조한음 | Manufacturing method of a film for preventing the damage of the front glass of vehicle |
-
1981
- 1981-09-27 JP JP56152715A patent/JPS5854962A/en active Granted
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6081549U (en) * | 1983-11-09 | 1985-06-06 | 千寿製薬株式会社 | Automatic liquid supply device for continuous eye drops using osmotic pressure |
| JPH01126979A (en) * | 1987-11-11 | 1989-05-19 | Nikkiso Co Ltd | Instrument for discharging minute amount of liquid |
| JP2005533782A (en) * | 2002-06-17 | 2005-11-10 | アルザ コーポレイション | An osmotic delivery system having an engine with fast extruding force and zero order including an osmotic agent dispersed in a fluid vehicle |
| WO2009048144A1 (en) * | 2007-10-10 | 2009-04-16 | Olympus Corporation | Medicinal solution dispenser |
| JP5302205B2 (en) * | 2007-10-10 | 2013-10-02 | オリンパス株式会社 | Chemical solution administration device |
| WO2009060994A1 (en) * | 2007-11-09 | 2009-05-14 | Canon Kabushiki Kaisha | Liquid supply drive mechanism using osmotic pump and microchip having the liquid supply drive mechanism |
| JP2009115755A (en) * | 2007-11-09 | 2009-05-28 | Canon Inc | Liquid feed drive mechanism using osmotic pressure pump and microchip having the liquid feed drive mechanism |
| US9339814B2 (en) | 2007-11-09 | 2016-05-17 | Canon Kabushiki Kaisha | Liquid supply drive mechanism using osmotic pump and microchip having the liquid supply drive mechanism |
| JP2015213596A (en) * | 2014-05-09 | 2015-12-03 | ニプロ株式会社 | Water removal pump for portable blood dialysis |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS6259586B2 (en) | 1987-12-11 |
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