Title:
IMPLANTABLE INDUSION PUMP
United States Patent 3731681


Abstract:
An implantable pump for infusing drugs or other chemicals or solutions into the body at a uniform slow flow rate. The pump comprises a housing divided into two chambers separated by a bellows, diaphragm or other pressure-communicating interphase. A volatile liquid partially filling one chamber provides 9 constant pressure energy source to act upon the interphase to force liquid infusate from the other chamber through a capillary tube or other flow-regulating resistance element to the infusion site. The infusate chamber is closed as by means of a self puncture sealing refill stopper. The pump is implanted with the refill stopper disposed under the skin and the pump is refilled periodically by injection through the skin.



Inventors:
Blackshear, Perry J. (Mahtomedi, MN)
Dorman, Frank D. (St. Paul, MN)
Blackshear Jr., Perry L. (Mahtomedi, MN)
Buchwald, Henry (Edina, MN)
Varco, Richard L. (St. Paul, MN)
Application Number:
05/217879
Publication Date:
05/08/1973
Filing Date:
01/14/1972
Assignee:
REGENTS OF THE UNIVERSITY OF MINNESOTA,US
Primary Class:
Other Classes:
222/386.5
International Classes:
A61M5/14; A61M5/142; (IPC1-7): A61M5/00
Field of Search:
128/214R,214F,214.2,216,1R,260 222
View Patent Images:



Foreign References:
AT196550B
DE664419C
GB960535A
Primary Examiner:
Medbery, Aldrich F.
Parent Case Data:


This application is a continuation of application, Ser. No. 38,356, filed May 18, 1970, and now abandoned.
Claims:
We claim

1. An infusion pump for implantation in a living body comprising:

2. The pump defined in claim 1 wherein the moving means is comprised of a volatile fluid in the first chamber which exerts a sufficient vapor pressure at physiological temperatures to more the dividing means and force the contents of the second chamber through the outlet conduit.

3. The pump defined in claim 2 and further including:

4. The pump defined in claim 1 and further including fluid flow regulating means in the outlet conduit.

5. An infusion pump for implantation in a living body comprising:

6. having a closed end wall,

7. being sealed with respect to the interior of the housing, and

8. being compressible in response to pressure exerted on the ouside of the end wall,

9. The pump defined in claim 5 and further including a volatile liquid in the housing outside the bellows which exerts a sufficient vapor pressure at physiological temperatures to compress the bellows and force the bellows contents through the outlet conduit.

10. The pump defined in claim 5 and further including means for controlling the rate of flow of fluid through the outlet conduit.

11. The pump defined in claim 5 wherein the penetrable member is comprised of a penetrable self-sealing stopper.

12. The pump defined in claim 5 and further including means for limiting the extent to which the bellows can be compressed in response to the pressure exerted on its end wall.

13. An infusion pump for implantation in a living body comprising:

14. A pump according to claim 10 further characterized in that:

15. The pump according to claim 10 and further characterized in that:

16. The pump according to claim 12 and further characterized in that:

17. The pump according to claim 13 wherein the conduit is a length of capillary tubing.

18. The pump according to claim 10 and further characterized in that the first chamber is partially filled with a stable, volatile liquid that exerts a vapor pressure of greater than 1 atmosphere at physiological temperatures, whereby the pump is self-powered through body warmth.

19. The method of infusing liquids into a living boby, said method comprising:

20. The method of infusing fluids into a living body, said method comprising the steps of:

Description:
The invention described herein was made in the course of work under a grant or award from the Department of Health, Education and Welfare.

This invention is directed to a permanently implantable self-recycling low-flow constant rate multi-purpose infusion pump of simple design. The pump is percutaneously refillable. It operates without any kind of intrinsic or extrinsic electrical power source. It can function independently of Vascular pressure to provide continuous uniform rate infusion. Drugs or other chemical substances or fluids can be infused intravenously, intra-arterially or into a body cavity or tissue at a constant volume slow flow delivery rate. It may be used for such purposes as continuous heparinization, artificial pancreas insulin injection, chemotherapeutic organ infusion, anti-hyperlipidemic agent infusion, regional vasodilator infusion, and the like.

Previous methods of infusion have required external connections and tubing. No completely permanently implantable infusion pump with percutaneous refilling access has been known. The pump of the present invention utilizes a recycling chemical vapor-liquid constant pressure energy source, avoiding the disadvantages of any electrically powered pump, whether operated from an external or internal power pack, atomic powered pump, magnetic powered pump, or the like. The present pump utilizes the pressure used to fill the inner chamber as the kinetic energy source for restoring the potential energy to the chemical pump. Operation of the pump depends upon the physical concept that a vapor in equilibrium with its liquid phase exerts a constant vapor pressure at a given temperature, regardless of volume.

The invention is illustrated in the accompanying drawings in which the corresponding parts are identified by the same numerals and in which:

FIG. 1 is a perspective view of the implantable infusion pump, partly broken away and partly in section, and showing the components in exploded relation;

FIG. 2 is a top plan fiew of the pump;

FIG. 3 is a bottom plan view; and

FIG. 4 is a transverse sectional view, on a slightly enlarged scale, of the assembled pump.

Referring now to the drawings, the infusion pump according to the present invention comprises an outer cylindrical housing, indicated generally at 10, and having a cylindrical side wall 11, circular bottom wall 12 and annular top wall 13. A shallow cup-like member, indicated generally at 14, of lesser diameter than housing 10,is fitted into the space within annular housing top wall 13. Cup-like member 14 is open at the top and includes a cylindrical side wall 15, generally circular bottom wall 16 and outwardly extending annular flange 17. The elements of housing 10 and cup-like member 14 are formed and secured together in liquid-tight vapor-tight junctions.

A bellows, indicated generally at 18, and comprised of a stack of plurality of concentric flat annular rings 19, a circular bottom wall 20, an annular top wall 21 and a cylindrical mouth or lip 22 is positioned within housing 10. Lip 22 is secured to the inner periphery of top wall 21 and to flange 17 of cup-like member 14 in liquid-tight vapor-tight relation. Adjacent rings 19 are secured together alternately at their inner and outer peripheries, the bottom-most ring is secured to the outer periphery of bottom wall 20 and the topmost ring is secured to the outer periphery of top wall 21, all in liquid-tight vapor-tight relation, in the usual manner to form an expandable-contractible bellows structure. The annular space between the housing wall and the cup-like member provides a recess into which the bellows may be collapsed.

Bellows 18 divides the interior of housing 10 into an outer chamber 23 and inner chamber 24 of varying volume. As chamber 23 becomes larger through contraction of the bellows, chamber 24 becomes smaller, and vice versa. Housing bottom wall 12 is provided with a screw-threaded fitting 25 defining a central inlet port or aperture to chamber 23 to receive a threaded plug 26. The head 27 of screw plug 26 is provided with a transverse slot 28 on its outer surface to facilitate closing of the opening, and an annular channel on its inner surface to receive a resilient O-ring 29 to form a liquid-tight vapor-tight seal.

The bottom wall 16 of cup-like member 14 is provided with a central aperture and annular fitting 30 internally threaded to receive one end 32 of nipple 31. The central portion of nipple 31 is of greater diameter than threaded portion 32, and is desirably hexagonal or other polygonal shape. Its bottom surface is provided with an annular groove or channel to receive an O-ring 33 adapted to be compressed against the upper surface of fitting 30 to form a liquid-tight seal.

The upper portion 34 of nipple 31 is of somewhat greater diameter than the lower portion 32 and is externally threaded to receive an internally threaded knurled cap 35 having a central top opening 36. A longitudinal passage 37 extends through nipple 31. The upper end of passage 37 receives a plug or stopper 38 formed of elastic self puncture-sealing material, which serves as an entry port to chamber 24. Stopper 38 has an outwardly flanged top 39 which engages the upper end of nipple 31, the stopper being secured by knurled ring 35 in liquid-tight relation.

The fitting enclosing passage 37 may also be elongated, or bent, as in the case where the pump itself would lie some distance under the skin, i.e. in a body cavity, between two muscle planes, etc. The liquid-tight closure apparatus, 35-39, would necessarily lie at the end of this extension directly underneath the skin for percutaneous refilling ease. This closure apparatus is not limited to a puncture-sealing rubber stopper as shown, but may be replaced by any displaceable self-sealing mechanism, such as a ball valve.

The expressions "upper," "lower," "top," "bottom," etc. are relative and refer only to positions as shown in the drawings. These relationships may vary in use when the pump is implanted in the body with the opening 36 of cap 35 and stopper 38 accessible under the skin for injection of refills of the drug or other chemical to be infused.

One end of a thin small-diameter flexible capillary tube 40 (preferably within a larger protective tube) is secured in a radial discharge passage in the body of nipple 31 so as to be in direct fluid communication with the longitudinal passage through the nipple and with chamber 24 to serve as a discharge therefrom. Tube 40 serves primarily as the pressure-drop flow regulator (e.g. may be replaced by a porous plug or other flow regulating device) and is of variable length and diameter. It is coiled around nipple 31 and fits within cup-like member 14. Tubing 40 extends to the infusion site where the infused material is dispensed from its opposite end. This capillary is preferably enclosed in a larger polyethylene or Silastic cannula to facilitate placement.

The capillary tubing 40 serves a two-fold function, as a flow-regulating resistance element and a discharge port into the site of infusion. This may be replaced by a combination of any two devices accomplishing the same end; for example, the resistance element may be a porous metal plug or other filter, or any other type of flow regulator, in direct fluid communication with the infusion site by means of a conduit, such as a catheter or cannula. Also, these resistance elements may number more than one, as in the case of more than one site of infusion.

Bellows 18 is one form of liquid-tight, vapor-tight, pressure-communicating interphase means which can be used to separate the two chambers of the pump. Alternatively the chambers may be separated by a resilient diaphragm which is compatible with the substances within the chambers; or the second chamber may be formed, in part at least, from a flexible bladder which is compatible with the materials and capable of expanding and contracting under influence of the infusate and vapor-producing material in the first chamber, and the like.

A vapor in equilibrium with its liquid phase exerts a constant vapor pressure at a given temperature regardless of volume. The outer pump chamber 23 at its minimum volume is partially filled with a stable volatile liquid that exerts a vapor pressure of greater than one atmosphere at physiological temperatures (approximately 37° C) to form the vapor-liquid mixture of the chemical power source. Volatile liquids among the members of this very large group of compounds include: Perfluoro pentane, Tetramethyl silane, Ethyl ether, Methyl formate, Ethanethiol, Dimethyl sulfide, Ethylamine, 2-Methyl butane, Hydrocyanic acid, Trichlorofluro methane, and Nitrogen tetroxide. These compounds, of course, should be compatible with the substance serving as the enclosure for chamber 23. The inner chamber 24 contains the displaceable infusate. The flow rate of the infusate is varied through the use of the capillary tubing 40 for the pressure drop, which is governed by the equation: Q = (πD4 ΔP)/128μL, where Q = flow in m1/sec., D = diameter in cm., μ = viscosity in poise, Δ P = pressure in dynes/cm2, and L = length in cm. The most readily adjustable parameters are the length and diameter of the capillary and the viscosity of the infusate. Refills of infusate are injected into the inner chamber through the self-sealing stopper 38. The pressure generated by this injection is sufficient to recycle the pump by condensing the volatile vapor phase within outer chamber 23.

One or more spacer members 41 are desirably provided on the inside of bellows bottom wall 20 (or cup bottom wall 16) to prevent wall members 20 and 16 from becoming adhered through surface tension of the infusate. Desirably a filter is installed on both the inlet and outflow sides of the pump to reduce the possibility of particulate contamination. The pump is constructed of materials non-toxic to the host animal and compatible with both the infusate and the chemical power source. Stainless steel is a desirable material for forming the housing, bellows, fittings, etc. All exposed parts of the pump are covered with Silastic, Teflon, or similar material, compatible with body fluids and well-known for the coating of devices to be implanted within the body.

In-vitro tests in an incubator at 37° C have shown a high degree of constancy in infusion rates at adjusted levels of extremely low flow over various time increments. Representative mean adjusted flow rates ± standard error for different time periods include: 0.078 ± 0.0017 m1/hr for a 39 hour period; 0.101 ± 0.00035 m1/hr for an 82 hour trail; 0.183 ± 0.0073 m1/hr for a 68 hour trial; 0.363 ± 0.0046 m1/hr for a 43 hour trial; 0.373 ± 0.013 m1/hr for a 44 hour trial; and 0.613 ± 0.020 m1/hr for a 13 hour trial. The capacity of a unit in which the housing 10 measures about 21/2 by 7 cm. is approximately 20 m1. This means that low flow may be maintained over 10 days before refilling is necessary.

In-vivo trials in dogs, utilizing chronic heparinization as the measureable parameter, have confirmed in-vitro pump specifications. The pump is placed beneath the external oblique muscle with the delivery catheter threaded into the inferior vena cava through the femoral vein and the refill nipple or stopper is placed subcutaneously to be readily accessible to percutaneous needle injection. Constant infusion flows have been maintained so that the daily Lee White clotting times and activated partial thromboplastin times have remained at twice control values.

It is apparent that many modifications and variations of this invention is hereinbefore set forth may be made without departing from the spirit and scope thereof. The specific embodiments described are given by way of example only and the invention is limited only by the terms of the appended claims.