JPS5949770A - Minute amount pump - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed Description of the Invention] ■ Background of the Invention (Technical Field) The present invention relates to an agile pump, and more particularly, to a pump for continuously injecting various medicinal solutions in minute amounts over a long period of time. It is.

(Prior art and its problems) Various pumps have been developed to continuously inject various medicinal solutions into the patient's temples, but most of them are based on bedside P7A, and can be carried by the patient and used for light work. It cannot be said that the opening 9 colors of small and light pumps are sufficient, and many conventional pumps require an electric power source, have complicated mechanisms, and are quite expensive.

Under these circumstances, it is important to make it smaller and lighter, and to make it OTi, pumps that utilize osmotic pressure are well-known. The osmotic pump basically fills one filling chamber formed through a semipermeable membrane with water, and the other filling chamber with an aqueous solution of a predetermined concentration, and moves the water to the aqueous solution side based on the osmotic pressure difference. The volume increase on the liquid side due to water (11) is transferred to the compartment filled with the medicinal solution to be administered, and the medicinal solution is poured out from the compartment for a long time (there is a type C).

However, when conventional osmotic pumps are used to continuously administer drug solutions into arteries and veins, they are small, lightweight, and simple enough to be carried by patients for light work. This has not yet been achieved.

In addition, conventionally, a flat membrane is used as a semipermeable membrane, and this flat membrane semipermeable membrane also functions as a partition between water J6 and aqueous solution QF≦, so once the ponfu size is determined,
Adjustment of the rate of water movement through the semipermeable membrane, -3- In other words, adjustment of the drug solution pouring speed.The aqueous solution must be prepared only once, and there is a degree of freedom in selecting the drug solution pouring speed. small. For this reason, compared to the small eaves girder, it is difficult to make the pouring force sufficiently large.However, in terms of the stability of the pouring speed or the insensitivity to the load pressure of the chemical liquid spout, However, no material showing good properties suitable for practical use has been obtained.

In view of this situation, the present inventor has previously proposed an osmotic lf-type dispensing pump using a so-called hollow fiber as a semipermeable membrane.

Regarding the dispensing pump 0 proposed in the future, the length of the hollow fiber, the pore diameter, the number of pieces used, etc.? By changing the pump size, it is possible to select the same pump size and the drug solution dispensing speed over a wide range.

However, as long as osmotic pressure is used, two liquids with different concentrations to compensate for the difference in osmotic pressure and a space to accommodate each liquid are essential, and the principle behind promoting further compactness and weight reduction is essential. It has become a major obstacle.

11. Purpose of the Invention The present invention was developed in view of the above circumstances, and is designed to be small enough to be carried by a patient for light work when used for continuous administration of drug solutions into arteries and veins. The first purpose is to provide a microponzo that is lightweight and has a simple structure.

The second object of the present invention is to
The purpose of the present invention is to provide a micro-volume pump that allows a wide range of drug solution dispensing speeds to be selected and set.

The third object of the present invention is to provide a micro-volume pump 2 that exhibits good characteristics in terms of stability of pouring rate and load pressure insensitivity that can be put to practical use.
That's what we're trying to offer.

A fourth object of the present invention is to provide a fine pomfom capable of OI by disposable decylation.

That is, the present invention provides a housing that is provided with a driving means on the proximal end side and an ejection port on the distal end side of the housing. A possible first partition wall, a second partition wall fixed to the inner circumferential wall of the housing, and a third partition wall capable of liquid-tightly sliding along the inner circumferential wall of the housing are formed, and the housing and the first partition wall form the spout. a second chamber for liquid filling that is closed by the housing and the first and second partitions, and a second chamber for liquid filling that is closed by the housing and the second and third partitions; a third chamber is provided, and at least one hollow fiber having micropores is attached between the second chamber and the third chamber so that the chamber communicates only through the micropores of the hollow fiber, and the drive The liquid in the third chamber pressurized by the means leaks into the second chamber through the hollow fiber, and as a result, the pressurized liquid in the second chamber directs the first partition wall toward the distal end of the housing. There is a small kt Ponzo C configured to continuously discharge the drug in the first chamber from the front ml spout depending on the position.

The micro-volume pump of the present invention will now be described in detail with reference to preferred embodiments shown in the accompanying drawings.

FIG. 1 is a longitudinal sectional view of a preferred example of the pump of the present invention. A drug solution spout 3 is formed at the distal end of the cylindrical nozzle 2 of the pump 110 of the present invention, and a driving means 4 is provided at the proximal end. Inside the housing song 2, a first partition wall 5 is fixed to the inner circumferential wall of the housing 2 and is slidable in a fluid-tight manner along the inner circumferential wall of the housing 2, sequentially spaced apart from the distal end side 1 of the housing 2 by a suitable distance. Similarly to the second partition wall 6 and the first partition wall 5, a third partition wall 7 is formed on the inner peripheral wall of the housing 2 and is slidable in a liquid-tight manner. As a result, the housing 2 and the first partition wall 5 form a first chamber 8 for filling the chemical liquid including the chemical liquid spout of the housing 2; A slidable first partition 5 and a fixed second partition 6 form a second chamber for filling with a suitable liquid, preferably water, and a housing 2, a fixed second partition 6 and a slidable third partition 7 form a second chamber for filling with a suitable liquid, preferably water. A jth chamber 10 is formed for filling with a suitable liquid, preferably water.

The first and third partition walls 5 and 7 are preferably structured so as to be liquid-tight and slide on the inner circumferential wall of the housing 2 with as little resistance as possible, and are preferably constructed of gaskets.

The first chamber 8 is filled with a medicinal solution such as insulin 7 that should be continuously injected in a small amount.

The 2nd to 9th and 3rd yen are filled with a liquid to provide 1E force for dispensing the medicinal solution in the first container 8, but water is most preferable for safety reasons. To the bamboo, add the second ¥9 liquid l/1. into the chemical solution in the first chamber 8. iJ) It is important to avoid contamination.

The second chamber 9 and the third chamber 10 are configured to be in fluid communication. At least two communication holes 11 are formed in the fixed partition wall 6, and at least one hollow fiber 12 having a large number of parallel holes, which will be described in detail later, is stretched between these holes for liquid leaching. High resistance film. As a result, both chambers 9 and 10 communicate only through the small #111 hole of the hollow fiber 12.

The hollow fibers 12 used in the second chamber 9 and the third chamber 100 may be any hollow tubes with minute #Iu porosity, but old cellulose The most surprising thing was discovered through the experiment. As a hollow fiber, the pore diameter is lθ~20A,
It is preferable to use a combination of many pieces having an inner diameter yj' 2 (10 μm and an outer diameter of 230 μm).

On the other hand, a driving means 4 is provided on the base end side of the housing 20. In the present invention, the driving means 4 includes:] A third partition wall slidable with a nut 16 attached to a screw shaft 15 rotatably attached to an opening 14 formed in the proximal wall 13 of the Uzong 2; A compression coil spring 17c is configured, which is stretched between the third partition wall 7 and the third partition wall 7.
It is preferable to guide by. A rotation knob 19 is provided at the end of the screw shaft 14, and a stop 202 is provided on the screw shaft 14 inside the end wall 13 of the housing 2, and the knob 19 is provided with a stop 202 inside the end wall 13 of the housing 2.
The stopper 20 prevents the screw shaft 15 from wobbling in the axial direction. 1d, the amount of rotation of the knob 19, that is, the dispensing speed of the medicinal solution, can be properly controlled by indicating means (not shown) such as a scale provided in connection with the knob 19.

■Specific effects of the invention In Nos. 1 to 8, the necessary chemical solution is supplied to the second chamber 9 and the #A3 peak 1.
When the screw shaft 15 is turned and turned by turning the knob 19 with the required amount of liquid filled in the required amount, the nut 1 screwed into the screw screw 11111s is turned.
6 is the end of Housing 2! 11111, and the coil 17 is compressed. The resulting spring pressure presses the third partition 7 toward the distal end of the housing 2, thereby pressurizing the liquid within the third partition 10. Pressure Pl in the third chamber lO! When the L wood is pushed out through the micropores of the hollow fiber 12 and oozes into the second chamber 9, the liquid in the second chamber 9 becomes pressurized or increases in volume, and due to this force, the first space A! 45 is pressed and moved toward the distal end of the housing 2. According to the amount of movement of this first partition wall, the medicinal solution in the first chamber 8 is poured out to a point indicated by an arrow 21 (f') and injected into a patient, etc.

If the knob 19 is sequentially rotated by a predetermined number of rotations as necessary, the above-described fine stitch dispensing of the medicinal solution is repeatedly and continuously performed over a long period of time.

Next, the action of J's quickness and 1 sonobu will be explained using a specific example.

Pump characteristics were measured using a pump having the structure shown in FIG. the result? The spring shown in Fig. 2 has a small spring constant (k = 4.12 x 10-'
The spring of the police/parrot was used.

As a hollow fiber, the inner diameter is 200 μm and the outer diameter is 23 μm.
0/jm, a semiuniform pore diameter of 10 to 20 A, and a length of 103, 18 hollow fibers made of regenerated cellulose were used. The pressure at the end of the chemical solution injection was set to 11 atmospheric pressure, and the outflow rate was measured five times in a row using a d balance, and the average value was taken as the outflow rate.

In the graph of Figure 2, the upper part shows the relationship between the output converted from the spring force and the outflow flow of the chemical solution.The linearity between the pressure and the outflow flow 1 is good, and this relationship is about 2 Kp /
It was maintained up to Cm2. In addition, in the graph of FIG. 2, the lower part shows the relationship between the pressure and the total outflow ambiguity when using the above-mentioned hollow fiber and spring, and the initial pressure P. This is the result when 5 ml is allowed to flow out, assuming that the effective area of the sliding partition wall 5 is 3.14a++' and 3.14a++'. When 5 ml flows out, the pressure decreases by approximately 25%. are doing.

Therefore, if this spring is used, when l, 7tnl flows out, the spring? It can be seen that by rewinding and resetting Po, the decrease in V (outflow flow) can be suppressed to 8% or less. This problem of reducing the outflow value and rewinding the spring can be solved by making the spring constant smaller VC
Improvements can be made more easily.

FIG. 3 shows the load characteristics of the pump of the present invention using pressure converted into spring force as a parameter.

This was obtained for the example using 25 hollow fibers of 1 Octn as described above, and the outflow flow rate shows a decreasing tendency as the load pressure increases. ), the difference is within a few heads, making it suitable for practical optical spectroscopy.

(2) Specific Effects of the Invention The micro-slip bond of the present invention has many advantages over conventional ones as described below.

ti) The pump as a whole is extremely small and lightweight, and has a simple structure, making it possible to carry the pump and perform light work when administering medicinal solutions.

(2) This pump has a simple structure, so the manufacturing cost is low and it can be made into an adjustable pump, making it useful from the viewpoint of economy and safety against infection.

(3) Since it does not use a mechanical power source and has almost no mechanical parts, there is no psychological burden on patients caused by conventional machines.

(4) Even if air gets mixed into the hollow fiber due to malfunction or damage to the drive unit, the outflow flow rate will simply decrease or stop, and there is no risk of air getting into the body or backflow of blood.

(5) In the present invention, since the semipermeable membrane is a hollow fiber, the drug solution pouring speed can be controlled over a wide range by selectively changing the length, porosity, inner and outer diameters, or number of hollow 7-eye bars. You can change it to Q.

(6) The chemical liquid pouring speed due to spring bias is low, and the insensitivity to haze pressure at the chemical liquid pouring end 1'' shows good characteristics that can be used for practical purposes.

[Brief explanation of the drawing]

Figure 1 shows the spring-driven micro-volume of the present invention; 1? Fig. 2 is a partial vertical sectional view of the pump, and the upper part shows the relationship between the pressure derived from the spring force and the R7ic outflow needle of the medicinal solution, and the upper part shows the relationship between the pressure and the total outflow needle. Figure 3 is a graph showing the charge qt characteristics of the pump of the present invention, with pressure in terms of spring force being plotted as parameters. Explanation of symbols 1--Pump of the present invention 0.2--Housing, 3--
・Medical solution spout, 4..., driving means, 5, 7--slidable partition, 6... fixed partition, 8... medicinal solution filling chamber, 9
, 10... Liquid filling chamber, 11... Hole, 12... Hollow fiber, 13... End wall, 14... Opening, 15
...Screw 1111.16...Cut, 17...Coil spring, 18...Guide, 19...Knob, 20...
・Stop, 21...Medicinal solution pouring direction Patent applicant: Terumo Co., Ltd. Agent Nozomi Watanabe Nozomu Watanabe, J, -゛
'') ＼￥・、°U゛Fig. 3 Hollow phiher 25 pieces Xl0cm Specific pressure load (mmHg) 371-

Claims (1)

[Claims] (1) Proximal fllfl K-blocking step and distal spout? In the housing, a first partition wall 16 is arranged at a predetermined distance from the distal end of the housing and is slidable along the inner peripheral wall of the housing in a liquid-tight manner, and a second partition wall 16 is fixed to the inner peripheral wall of the housing. and a third partition wall that can slide liquid-tightly along the inner circumferential wall of the housing to connect the housing to the housing.
iJ #iJ1 A first chamber for dispensing the medicine including the spout by the partition wall, a second chamber for liquid filling closed by the housing and the first and second partition walls, and the front housing and the second and second chambers. A third chamber for liquid filling is provided which is closed by a third partition wall, and at least one hollow fiber having micropores is provided between the second chamber and the third chamber. The fine pores are installed so that only the -C communicates with each other, and the r is pressurized by the driving means.
Is the liquid in chamber A3 1'+1 hollow eye bar? After that, the second
The liquid in the +i'+J second chamber, which is pressurized as a result of seeping into the chamber, displaces the first partition wall toward the end of the housing. A micro-dose bottle is characterized in that it is configured to continuously discharge the liquid from the spout. (Force) The front self-driving means is taken from the proximal end of the NiI housing towards the U-song/between the nut screwed onto the screw shaft and the surface of the proximal end 1 of the three partition walls. A micro-volume pump with a 0°