WO1987004629A1 - Pressure regulated implantable infusion pump - Google Patents
Pressure regulated implantable infusion pump Download PDFInfo
- Publication number
- WO1987004629A1 WO1987004629A1 PCT/US1987/000208 US8700208W WO8704629A1 WO 1987004629 A1 WO1987004629 A1 WO 1987004629A1 US 8700208 W US8700208 W US 8700208W WO 8704629 A1 WO8704629 A1 WO 8704629A1
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- WIPO (PCT)
- Prior art keywords
- chamber
- drug
- pressure
- fluid
- drug solution
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M5/14276—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body specially adapted for implantation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M2005/14264—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body with means for compensating influence from the environment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/35—Communication
- A61M2205/3507—Communication with implanted devices, e.g. external control
- A61M2205/3523—Communication with implanted devices, e.g. external control using telemetric means
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/12—Pressure infusion
Definitions
- the present invention relates to an implantable infusion pump. More particularly, the present invention relates to an implantable infusion pump which includes a pressure regulator apparatus for producing a constant drive pressure from a more variable driving force exerted on a drug solution contained in a variable volume drug chamber of the implantable infusion pump.
- a pressure regulator apparatus for producing a constant drive pressure from a more variable driving force exerted on a drug solution contained in a variable volume drug chamber of the implantable infusion pump.
- One of the earliest implantable infusion pumps intended for use in laboratory animals comprised a micro-injector comprising a compressed spring held away from a rubber-capped glass tube by a metal alloy disk with a low melting point. Administration of the injection was accomplished by placing the animal near the coils of a high-frequency induction heater. Activation of the coils melted the alloy disk and the spring ejected infusate into the desired site in the animal.
- a second implantable infusion pump for the continuous infusion of drugs utilized the osmotic pressure developed by a saturated aqueous solution of Congo red dye against water as its power source.
- the infusion pump comprised a partially collapsed rubber compartment filled with Congo red dye separated from a second water compartment by a semi-permeable cellophane member. Expansion of the rubber compartment as the water moved by osmosis into the Congo red solution ejected the drug from the infusion pump.
- Implantable infusion pumps were clinically introduced in 1975. Implantable infusion pumps currently in clinical use or in animal trials antici-naming clinical studies in the near future, include vapor pressure powered pumps, peristaltic pumps, and pulsatile solenoid pumps.
- the vapor pressure powered pump was developed at the University of Minnesota and is described hereafter.
- the peristaltic pump generally comprises a flexible tube placed in a u-shaped chamber in contact with rollers that press against the tupe with sufficient force to occlude the tube's umen. The rollers are rotated by a motor. As the rotor turns and the rollers compress the lumen of the tube, fluid is moved toward an exit.
- the rollers and housing are arranged so that a second roller begins to squeeze the tube before the first disengaged, preventing backflow of the infusate.
- Sandia Laboratories, Siemens AG, and Medtronic, Inc. have developed implantable pumps with peristaltic pumping mechanisms.
- a pulsatile solenoid pump includes a solenoid driven reciprocating chamber with two check valves to move infusate from the reservoir out through the delivery catheter. Infusate is stored in a flexible metal diaphragm reservoir.
- Such a pump has been developed by Fischell and colleagues at Johns Hopkins University Applied Physics Laboratory and by the pacesetter Corporation.
- Patent 1,314,002 are examples of such devices.
- the spring action of the metal bellows typically used to separate the drug solution from the two-phase fluid adds a variable force to the otherwise volume independent force exerted by the vapor pressure, thereby causing a steady, although predictable decline in flow rates as the drug chamber empties.
- Infusion, pumps for example, U.S.
- Patent Nos. 4,373,527- and 4,146,029 have been developed which utilize electronic controls that respond to transmitted electromagnetic signals and thus can be programed by a non-invasive procedure.
- the electronics in these infusion pumps work relatively well due to the availability of very complex, low powered integrated circuits.
- such infusion pumps have complex flow control
- An approach commonly used is to have the flow control device provide an impulse of drug solution flow for every impulse of electrical signal from the electronic control circuit. 3y having very small (microliter) individual impulses and repeating them within the normal clearance time of an infused drug solution in the blood stream (e.g. one to ten minutes), an approximation of steady flow is obtained.
- This method is very flexible in that both steady flow and variable flow up to bolus doses can be celivered by a single flow control mechanism.
- the high cycle rate of the flow control mechanism increases the wear rate of the components, increases power losses in start and stop events, and increases probability of failure of some component. If a particular component has a finite failure rate per cycle, the mean time to failure decreases as the rate of cycling goes up.
- Typical systems employed in such electronically controlled infusion pumps include: (a) cyclic filling and emptying of a small drug accumulator with upstream and downstream valves; (b) an active piston pump with passive valves; and (c) miniature roller (peristaltic) pumps.
- the drug solution storage chamber is passive and is held at a fixed pressure usually a little above atmospheric
- the low pressure serves to reduce the potential hazard of an infusator leak.
- Accumulator systems use a higher drug chamber pressure to get positive filling cycles.
- the above described electronically controlled infusion pumps have an unnecessarily wide dynamic range and re ponse time for many applications. Moreover, they are complex, expensive and subject to failure.
- the fixed flow rate infusion pump has been shown to provide adequate therapy for a range of disease states with no flow control for a given cycle.
- An infusion pump is required which provides a degree of drug solution flow control which is better than currently available infusion pumps of the constant flow design but which is less complex than that of the presently available electronically controlled infusion pumps.
- the present invention solves these and many other problems associated with currently existing infusion pumps.
- the present invention relates to an apparatus and method for controlling the pressure applied to a drug solution in the drug chamber of an implantable infusion pump.
- the preferred embodiment of the present invention utilizes a pressurized support piston and pressure regulator arrangement to produce a constant force (drive pressure) on a drug solution in the drug chamber from a more variable driving force that might be a spring mechanism or any other force producing device.
- the pressure can be maintained without subjecting the drug solution to the high shear force at the exit port of the pressure regulator.
- a preferred embodiment of the present invention readily lends itself to electronic control whereby the flow rate of the drug solution can be changed by transmitted electromagnetic signals. Moreover/ the electronic control can be preprogrammed to vary the drug solution flow rate as required.
- the present invention provides an electronically controlled infusion pump which is less complex than existing, electronically controlled infusion pumps.
- telemetry can be used either to directly set the reference pressure of the infusion pump's regulator by supplying telemetered power to an otherwise passive motor control circuit or provide commands to an electronic timing circuit that can execute the command at a later time using internal battery power.
- Many applications of the infusion pump of the present invention will require only a non-invasive method of resetting the drug solution flow rate and maintaining the flow rate until the next cycle time.
- the infusion pump of the present invention can be preprogrammed and not require any intervention by the patient.
- the preferred embodiment of the present invention has a variable volume drug chamber formed partially by a movable, relatively rigid diaphragm which moves under the influence of a force producing device to expell the drug solution from the drug chamber.
- Movement of the diaphragm is opposed by a column of pressurized fluid, herein referred to as a support piston, whose pressure is controlled by the reference pressure of a pressure regulator apparatus so as to allow only a constant force to be applied by the diaphragm on the drug solution in the drug chamber. Any excess force exerted by the diaphragm is absorbed by the support piston.
- the reference pressure of the regulator is interconnected to the support piston by a one-way flow valve which regulates fluid flow from the support piston to a reference pressure chamber of the regulator.
- the regulator need only release fluid from the support piston at a controlled rate in order to maintain constant drug solution pressure.
- the reference pressure of the regulator will be preselected by appropriate configuration of a force producing device such as a spring device which acts on a diaphragm of the regulator so as to produce the regulator reference pressure.
- the pressure regulator can maintain either an absolute internal drug chamber pressure or a relative internal drug chamber pressure wherein the regulator compensates for atmospheric pressure so as to maintain a constant pressure differential between the drug chamber and the internal body pressure.
- the support piston will utilize a closed system wherein its operating fluid is kept separate from the drug solution or an open system wherein the drug solution itself is used as the operating fluid of the support piston.
- An advantage of the regulator of the present invention is that power is required only to change the reference pressure of the regulator in order to change the drug solution flow rate.
- the actual work, needed to deliver the drug solution at the selected flow rate is accomplished by the pressure of the drug chamber.
- the pressure of the drug chamber can be readily varied by changing the reference pressure of the regulator since the drug chamber pressure is the difference between the total force being exerted by the drug chamber diaphragm and the countering force of the support piston whose pressure is controlled by the reference pressure of the regulator.
- the regulator decreases the outflow of fluid from the support piston.
- the fluid in the support piston is released more rapidly by the regulator. Accordingly, the regulator need only vary the flow of fluid out of the support piston in order to vary drug chamber pressure.
- An advantage of the present invention is that by using a variable drug chamber pressure design, much of the safety and ease of use of the steady flow infusion pump designs is retained.
- An electronically controlled embodiment of the present invention might use an electromechanical arrangement to compress or expand the regulator diaphragm in order to vary the reference pressure of the regulator.
- Figure 1 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the regulator compensates for atmospheric pressure
- Figure 2 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the drug solution is used as the support fluid of the support piston
- Figure 3 is a diagrammatic/cross-sectional view wherein the regulator does not compensate for atmospheric pressure
- Figure 4 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the regulator does not compensate for atmospheric pressure and the drug solution serves as the support fluid for the support piston
- Figure 5 is a diagrammatic/cross-sectional view illustrating an electronically controlled embodiment of the present invention
- Figure 6 is a diagrammatic/cross-sectional view illustrating a possible packaging arrangement of components of an embodiment of an infusion pump in accordance with the principles of the present invention
- Figure 7 is a diagrammatic/cross-sectional view of an embodiment of the present invention whichutilizes an adjustable force applicator device for varying the reference pressure of the regulator;
- Figure 8 is an enlarged partial sectional view of the regulator valve in an increased flow setting
- Figure 9 is a view s i mi l ar to Figure 8 wherein the regulator valve is in a reduced flow setting.
- FIG. 1 there is illustrated in Figures 1 through 7 various embodiments of an implantable infusion pump in accordance with the principles of the present invention, the infusion pump being generally referenced by the reference numeral 20.
- the embodiment of the infusion pump 20 illustrated in Figure 1 includes a variable volume drug chamber 22 formed by a wall structure 24 of the infusion pump 20 and a diaphragm 26 interconnected to the wall structure 24 by a spring arrangement 28.
- the spring arrangement 28 functions as a force producing ( F p ) device causing the diaphragm 26 to exert a variable force on the drug solution in the drug chamber 22.
- F p force producing
- the support piston 32 is interconnected to a regulator apparatus 33 including a chamber 34 defined by a diaphragm 36 and force producing spring arrangement 38 which produces a predetermined force (F s ) on the diaphragm 36.
- the support fluid of the support piston is interconnected to the regulator chamber 34 by a one-way valve arrangement 40 which controls the fluid flow into the regulator chamber 34.
- the spring 38 can exert a variable force ever a range of movement ant still be used to provide a predetermined force, since in operation, the diaphragm 36 will move very little.
- the valve arrangement 40 will provide a steady, regulated flow.
- the support fluid of the support piston 32 is contained in the regulator chamber 34 and a chamber 42 interconnected to the chamber 34 by a pathway 45 and including a diaphragm 41 and bellows 43 arrangement, so as to be kept separate from the drug solution in the drug chamber 22.
- the diaphragm 36 is exposed to the internal body pressure which reflects the atmospheric pressure. In this manner, the regulator 33 comprising diaphragm 36 and spring bellows 38 is referenced to atmospheric pressure and produces a constant flow rate regardless of atmospheric changes.
- the embodiment illustrated in Figure 2 utilizes the drug solution as the support fluid for the piston 32 and thus does not include the fluid chamber 42. Since the drug solution itself is used as the support fluid in the support piston, it must pass through the regulator valve 40. This embodiment achieves a larger volumetric efficiency and a lower cost due to fewer parts compared to electronic or vapor pressure driven pumps. Moreover, the regulator diaphragm 26 is exposed to the external pressure as illustrated in Figure 1.
- Figure 3 illustrates an embodiment of the present invention wherein the regulator diaphragm 36 is internally referenced to a chamber 50 enclosed by an immovable shell structure 32, the chamber 50 being filled with gas at atmospheric pressure (or lower).
- This embodiment does not provide any reference to the atmospheric pressure and as a result, has to operate at a higher pressure in order to avoid variation in atmospheric pressure.
- This embodiment as well as that shown in Figure 4 which has the same closed chamber 50 but no support piston fluid reservoir 42, are designs that allow more freedom in construction since the small regulator mechanism can be placed in the pump interior with no connection to the exterior. It also provides a sealed place for electronic controls that can mechanically change the regulator pressure (P R ) or set point.
- FIG. 5 illustrates an electronically controlled version of an infusion pump in accordance with the principles of the present invention.
- conventional telemeter receiver controlling circuits 54 for receiving commands from a telemetry transmitter 56 and for controlling small electromechanical components or servomechanisms 55 that can vary the force exerted on the diaphragm 36 and thus vary the regulator reference pressure.
- any number of well known devices might be utilized. For example, this might be in the form of a small electric motor and gear train that would compress or expand the spring arrangement 38 supplying the force on the diaphragm 36. Battery power would be required only when the settings were changed.
- the telemetry transmitter and receiver could be of the type presently used for transcutaneous signal transmission and are available commercially. Examples of such control circuitry are disclosed in U.S. Patent Nos. 4,373,527 and 4,146,029. Signal coding could be used to decrease the possibility of accidental operation.
- the receiver controls might be passive circuits that obtain their power from the transmitter since they would be activated only to change the pressure.
- the regulator of the present invention is particularly suited to changing the reference pressure set point slowly due to the slow flow rate out of the infusion pump, and rapid changes in drug solution flow rate are not particularly suited for this design.
- the pressure control circuit would pr eferably be in the form of an adjustable basal rate rather than the flexible control used in other pumps that can be used to deliver fast bolus flows. This slow control greatly increases the safety of its operation.
- an infusion pump ofthe present invention uses the outer shell structure of the infusion pump as a spring element that stores energy in the form of tension and compression of the metal or plastic material comprising the shell structure.
- the reference pressure for the regulator can be obtained from either the top or bottom of the pump in the form of a thin, large diameter diaphragm that separates the pressure transmitting fluid from the body tissue.
- Figure 6 illustrates a possible packaging of the components of the embodiment illustrated in Figure 3.
- the present invention will include an inlet port 60 and an outlet port 62.
- a self-sealing, penetrable septum member 64 Suitably positioned in the inlet port 60 is a self-sealing, penetrable septum member 64, a filter 65 being positioned in the outlet port.
- a capillary flow restricter 66 is inter onnected to the outlet port by a suitable connecter 68. The capillary flow restrictor might then be interconnected to a catheter for delivery of the drugs to an infusion site in the body although any number of other well known devices might be used.
- a convoluted diaphragm 67 is utilized to allow nesting of the drug chamber diaphragm 26 therewith. (In this illustration, the regulator 34 is generally illustrated without any of its individual components.) The total force on the diaphragm 26 is opposed by the sum of the drug solution pressure in the drug chamber 22 and the support piston 32 fluid pressure:
- a P area of diaphragm 26
- P S pressure of fluid in support piston
- a S area of support piston diaphragm.
- P D pressure in drug chamber
- a D area of drug chamber diaphragm.
- Regulation of the drug solution pressure (P D ) occurs due to mechanical negative feedback action of the valve 40 so as to maintain a balanced force on the diaphragm 36. If the pressure (P D ) of the drug solution drops, so does the regulator pressure (P R ) which causes the valve 40 to open to allow entry of more of the fluid from the support piston chamber which is at a high pressure (P s ).
- P R regulator pressure
- FIG 8 illustrates the valve 40 in a reduces flow setting wherein a smaller opening 37 is provide for drug solution flow.
- the valve 40 will preferably include a seal 35, such as an O-ring or the like. This restores the balance forces on the regulation diaphragm 36 by increasing regulator pressure (P R ) .
- the control equations are:
- the regulator force (F R ), the regulator diaphragm area (A R ) and the capillary resistance R are fixed quantities, therefore, the flow Q will be fixed independent of the atmospheric pressure and the force on the drug chamber diaphragm 26.
- the regulator force ( F R ) might be preset by selecting a spring member 38 which creates the required force ( F R ) .
- an adjustable force applicator 25 is utilized to apply a predetermined force (F R ) on the diaphragm 36.
Abstract
An implantable infusion pump (20) for infusing drugs or other chemical or solutions into the body. A movable diaphragm (26) forming a variable volume drug chamber (22). A fluid piston (32) opposing the force exerted by the diaphragm (26) on the drug solution in the drug chamber (22). The pressure of the fluid piston (32) being controlled by a regulator (33) providing a reference pressure and in fluid communication with the fluid piston (32). The regulator (33) reducing the fluid pressure of the piston fluid (32) as drug solution is expelled from the drug chamber (22) so as to maintain a constant pressure differential between the drug chamber (22) and an infusion site in the body. The implantable infusion pump (20) being readily adaptable to variable or electronic flow control.
Description
PRESSURE REGULATED IMPLANTABLE INFUSION PUMP
BACKGROUND OF THE INVENTION
The present invention relates to an implantable infusion pump. More particularly, the present invention relates to an implantable infusion pump which includes a pressure regulator apparatus for producing a constant drive pressure from a more variable driving force exerted on a drug solution contained in a variable volume drug chamber of the implantable infusion pump. Infusion pump designs rarely appeared in the medical literature until the 1950s. Most of these early infusion pumps were extracorporeal. One such device included a reciprocating air pump driven by an electric motor. Yet another design considered comprised a metal housing for a class syringe and a compression chamber fed by a tank of nitrogen gas. Yet another such infusion. pump included a motorized syringe pump which induced an electric motor connected to the worm drive that moved a syringe plunger by a gear box. The gears were interchangeable such that replacement of the gears permitted different delivery rates. Yet another infusion pump included a syringe plunger driven by a rider on a threaded shaft. Numerous other designs were considered for these extracorporeal infusion pumps. P.D.W. Soden in his thesis entitled, "A Methodical Design Study of Miniature Profusion Devices For Chemotherapy of Cancer of the Head and Neck" , studied possible designs for producing a miniature profusion device to be carried by smb-ulating patients receiving chemctherapeutic traat- ment for cancer of the head and neck. Quoting from his thesis, "Approximately two millien alternative design, solutions were synthesized and recorded in compact matrix form on a 'morphological chart'". One of the numerous design concepts mentioned by Soden for possible use with an extracorporeal infusion pump was the use of
a small tubular arrangement containing an elastic metal bellows possibly constructed from preloaded disks so as to form a relatively small diaphragm in the tubular arrangement for exerting a fairly constant force on the drug solution being infused. Due to the size of the diaphragm, this design provided for very little, if any, compensation for changes in atmostpheric pressure.
One of the earliest implantable infusion pumps intended for use in laboratory animals comprised a micro-injector comprising a compressed spring held away from a rubber-capped glass tube by a metal alloy disk with a low melting point. Administration of the injection was accomplished by placing the animal near the coils of a high-frequency induction heater. Activation of the coils melted the alloy disk and the spring ejected infusate into the desired site in the animal. A second implantable infusion pump for the continuous infusion of drugs utilized the osmotic pressure developed by a saturated aqueous solution of Congo red dye against water as its power source. The infusion pump comprised a partially collapsed rubber compartment filled with Congo red dye separated from a second water compartment by a semi-permeable cellophane member. Expansion of the rubber compartment as the water moved by osmosis into the Congo red solution ejected the drug from the infusion pump.
Implantable infusion pumps were clinically introduced in 1975. Implantable infusion pumps currently in clinical use or in animal trials antici-naming clinical studies in the near future, include vapor pressure powered pumps, peristaltic pumps, and pulsatile solenoid pumps. The vapor pressure powered pump was developed at the University of Minnesota and is described hereafter. The peristaltic pump generally comprises a flexible tube placed in a u-shaped chamber
in contact with rollers that press against the tupe with sufficient force to occlude the tube's umen. The rollers are rotated by a motor. As the rotor turns and the rollers compress the lumen of the tube, fluid is moved toward an exit. The rollers and housing are arranged so that a second roller begins to squeeze the tube before the first disengaged, preventing backflow of the infusate. Sandia Laboratories, Siemens AG, and Medtronic, Inc. have developed implantable pumps with peristaltic pumping mechanisms. A pulsatile solenoid pump includes a solenoid driven reciprocating chamber with two check valves to move infusate from the reservoir out through the delivery catheter. Infusate is stored in a flexible metal diaphragm reservoir. Such a pump has been developed by Fischell and colleagues at Johns Hopkins University Applied Physics Laboratory and by the pacesetter Corporation.
Much effort has been expended in developing external infusion devices which provide a steady pressure on the drug solution so as to provide a steady flow of drug solution to the patient. For example, U.S.
Patent Nos. 2,515,152 and 3,023, -50 as well as French
Patent 1,314,002 are examples of such devices.
Currently available implantable infusion pumps also have difficulty in maintaining constant pressure as the volume of the drug solution in their drug chambers chances. Typically, the output flow of drug solution is regulated by external means, an example of whicn is illustrated in U.S. Patent Ho. 4,299,220, or if passive flow restrictors are used to control the drug solution output, flow variation must be tolerated. The two ambient conditions that commonly cause flow variation are temperature and atmospheric pressure. In the vaporpressure powered infusion pump disclosed in U.S. patent Ho. 3,731,651, both of these conditions cause the
pressure differential between the drug chamber and the internal body pressure to change thereby causing a corresponding change in drug solution flow rate from the infusion pump into an infusion site in the body. In addition, the spring action of the metal bellows typically used to separate the drug solution from the two-phase fluid adds a variable force to the otherwise volume independent force exerted by the vapor pressure, thereby causing a steady, although predictable decline in flow rates as the drug chamber empties. In many applications it is necessary to change the flow rate of the drug solution frequently, more frequently than can be cone by changing the concentration by an empty-refill cycle en a constant flow rate infusion pump. Examples of such applications are: (1) the delivery of insulin to a brittle diabetic with no residual insulin production, (2) the delivery of a chemotherapeutic agent that has a strong dependence on biological timing, or (3) the delivery of a hormone that is timed to the natural rhythm of the body. Infusion, pumps; for example, U.S. Patent Nos. 4,373,527- and 4,146,029, have been developed which utilize electronic controls that respond to transmitted electromagnetic signals and thus can be programed by a non-invasive procedure. The electronics in these infusion pumps work relatively well due to the availability of very complex, low powered integrated circuits. However, such infusion pumps have complex flow control
An approach commonly used is to have the flow control device provide an impulse of drug solution flow for every impulse of electrical signal from the electronic control circuit. 3y having very small (microliter) individual impulses and repeating them within the normal clearance time of an infused drug solution in the blood
stream (e.g. one to ten minutes), an approximation of steady flow is obtained. This method is very flexible in that both steady flow and variable flow up to bolus doses can be celivered by a single flow control mechanism. However, the high cycle rate of the flow control mechanism increases the wear rate of the components, increases power losses in start and stop events, and increases probability of failure of some component. If a particular component has a finite failure rate per cycle, the mean time to failure decreases as the rate of cycling goes up. When a repeatedly cycled valve is used to produce a constant flow rate for an extended time period (several hours) there is an unnecessary hazard involved that would not be present if the same fixed flow rate were achieved by other means. If the fixed flow rate were known, a simple capillary tube could deliver that rate with only one cycle of valve open and fixed dose, rather than a hundred or so open dose cycles which might be required in an electronic impulse controlled system.
Typical systems employed in such electronically controlled infusion pumps include: (a) cyclic filling and emptying of a small drug accumulator with upstream and downstream valves; (b) an active piston pump with passive valves; and (c) miniature roller (peristaltic) pumps. In all three of these mechanisms, the drug solution storage chamber is passive and is held at a fixed pressure usually a little above atmospheric
dissolved air. The low pressure serves to reduce the potential hazard of an infusator leak. Accumulator systems use a higher drug chamber pressure to get positive filling cycles.
The above described electronically controlled infusion pumps have an unnecessarily wide dynamic range
and re ponse time for many applications. Moreover, they are complex, expensive and subject to failure. On the other hand, the fixed flow rate infusion pump has been shown to provide adequate therapy for a range of disease states with no flow control for a given cycle. An infusion pump is required which provides a degree of drug solution flow control which is better than currently available infusion pumps of the constant flow design but which is less complex than that of the presently available electronically controlled infusion pumps. The present invention solves these and many other problems associated with currently existing infusion pumps.
SUMMARY OF THE INVENTION
The present invention relates to an apparatus and method for controlling the pressure applied to a drug solution in the drug chamber of an implantable infusion pump. The preferred embodiment of the present invention utilizes a pressurized support piston and pressure regulator arrangement to produce a constant force (drive pressure) on a drug solution in the drug chamber from a more variable driving force that might be a spring mechanism or any other force producing device. Moreover, the pressure can be maintained without subjecting the drug solution to the high shear force at the exit port of the pressure regulator.
A preferred embodiment of the present invention readily lends itself to electronic control whereby the flow rate of the drug solution can be changed by transmitted electromagnetic signals. Moreover/ the electronic control can be preprogrammed to vary the drug solution flow rate as required.
The present invention provides an electronically controlled infusion pump which is less complex than existing, electronically controlled infusion pumps. In an electronically controlled embodiment of the present invention, telemetry can be used either to directly set the reference pressure of the infusion pump's regulator by supplying telemetered power to an otherwise passive motor control circuit or provide commands to an electronic timing circuit that can execute the command at a later time using internal battery power. Many applications of the infusion pump of the present invention will require only a non-invasive method of resetting the drug solution flow rate and maintaining the flow rate until the next cycle time. An example of this might include most insulin delivery systems where the increase in flow rate to adjust for mealtime demand is done by the patient on his/her own schedule (e.g. at night the insulin flow rate is typically reduced to adjust for the lower demand curing sleep). In applications where drug solution is delivered on a fixed variable rate schedule, such as in the case of hormone or chemotherapeutic agents, the infusion pump of the present invention can be preprogrammed and not require any intervention by the patient. The preferred embodiment of the present invention has a variable volume drug chamber formed partially by a movable, relatively rigid diaphragm which moves under the influence of a force producing device to expell the drug solution from the drug chamber. Movement of the diaphragm is opposed by a column of pressurized fluid, herein referred to as a support piston, whose pressure is controlled by the reference pressure of a pressure regulator apparatus so as to allow only a constant force to be applied by the diaphragm on the drug solution in the drug chamber. Any
excess force exerted by the diaphragm is absorbed by the support piston. The reference pressure of the regulator is interconnected to the support piston by a one-way flow valve which regulates fluid flow from the support piston to a reference pressure chamber of the regulator. In the preferred embodiment, the regulator need only release fluid from the support piston at a controlled rate in order to maintain constant drug solution pressure. In some embodiments of the present invention, the reference pressure of the regulator will be preselected by appropriate configuration of a force producing device such as a spring device which acts on a diaphragm of the regulator so as to produce the regulator reference pressure.
In various embodiments of the present invention, the pressure regulator can maintain either an absolute internal drug chamber pressure or a relative internal drug chamber pressure wherein the regulator compensates for atmospheric pressure so as to maintain a constant pressure differential between the drug chamber and the internal body pressure.
In various embodiments of the present invention, the support piston will utilize a closed system wherein its operating fluid is kept separate from the drug solution or an open system wherein the drug solution itself is used as the operating fluid of the support piston.
An advantage of the regulator of the present invention is that power is required only to change the reference pressure of the regulator in order to change the drug solution flow rate. The actual work, needed to deliver the drug solution at the selected flow rate is accomplished by the pressure of the drug chamber. The pressure of the drug chamber can be readily varied by
changing the reference pressure of the regulator since the drug chamber pressure is the difference between the total force being exerted by the drug chamber diaphragm and the countering force of the support piston whose pressure is controlled by the reference pressure of the regulator. In the preferred embodiment, to reduce drug chamber pressure, the regulator decreases the outflow of fluid from the support piston. In order to increase the drug chamber pressure, the fluid in the support piston is released more rapidly by the regulator. Accordingly, the regulator need only vary the flow of fluid out of the support piston in order to vary drug chamber pressure.
An advantage of the present invention is that by using a variable drug chamber pressure design, much of the safety and ease of use of the steady flow infusion pump designs is retained.
An electronically controlled embodiment of the present invention might use an electromechanical arrangement to compress or expand the regulator diaphragm in order to vary the reference pressure of the regulator.
These and various other advantages and features of novelty which characterize the present invention are pointed out with particularity in the claims and next hereto and forming a part hereof. However, for a better understanding of the invention, its advantages and objects obtained by its use, reference should be had to the drawings which form a further part hereof and to the accompanying descriptive matter in which there is illustrated and described a oreferred embodiment of the present invention.
BRIEF DESCRIPTION OF THE DRAWINGS In the drawings, in which like reference numerals and letters indicate corresponding part throughout the several views; Figure 1 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the regulator compensates for atmospheric pressure; Figure 2 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the drug solution is used as the support fluid of the support piston;
Figure 3 is a diagrammatic/cross-sectional view wherein the regulator does not compensate for atmospheric pressure; Figure 4 is a diagrammatic/cross-sectional view of an embodiment of the present invention wherein the regulator does not compensate for atmospheric pressure and the drug solution serves as the support fluid for the support piston; Figure 5 is a diagrammatic/cross-sectional view illustrating an electronically controlled embodiment of the present invention;
Figure 6 is a diagrammatic/cross-sectional view illustrating a possible packaging arrangement of components of an embodiment of an infusion pump in accordance with the principles of the present invention;
Figure 7 is a diagrammatic/cross-sectional view of an embodiment of the present invention whichutilizes an adjustable force applicator device for varying the reference pressure of the regulator;
Figure 8 is an enlarged partial sectional view of the regulator valve in an increased flow setting; and
Figure 9 is a view s i mi l ar to Figure 8 wherein the regulator valve is in a reduced flow setting.
DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT OF THE PRESENT INVENTION
Referring now to the drawings, there is illustrated in Figures 1 through 7 various embodiments of an implantable infusion pump in accordance with the principles of the present invention, the infusion pump being generally referenced by the reference numeral 20. The embodiment of the infusion pump 20 illustrated in Figure 1 includes a variable volume drug chamber 22 formed by a wall structure 24 of the infusion pump 20 and a diaphragm 26 interconnected to the wall structure 24 by a spring arrangement 28. The spring arrangement 28 functions as a force producing ( Fp) device causing the diaphragm 26 to exert a variable force on the drug solution in the drug chamber 22. It will be appreciated, that any ether number of force producing devices might be used to exert a force on the drug solution. Interconnecting the wall structure 24 to the diaphragm 26 is a cylindrical column of under pressure fluid (P3) enclosed by a flexible bellows arrangement 30 so as to form a support piston 32 which counters the force being exerted by the diaphragm 26 on the drug s o l ution in the drug chamber 22. The support piston 32 is interconnected to a regulator apparatus 33 including a chamber 34 defined by a diaphragm 36 and force producing spring arrangement 38 which produces a predetermined force (Fs) on the diaphragm 36. The support fluid of the support piston is interconnected to the regulator chamber 34 by a one-way valve arrangement 40 which controls the fluid flow into the regulator chamber 34. It will be appreciated that the spring 38 can exert a variable force ever a range of movement ant still be used to provide a predetermined force, since in operation, the diaphragm 36 will move very little. The valve
arrangement 40 will provide a steady, regulated flow. In the embodiment shown in Figure 1, the support fluid of the support piston 32 is contained in the regulator chamber 34 and a chamber 42 interconnected to the chamber 34 by a pathway 45 and including a diaphragm 41 and bellows 43 arrangement, so as to be kept separate from the drug solution in the drug chamber 22. Additionally, the diaphragm 36 is exposed to the internal body pressure which reflects the atmospheric pressure. In this manner, the regulator 33 comprising diaphragm 36 and spring bellows 38 is referenced to atmospheric pressure and produces a constant flow rate regardless of atmospheric changes.
The embodiment illustrated in Figure 2 utilizes the drug solution as the support fluid for the piston 32 and thus does not include the fluid chamber 42. Since the drug solution itself is used as the support fluid in the support piston, it must pass through the regulator valve 40. This embodiment achieves a larger volumetric efficiency and a lower cost due to fewer parts compared to electronic or vapor pressure driven pumps. Moreover, the regulator diaphragm 26 is exposed to the external pressure as illustrated in Figure 1. Figure 3 illustrates an embodiment of the present invention wherein the regulator diaphragm 36 is internally referenced to a chamber 50 enclosed by an immovable shell structure 32, the chamber 50 being filled with gas at atmospheric pressure (or lower). This embodiment does not provide any reference to the atmospheric pressure and as a result, has to operate at a higher pressure in order to avoid variation in atmospheric pressure. This embodiment, as well as that shown in Figure 4 which has the same closed chamber 50 but no support piston fluid reservoir 42, are designs
that allow more freedom in construction since the small regulator mechanism can be placed in the pump interior with no connection to the exterior. It also provides a sealed place for electronic controls that can mechanically change the regulator pressure (PR) or set point.
In the embodiments illustrated in Figure 1 and
Figure 3, at the end of a cycle when the drug chamber 22 is empty, most of the operating fluid of the piston 32 will be transferred to the chamber 42. When drug solution is injected into the infusion pump through the refill septum, the pressure (PD) in the drug chamber 22 will rise and the diaphragm 26 will retract producing negative pressure across the regulator 33. This excess negative drug pressure will cause the regulator 33 to close to allow the internal pressure to fall to the control point. In order to reset the infusion pump for another cycle, a bypass check valve 41 responds to the negative pressure and allows operating fluid to flow back into the support piston 32. When the infusion pump drug chamber is full, the regulator 33 takes over control of the drug chamber pressure as scon as a small amount of drug solution has left the drug chamber. In the embodiment illustrated in Figures 2 and
4, the drug solution itself refills the support piston chamber, through the check valve. The embodiment illustrated in Figure 5 illustrates an electronically controlled version of an infusion pump in accordance with the principles of the present invention. In the air space in the chamber 50 behind the regulator diaphragm 36 there are placed conventional telemeter receiver controlling circuits 54 for receiving commands from a telemetry transmitter 56 and for controlling small electromechanical components or servomechanisms 55
that can vary the force exerted on the diaphragm 36 and thus vary the regulator reference pressure. It will be appreciated that any number of well known devices might be utilized. For example, this might be in the form of a small electric motor and gear train that would compress or expand the spring arrangement 38 supplying the force on the diaphragm 36. Battery power would be required only when the settings were changed. The telemetry transmitter and receiver could be of the type presently used for transcutaneous signal transmission and are available commercially. Examples of such control circuitry are disclosed in U.S. Patent Nos. 4,373,527 and 4,146,029. Signal coding could be used to decrease the possibility of accidental operation. The receiver controls might be passive circuits that obtain their power from the transmitter since they would be activated only to change the pressure.
The regulator of the present invention is particularly suited to changing the reference pressure set point slowly due to the slow flow rate out of the infusion pump, and rapid changes in drug solution flow rate are not particularly suited for this design. The pressure control circuit would pr eferably be in the form of an adjustable basal rate rather than the flexible control used in other pumps that can be used to deliver fast bolus flows. This slow control greatly increases the safety of its operation.
The most compact design of an infusion pump ofthe present invention uses the outer shell structure of the infusion pump as a spring element that stores energy in the form of tension and compression of the metal or plastic material comprising the shell structure. The reference pressure for the regulator can be obtained from either the top or bottom of the pump in the form of a thin, large diameter diaphragm that separates the
pressure transmitting fluid from the body tissue. Figure 6 illustrates a possible packaging of the components of the embodiment illustrated in Figure 3. As with other infusion pumps, such as U.S. Patent No. 3,731,681, hereby incorporated by reference, the present invention will include an inlet port 60 and an outlet port 62. Suitably positioned in the inlet port 60 is a self-sealing, penetrable septum member 64, a filter 65 being positioned in the outlet port. A capillary flow restricter 66 is inter onnected to the outlet port by a suitable connecter 68. The capillary flow restrictor might then be interconnected to a catheter for delivery of the drugs to an infusion site in the body although any number of other well known devices might be used. A convoluted diaphragm 67 is utilized to allow nesting of the drug chamber diaphragm 26 therewith. (In this illustration, the regulator 34 is generally illustrated without any of its individual components.) The total force on the diaphragm 26 is opposed by the sum of the drug solution pressure in the drug chamber 22 and the support piston 32 fluid pressure:
FP + (PAAP) = (PSAS) + (PDAD) wherein ; FP =spring force of diaphragm PA =pressure of atmosphere
AP =area of diaphragm 26 PS =pressure of fluid in support piston
AS =area of support piston diaphragm. PD =pressure in drug chamber
AD =area of drug chamber diaphragm.
Regulation of the drug solution pressure (PD) occurs due to mechanical negative feedback action of the valve 40 so as to maintain a balanced force on the diaphragm 36. If the pressure (PD) of the drug solution drops, so does the regulator pressure (PR) which causes
the valve 40 to open to allow entry of more of the fluid from the support piston chamber which is at a high pressure (Ps). This is illustrated in Figure 8 wherein the valve 40 provides a larger opening 39 so as to allow more of the support solution in the support piston 32 to flow into the regulator reservoir 4. Figure 9 illustrates the valve 40 in a reduces flow setting wherein a smaller opening 37 is provide for drug solution flow. As illustrated in Figures 8 and 9, the valve 40 will preferably include a seal 35, such as an O-ring or the like. This restores the balance forces on the regulation diaphragm 36 by increasing regulator pressure (PR) . The control equations are:
PRAR - PAAR = FR wherein;
PR =pressure in regulation chamber AR =area of regulator diaphragm PA =pressure of atmosphere FR =spring force on regulator diaphragm The fluid storage chamber 42 has a soft bellows so the pressure (PD) is about equal to (PR). Therefore, the drug chamber pressure can be expressed as:
PDAR - PAAR = FR Solving for PD: PD = + PA
The flow through the capillary tube 66 is expressed in terms of the pressure difference across it divided by the fluid resistance:
wherein;
Q = flow in volume per unit time R = fluid resistance of capillary
Solving for Q putting in terms for the pressure PD:
RQ = PD - PA = + PA - PA
The two terms for atmospheric pressure cancel to give:
The regulator force (FR), the regulator diaphragm area (AR) and the capillary resistance R are fixed quantities, therefore, the flow Q will be fixed independent of the atmospheric pressure and the force on the drug chamber diaphragm 26. In a non-electronically controlled version of the infusion pump, the regulator force ( FR) might be preset by selecting a spring member 38 which creates the required force ( FR) . In Figure 7, another embodiment is illustrated wherein an adjustable force applicator 25 is utilized to apply a predetermined force (FR) on the diaphragm 36. It is to be understood that even though the above numerous characteristics and advantages of the invention have been set forth in the foregoing description, together with details of the structure and function of the invention, the disclosure is illustrative only, and changes may be in detail, especially in matter of shape, size and arrangement of parts with the principles of the invention to the full extent indicated by the broad general meaning of the terms in which the appended claims are expressed.
Claims
1. An infusion pump for implantation in a living body, comprising: a. a housing having a variable volume, drug chamber for holding a drug solution; b. outlet port means for conducting the drug solution from the drug chamber to a first site outside the housing; c. inlet port means for introducing the drug solution into the drug chamber from a second site outside the housing; d. force means including a diaphragm for exerting a force on the drug solution in the drug chamber; e. fluid piston means for opposing the force exerted by the diaphragm of the force means on the drug solution; and f . regulator means for regulating the pressure of the fluid of the piston means such that a constant total force is exerted on the drug solution in the drug chamber.
2. An infusion pump for implantation in a living body, comprising: a. a housing having a variable volume drug chamber for holding a drug solution; b. outlet port means for conducting the drug solution from the drug chamber to a first site outside the housing; c. inlet port means for introducing the drug solution into the drug chamber from a second site outside the housing;
d. first diaphragm means for exerting a force on the drug solution in the drug chamber; and e. regulator means for regulating the pressure of the drug solution, the regulator means including fluid piston means including a column of pressurized fluid for opposing the force of the first diaphragm means and second diaphragm means exerting a predetermined force on a second chamber of the housing so as to provide a reference pressure, the second chamber being in fluid communication and interconnected to the fluid piston means by one-way valve means for regulating fluid flow from the fluid piston means to the second chamber whereby a constant total force is exerted on the drug solution of the drug chamber, the fluid pressure of the second chamber corresponding to the fluid pressure of the drug chamber.
3. An infusion pump in accordance with claim
2, wherein the fluid of the second chamber and the fluid piston means is maintained separate from that of the drug solution.
4. An infusion pump in accordance with claim 2, wherein the fluid of the fluid piston means is the drug solution itself.
5. An infusion pump in accordance with claim 2, wherein the second diaphragm is enclosed by a rigid outer shell such that the force exerted by the second diaphragm on the second chamber remains constant regardless of atmospheric pressure changes.
6. An infusion pump in accordance with claim 2, wherein the second diaphragm is exposed to internal body pressure such that the force exerted by the second diaphragm on the fluid of the second chamber reflects changes in atmospheric pressure.
7. An infusion pump in accordance with claim 2, wherein the reference pressure of the regualtor means is electronically controlled.
8. An infusion pump in accordance with claim 2, wherein the regulator means is programmable so as to provide for varying the reference pressure and predetermined times.
9. An infusion pump for implantation in a living body, comprising: a. a housing having a first wall portion and a second wall portion defining a variable volume drug chamber for holding the drug solution; b. outlet port means for conducting the drug solution from the drug chamber to a first site outside the housing; c. inlet port means for introducing the drug solution into the drug chamber from a second site outside the housing; d. force means for forcing the second wall portion toward the first wall portion whereby the drug solution in the drug chamber is placed under pressure; e. regulator means for regulating the pressure of the drug solution in the drug chamber, and thus the infusion rate of the drug solution into the body, the regulator means including fluid piston means
interconnecting the first and second wall portions of the housing and including an enclosed column of fluid under pressure for opposing the force exerted by the second wall portion, the regulator means further including a regulator chamber in fluid communication with, and interconnected to, the fluid piston means by one-way valve means for allowing fluid flow from the fluid piston means into the regulator chamber, the regulator chamber being operatively interconnected to the drug chamber such that the pressure of the fluid in the regulator chamber and the drug solution pressure correspond, the regulator means being operated on by reference force means defining the operational drug solution pressure of the infusion pump.
10. An infusion pump in accordance with claim 8, wherein the reference force means is adjustable.
11. An infusion pump in accordance with claim 8, including electronic receiver means for receiving control signals transmitted from a location exterior of the body, the electronic receiver means being operatively interconnected to means for varying the reference force whereby the infusion rate of the implantable infusion pump can be electronically controlled.
12. A method of infusing fluids into a living body, the method comprising the following steps: a. implanting a self-powered infusion pump including a variable volume drug chamber into a living body, an inlet port leading to a variable volume drug chamber of the infusion pump; b. interconnecting an outlet port to at least one infusion site in the body;
c. injecting drug solution through skin of the body and through a self-sealing, penetrable member positioned in the inlet port to fill the drug chamber; and d. exerting a cumulative force on the drug solution in the drug chamber corresponding to the total force exerted by a first diaphragm means on the drug solution and an imposing force exerted by fluid piston means whose fluid pressure is controlled by pressure regulator means operatively interconnected to the fluid piston.
13. An infusion pump in accordance with claim 9, wherein the housing includes an external, flexible wall portion formed in part by the second wall portion.
14. An infusion pump in accordance with claim 1, wherein the housing includes an external wall structure, a first portion of the external wall structure being substantially rigid, the force means including movable spring diaphragm means forming a second portion of the external wall structure.
15. An infusion pump in accordance with claim 1, wherein the diaphragm forms an external wall portion of the housing so as to be subjected to the internal body pressure.
16. An infusion pump in accordance with claim 15, wherein the diaphragm includes a plurality of conical spring sections integral therewith.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DK521287A DK521287A (en) | 1986-02-03 | 1987-10-05 | IMPLANTABLE INFUSION PUMP AND PROCEDURE FOR INFUSION OF LIQUID |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US825,246 | 1986-02-03 | ||
US06/825,246 US4718893A (en) | 1986-02-03 | 1986-02-03 | Pressure regulated implantable infusion pump |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1987004629A1 true WO1987004629A1 (en) | 1987-08-13 |
Family
ID=25243500
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1987/000208 WO1987004629A1 (en) | 1986-02-03 | 1987-02-02 | Pressure regulated implantable infusion pump |
Country Status (8)
Country | Link |
---|---|
US (1) | US4718893A (en) |
EP (1) | EP0291510A4 (en) |
JP (1) | JPS63503359A (en) |
AU (1) | AU594269B2 (en) |
CA (1) | CA1262325A (en) |
DK (1) | DK521287A (en) |
IL (1) | IL81444A (en) |
WO (1) | WO1987004629A1 (en) |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE9016235U1 (en) * | 1990-11-29 | 1991-04-25 | Anschuetz & Co Gmbh, 2300 Kiel, De | |
WO2002036184A1 (en) | 2000-11-03 | 2002-05-10 | Endoart Sa | Implantable medical device for delivering a liquid |
US6635049B1 (en) | 1999-04-30 | 2003-10-21 | Medtronic, Inc. | Drug bolus delivery system |
WO2012103544A2 (en) | 2011-01-28 | 2012-08-02 | Brett Carter | Detachable drug delivery device |
WO2013153436A3 (en) * | 2012-04-12 | 2014-01-23 | Preciflex Sa | Compensated capillary indicator |
WO2013166038A3 (en) * | 2012-05-01 | 2015-06-18 | Nidus Medical, Llc | Peritoneal drain and infusion |
Families Citing this family (90)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4886514A (en) * | 1985-05-02 | 1989-12-12 | Ivac Corporation | Electrochemically driven drug dispenser |
US4772263A (en) * | 1986-02-03 | 1988-09-20 | Regents Of The University Of Minnesota | Spring driven infusion pump |
US4846806A (en) * | 1987-10-06 | 1989-07-11 | 501 Regents Of University Of Minnesota | Implantable intravascular access system |
US5006997A (en) * | 1987-12-15 | 1991-04-09 | Shiley Infusaid, Inc. | Pump diagnostic system |
US4931050A (en) * | 1988-04-13 | 1990-06-05 | Shiley Infusaid Inc. | Constant pressure variable flow pump |
US5222362A (en) * | 1989-01-10 | 1993-06-29 | Maus Daryl D | Heat-activated drug delivery system and thermal actuators therefor |
US5716343A (en) * | 1989-06-16 | 1998-02-10 | Science Incorporated | Fluid delivery apparatus |
US5067943A (en) * | 1989-09-26 | 1991-11-26 | Infusaid, Inc. | Pressure regulator for implantable pump |
US5120312A (en) * | 1990-04-20 | 1992-06-09 | Regents Of The University Of Minnesota | Method and apparatus for catheterization |
US5203770A (en) * | 1990-04-20 | 1993-04-20 | Regents Of The University Of Minnesota | Method and apparatus for catheterization |
USRE35501E (en) * | 1991-06-25 | 1997-05-06 | Medication Delivery Devices | Infusion pump, treatment fluid bag therefor, and method for the use thereof |
US5207645A (en) * | 1991-06-25 | 1993-05-04 | Medication Delivery Devices | Infusion pump, treatment fluid bag therefor, and method for the use thereof |
US5346476A (en) * | 1992-04-29 | 1994-09-13 | Edward E. Elson | Fluid delivery system |
US5308230A (en) * | 1993-03-08 | 1994-05-03 | Stainless Steel Products, Inc. | Bellows pump |
US5607418A (en) * | 1995-08-22 | 1997-03-04 | Illinois Institute Of Technology | Implantable drug delivery apparatus |
US5957890A (en) * | 1997-06-09 | 1999-09-28 | Minimed Inc. | Constant flow medication infusion pump |
US5957895A (en) * | 1998-02-20 | 1999-09-28 | Becton Dickinson And Company | Low-profile automatic injection device with self-emptying reservoir |
US8480580B2 (en) * | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) * | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6175752B1 (en) * | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US5957153A (en) * | 1998-09-18 | 1999-09-28 | Frey Turbodynamics, Ltd. | Oscillating dual bladder balanced pressure proportioning pump system |
US6132187A (en) * | 1999-02-18 | 2000-10-17 | Ericson; Paul Leonard | Flex-actuated bistable dome pump |
US7022107B1 (en) | 1999-09-22 | 2006-04-04 | Advanced Infusion, Inc. | Infusion pump with pressure regulator |
US6638263B1 (en) | 1999-10-12 | 2003-10-28 | Durect Corporation | Regulation of drug delivery through flow diversion |
US6589205B1 (en) * | 1999-12-17 | 2003-07-08 | Advanced Bionica Corporation | Externally-controllable constant-flow medication delivery system |
US6764472B1 (en) * | 2000-01-11 | 2004-07-20 | Bard Access Systems, Inc. | Implantable refillable infusion device |
US6592571B1 (en) | 2000-05-24 | 2003-07-15 | Medtronic, Inc. | Drug pump with suture loops flush to outer surface |
US6409698B1 (en) | 2000-11-27 | 2002-06-25 | John N. Robinson | Perforate electrodiffusion pump |
US6560471B1 (en) * | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
DE10106758A1 (en) * | 2001-02-14 | 2002-08-29 | Hilti Ag | Piston pump with filter pump |
US7041468B2 (en) * | 2001-04-02 | 2006-05-09 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
DE60317766T2 (en) * | 2002-04-09 | 2008-11-27 | Matsushita Electric Industrial Co., Ltd., Kadoma | HEALTH CARE SYSTEM AND METHODS FOR MAINTAINING HEALTH |
US7008403B1 (en) * | 2002-07-19 | 2006-03-07 | Cognitive Ventures Corporation | Infusion pump and method for use |
US20040068224A1 (en) * | 2002-10-02 | 2004-04-08 | Couvillon Lucien Alfred | Electroactive polymer actuated medication infusion pumps |
US7811231B2 (en) | 2002-12-31 | 2010-10-12 | Abbott Diabetes Care Inc. | Continuous glucose monitoring system and methods of use |
EP1622592A4 (en) * | 2003-03-27 | 2008-09-17 | Medical Res Products A Inc | Implantable medication delivery device using pressure regulator |
JP4565193B2 (en) * | 2003-04-23 | 2010-10-20 | バレリタス, インコーポレイテッド | Hydraulically operated pump for long duration pharmaceutical administration |
EP1635894B1 (en) * | 2003-06-25 | 2015-05-27 | Infusion Systems, LLC | Medication infusion device using negatively biased ambient pressure medication chamber |
US7367968B2 (en) * | 2003-09-05 | 2008-05-06 | Codman & Shurtleff, Inc. | Implantable pump with adjustable flow rate |
US8454324B2 (en) * | 2004-03-18 | 2013-06-04 | Precision Dispensing Systems Limited | Pump |
US9089636B2 (en) * | 2004-07-02 | 2015-07-28 | Valeritas, Inc. | Methods and devices for delivering GLP-1 and uses thereof |
US8114055B2 (en) | 2005-05-10 | 2012-02-14 | Palyon Medical (Bvi) Limited | Implantable pump with infinitely variable resistor |
US8915893B2 (en) | 2005-05-10 | 2014-12-23 | Palyon Medical (Bvi) Limited | Variable flow infusion pump system |
US8211060B2 (en) | 2005-05-10 | 2012-07-03 | Palyon Medical (Bvi) Limited | Reduced size implantable pump |
US7637892B2 (en) * | 2005-05-10 | 2009-12-29 | Palyon Medical (Bvi) Limited | Variable flow infusion pump system |
WO2006127508A2 (en) * | 2005-05-20 | 2006-11-30 | Wilson Greatbatch Technologies Inc. | Improved configuration for drug delivery systems |
US8002747B2 (en) * | 2005-05-26 | 2011-08-23 | The Alfred E. Mann Foundation For Scientific Research | Implantable infusion device with multiple controllable fluid outlets |
US7905878B2 (en) | 2005-10-31 | 2011-03-15 | Codman & Shurtleff, Inc. | Implantable pump with reservoir level detector |
US20070129678A1 (en) * | 2005-12-06 | 2007-06-07 | Medtronic, Inc. | Regulator |
US20070264130A1 (en) * | 2006-01-27 | 2007-11-15 | Phluid, Inc. | Infusion Pumps and Methods for Use |
EP2005309B1 (en) | 2006-03-30 | 2016-02-17 | Valeritas, Inc. | Multi-cartridge fluid delivery device |
US7920907B2 (en) * | 2006-06-07 | 2011-04-05 | Abbott Diabetes Care Inc. | Analyte monitoring system and method |
CA2657348C (en) * | 2006-07-11 | 2015-06-16 | Bernhard Frey | Cylinder piston arrangement for a fluid pump or a fluid engine |
US20080029173A1 (en) * | 2006-08-07 | 2008-02-07 | Diperna Paul Mario | Variable flow reshapable flow restrictor apparatus and related methods |
FR2905429A1 (en) * | 2006-09-04 | 2008-03-07 | Debiotech Sa | DEVICE FOR DELIVERING A LIQUID COMPRISING A PUMP AND A VALVE |
US8167832B2 (en) | 2006-12-09 | 2012-05-01 | The Alfred E. Mann Foundation For Scientific Research | Ambulatory infusion devices and methods including occlusion monitoring |
US20080147007A1 (en) * | 2006-12-19 | 2008-06-19 | Toby Freyman | Delivery device with pressure control |
US20090191067A1 (en) * | 2008-01-25 | 2009-07-30 | Phluid,Inc. | Two chamber pumps and related methods |
US8986253B2 (en) * | 2008-01-25 | 2015-03-24 | Tandem Diabetes Care, Inc. | Two chamber pumps and related methods |
US7867192B2 (en) * | 2008-02-29 | 2011-01-11 | The Alfred E. Mann Foundation For Scientific Research | Ambulatory infusion devices and methods with blockage detection |
EP2276525A4 (en) * | 2008-05-19 | 2012-04-04 | Tandem Diabetes Care Inc | Disposable pump reservoir and related methods |
US11078897B2 (en) * | 2008-06-27 | 2021-08-03 | Lynntech, Inc. | Apparatus for pumping fluid |
US9518577B2 (en) | 2008-06-27 | 2016-12-13 | Lynntech, Inc. | Apparatus for pumping a fluid |
ES2396748T3 (en) * | 2008-06-30 | 2013-02-25 | Animas Corporation | Volumetric Micropump |
US8056582B2 (en) * | 2008-08-08 | 2011-11-15 | Tandem Diabetes Care, Inc. | System of stepped flow rate regulation using compressible members |
US8408421B2 (en) * | 2008-09-16 | 2013-04-02 | Tandem Diabetes Care, Inc. | Flow regulating stopcocks and related methods |
US8650937B2 (en) * | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US8105269B2 (en) | 2008-10-24 | 2012-01-31 | Baxter International Inc. | In situ tubing measurements for infusion pumps |
US20100121274A1 (en) * | 2008-11-12 | 2010-05-13 | Baxter International Inc. | Prefillable constant pressure ambulatory infusion pump |
US8137083B2 (en) | 2009-03-11 | 2012-03-20 | Baxter International Inc. | Infusion pump actuators, system and method for controlling medical fluid flowrate |
US8721605B2 (en) | 2009-04-27 | 2014-05-13 | The Alfred E. Mann Foundation For Scientific Research | Implantable infusion devices with palpable landmarks and methods of needle detection |
CA2805030C (en) * | 2009-07-10 | 2020-05-05 | Milux Holding S.A. | Implantable lubrication device and method of treating a human or mammal patient by means of the device |
CA2769030C (en) * | 2009-07-30 | 2016-05-10 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8382447B2 (en) * | 2009-12-31 | 2013-02-26 | Baxter International, Inc. | Shuttle pump with controlled geometry |
US8567235B2 (en) | 2010-06-29 | 2013-10-29 | Baxter International Inc. | Tube measurement technique using linear actuator and pressure sensor |
JP2013125792A (en) * | 2011-12-13 | 2013-06-24 | Canon Inc | Holding device, drawing device, and method of manufacturing article |
US8568360B2 (en) | 2011-12-28 | 2013-10-29 | Palyon Medical (Bvi) Limited | Programmable implantable pump design |
US9180242B2 (en) | 2012-05-17 | 2015-11-10 | Tandem Diabetes Care, Inc. | Methods and devices for multiple fluid transfer |
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US9616207B2 (en) | 2014-06-26 | 2017-04-11 | Cochlear Limited | Treatment of the ear |
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EP3769719A1 (en) | 2019-07-23 | 2021-01-27 | National University of Ireland Galway | An implantable medical device |
Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3731681A (en) * | 1970-05-18 | 1973-05-08 | Univ Minnesota | Implantable indusion pump |
US3951147A (en) * | 1975-04-07 | 1976-04-20 | Metal Bellows Company | Implantable infusate pump |
US4056095A (en) * | 1975-04-04 | 1977-11-01 | Agence Nationale De Valorisation De La Recherche (Anvar) | Control device for medical and surgical uses |
US4299220A (en) * | 1979-05-03 | 1981-11-10 | The Regents Of The University Of Minnesota | Implantable drug infusion regulator |
US4447224A (en) * | 1982-09-20 | 1984-05-08 | Infusaid Corporation | Variable flow implantable infusion apparatus |
US4487603A (en) * | 1982-11-26 | 1984-12-11 | Cordis Corporation | Implantable microinfusion pump system |
US4557726A (en) * | 1982-12-27 | 1985-12-10 | Consolidated Controls Corporation | Precision medication dispensing system and method |
Family Cites Families (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
USRE24918E (en) * | 1949-10-07 | 1961-01-03 | Dispensing package and method | |
NL95211C (en) * | 1956-03-02 | 1900-01-01 | ||
US3023750A (en) * | 1959-03-04 | 1962-03-06 | Howard C Baron | Self-generating pressure device for infusion administration systems |
FR1314002A (en) * | 1961-11-24 | 1963-01-04 | Method and device for dispensing a non-compacted substance | |
GB1549402A (en) * | 1976-09-28 | 1979-08-08 | Pye Ltd | Apparatus for delivering fluids with controlled rate of flow |
US4373527B1 (en) * | 1979-04-27 | 1995-06-27 | Univ Johns Hopkins | Implantable programmable medication infusion system |
CA1237600A (en) * | 1983-05-31 | 1988-06-07 | Tatsuhei Kondo | Non-contact controlled micropump |
WO1985003232A1 (en) * | 1984-01-25 | 1985-08-01 | Imed Corporation | Hydraulic syringe drive |
-
1986
- 1986-02-03 US US06/825,246 patent/US4718893A/en not_active Expired - Lifetime
-
1987
- 1987-02-02 EP EP19870901802 patent/EP0291510A4/en not_active Withdrawn
- 1987-02-02 WO PCT/US1987/000208 patent/WO1987004629A1/en not_active Application Discontinuation
- 1987-02-02 JP JP62501339A patent/JPS63503359A/en active Pending
- 1987-02-02 IL IL81444A patent/IL81444A/en unknown
- 1987-02-02 AU AU70319/87A patent/AU594269B2/en not_active Ceased
- 1987-02-02 CA CA000528684A patent/CA1262325A/en not_active Expired
- 1987-10-05 DK DK521287A patent/DK521287A/en not_active Application Discontinuation
Patent Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3731681A (en) * | 1970-05-18 | 1973-05-08 | Univ Minnesota | Implantable indusion pump |
US4056095A (en) * | 1975-04-04 | 1977-11-01 | Agence Nationale De Valorisation De La Recherche (Anvar) | Control device for medical and surgical uses |
US3951147A (en) * | 1975-04-07 | 1976-04-20 | Metal Bellows Company | Implantable infusate pump |
US4299220A (en) * | 1979-05-03 | 1981-11-10 | The Regents Of The University Of Minnesota | Implantable drug infusion regulator |
US4447224A (en) * | 1982-09-20 | 1984-05-08 | Infusaid Corporation | Variable flow implantable infusion apparatus |
US4487603A (en) * | 1982-11-26 | 1984-12-11 | Cordis Corporation | Implantable microinfusion pump system |
US4557726A (en) * | 1982-12-27 | 1985-12-10 | Consolidated Controls Corporation | Precision medication dispensing system and method |
Non-Patent Citations (1)
Title |
---|
See also references of EP0291510A4 * |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE9016235U1 (en) * | 1990-11-29 | 1991-04-25 | Anschuetz & Co Gmbh, 2300 Kiel, De | |
US6635049B1 (en) | 1999-04-30 | 2003-10-21 | Medtronic, Inc. | Drug bolus delivery system |
WO2002036184A1 (en) | 2000-11-03 | 2002-05-10 | Endoart Sa | Implantable medical device for delivering a liquid |
WO2012103544A2 (en) | 2011-01-28 | 2012-08-02 | Brett Carter | Detachable drug delivery device |
EP2667917A2 (en) * | 2011-01-28 | 2013-12-04 | Calibra Medical, Inc. | Detachable drug delivery device |
EP2667917A4 (en) * | 2011-01-28 | 2014-08-27 | Calibra Medical Inc | Detachable drug delivery device |
AU2012211080B2 (en) * | 2011-01-28 | 2016-08-25 | Calibra Medical, Inc. | Detachable drug delivery device |
WO2013153436A3 (en) * | 2012-04-12 | 2014-01-23 | Preciflex Sa | Compensated capillary indicator |
CN104245013A (en) * | 2012-04-12 | 2014-12-24 | 普雷斯弗雷克斯股份公司 | Compensated capillary indicator |
US10815032B2 (en) | 2012-04-12 | 2020-10-27 | Preciflex Sa | Compensated capillary indicator |
WO2013166038A3 (en) * | 2012-05-01 | 2015-06-18 | Nidus Medical, Llc | Peritoneal drain and infusion |
Also Published As
Publication number | Publication date |
---|---|
AU594269B2 (en) | 1990-03-01 |
US4718893A (en) | 1988-01-12 |
DK521287D0 (en) | 1987-10-05 |
AU7031987A (en) | 1987-08-25 |
DK521287A (en) | 1988-08-04 |
IL81444A (en) | 1991-07-18 |
CA1262325A (en) | 1989-10-17 |
EP0291510A1 (en) | 1988-11-23 |
IL81444A0 (en) | 1987-09-16 |
EP0291510A4 (en) | 1989-08-16 |
JPS63503359A (en) | 1988-12-08 |
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