WO1989011302A1 - Infusion device with disposable elements - Google Patents
Infusion device with disposable elements Download PDFInfo
- Publication number
- WO1989011302A1 WO1989011302A1 PCT/US1989/002131 US8902131W WO8911302A1 WO 1989011302 A1 WO1989011302 A1 WO 1989011302A1 US 8902131 W US8902131 W US 8902131W WO 8911302 A1 WO8911302 A1 WO 8911302A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- follower
- tube
- pump
- cam
- administration set
- Prior art date
Links
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
- A61M5/14212—Pumping with an aspiration and an expulsion action
- A61M5/14228—Pumping with an aspiration and an expulsion action with linear peristaltic action, i.e. comprising at least three pressurising members or a helical member
-
- 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
-
- 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
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
-
- 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
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
- A61M5/16854—Monitoring, detecting, signalling or eliminating infusion flow anomalies by monitoring line pressure
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
- F04B43/082—Machines, pumps, or pumping installations having flexible working members having tubular flexible members the tubular flexible member being pressed against a wall by a number of elements, each having an alternating movement in a direction perpendicular to the axes of the tubular member and each having its own driving mechanism
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B49/00—Control, e.g. of pump delivery, or pump pressure of, or safety measures for, machines, pumps, or pumping installations, not otherwise provided for, or of interest apart from, groups F04B1/00 - F04B47/00
- F04B49/06—Control using electricity
- F04B49/065—Control using electricity and making use of computers
-
- 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
- A61M2205/60—General characteristics of the apparatus with identification means
- A61M2205/6018—General characteristics of the apparatus with identification means providing set-up signals for the apparatus configuration
-
- 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
- A61M2205/60—General characteristics of the apparatus with identification means
- A61M2205/6063—Optical identification systems
- A61M2205/6072—Bar codes
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B2203/00—Motor parameters
- F04B2203/02—Motor parameters of rotating electric motors
- F04B2203/0207—Torque
Definitions
- This invention relates generally to a medication infusion device for administering fluid to patients and more particularly to an improved, ambulatory infusion device with a disposable administration set which is inexpensive to manufacture, convenient to operate and which ensures fluid delivery at a consistent and uniform rate.
- medication dispensers and infusion devices are used for infusion of predetermined amounts of medication into the body of a patient.
- Various types of medication dispensers employing different techniques for a variety of applications are known to exist.
- Some existing infusion devices utilize a series of diaphragms which roll up and down inside cylinders in response to pistons located within the cylinders. Such devices, for example, as disclosed in U.S.
- Patents Nos. 4,236,880, 4,277,226, 4,391,600 and 4,410,322 are characterized by relatively complicated operational procedures and numerous manufacturing and maintenance adjustments to ensure proper operation of the loading and valving functions.
- the finger type displacement pump unit as disclosed in U.S. Patent 4,479,797 includes a plurality of elongate fingers which are depressed by an equal number of associated cams rotating about a shaft which is driven by a motor.
- a feeding tube when placed between the fingers, is squeezed by the fingers to infuse liquid medication into a human body.
- the elongate fingers comprise a central finger and two side fingers arranged o ⁇ either side.
- the side fingers completely squeeze or collapse the feeding tube at the designated point of contact on either side, and the central finger is shaped for squeezing the feeding tube and pumping medication over the length of tube between the two points, providing a pulsatile flow of fluid.
- the downstream side finger completely squeezes the feeding tube, while the pumping portion of the tube is filling from an upstream supply, the flow of fluid to the patient is completely obstructed.
- a disposable administration set including the pumping tube itself, a base plate against which the tube is depressed, and the cam followers.
- the system operates reliably and accurately over a longer period of time because its major pumping components are replaced with each use.
- Another important consideration for disposable elements is cost, since clinical application of disposable administration sets requires that the administration sets be regularly replaced. Typically, such sets are replaced every 24 to 48 hours, and seldom remain in use longer than one week. This frequent replacement interval should ideally be fulfilled by an inexpensively molded. disposable, mechanism which would normally not last the years of service life expected from the pump itself.
- occlusion detection system It is also desireable to have an efficient but inexpensive occlusion detection system.
- Some prior art devices incorporate a pressure transducer and diaphragm assembly to monitor fluid pressure as an indication of occlusion. Such an occlusion detection technique is undesirable in view of the complexities and cost involved.
- Prior art devices utilizing pistons and cylinders detect occlusion by utilizing a switch mounted within the cylinder. When the pressure reaches a certain value the rotating diaphragm causes the switch to be depressed. The switch may also be mounted against the tubing such that the switch is activated when the tubing expands as a result of increased pressure due to an occlusion. Summary of the Invention
- the present invention is an improved, ambulatory infusion device having a disposable administration set which is inexpensive to manufacture and a pumping mechanism which provides a consistent and uniform fluid flow.
- the infusion device comprises an administration set having a plurality of cam followers which are depressed in a predetermined sequence by a plurality of associated rotating cams.
- the cam followers squeeze a delivery tube to dispense fluid which is intravenously infused into a patient's body.
- the rotating cams are mounted to an axle shaft driven by a motor.
- the disposable administration set further comprises a plate assembly to which the ca followers are attached.
- the cam followers force th delivery tube against the plate assembly to pinch off th delivery tube or force fluid to flow through it.
- th administration set is advantageously disposable an inexpensive to manufacture.
- the cam followers are all molde together as one piece.
- the cam follower may also be molded as one piece with the plate assembly, provided that a hinge is molded to connect the ca followers with the plate assembly. This provides a cos effective assembling technique which allows the ca followers and plate to be replaced regularly at minima cost.
- the thickness o the cam followers is a critical dimension which directl affects the degree of tube compression, and thus the cross sectional area of the delivery tube. Because some variations in thickness can be expected from one molded part to the next due to normal molding process variations, the invention utilizes gap correction spacers which counteract these thickness variations.
- the gap correction spacers fit between the plate and the support for the rotating cam, and thus adjust the distance between the cam and the plate. If the cam follower assembly varies in thickness, for example due to change in the pressure of an injection molding machine, both the cam followers and the gap correction spacers vary by the same amount, because they are molded as a single unit.
- An additional feature of the invention allows the use of a low cost molded pressure plate assembly.
- Springs are used to force the face of the tubing retainer plate against the gap correction spacers. These springs, of course, must be stiff enough to be unyielding as the cams squeeze the delivery tube. By floating the plate on such springs, changes in thickness from plate to plate due to molding variations do not change the tubing gap from part to part. This is another important part of the invention which allows an easily loaded and inexpensive disposable administration set to be used without sacrificing performance or accuracy.
- the plate referencing system and the gap correction spacers described above are adapted to increase the accuracy of the delivery system.
- a channel in the pumping system receives the retainer plate and the spacers.
- the springs mentioned above are mounted in this channel and force the disposable assembly against a reference shoulder within the channel.
- This shoulder allows an easily manufactured dimensional precision to accurately define the tubing gap.
- the critical dimensions are the cam radius itself and the distance between the cam axis and the plate referencing shoulder. These two dimensions can be precisely controlled in the manufacturing process and they will not change significantly with time or usage.
- the pumping mechanism includes an axle shaft and a plurality of cams mounted thereto. As the axle shaft rotates, the cams force the cam followers -to squeeze the tubing and thereby displace a certain volume of fluid which is then forced out of the pump.
- the cams are structurally adapted such the each incremental angle of revolution displaces the same amount of fluid. This is facilitated by a non-linear cam design which provides a non-linear change in the delivery tube gap. The change in cross sectional area of the delivery tube caused by a given change in th gap depends on the tube gap at the start of the change.
- the cam non-linearity is designed to correlate with thi change.
- the present invention utilizes two pumping cams an two pumping cam followers, which function such that, at an point in time, one of the two pumping cams is alway pumping.
- the two pumping cams comprise a primary pumpin cam associated with an upstream segment of the deliver tube and a secondary pumping cam associated with downstream segment of the delivery tube.
- the primar pumping cam is wider than the secondary pumping cam, so that it can displace sufficient fluid during its pumping stroke to deliver fluid external to the pump and at the same time deliver fluid to the section of the tubing beneath the secondary pumping cam to allow it to fill.
- the secondary pumping cam is narrower, since it only needs to deliver fluid external to the pump.
- the present invention additionally utilizes pinching cams and pinching cam followers, which open and close the delivery tube to allow the pumping action to function properly.
- the pinching cams comprise an inlet pinching cam associated with the upstream segment of the tube and an outlet pinching cam associated with the downstream segment of the tube.
- the pumping cam followers acted upon by the pumping cams, control the rate of fluid flow, while the pinching cam followers acted upon by the pinching cams, operate as valves for the pump.
- Such a configuration allows one segment of the delivery tube to fill with fluid while another segment of the delivery tube is pumping, thus providing a continuous and uniform fluid flow.
- the disposable administration set of the infusion device is less prone to operator loading errors. This is accomplished through a reduced number of required operations and a reduction in the complexity of the operations. This is facilitated by providing channels extending along the length of the walls of a housing structure of the infusion device. These channels slidingly receive the disposable administration set in a simple, single insertion step. Additionally, since the disposable administration set includes the delivery tube retainer plate and cam followers, the position of the delivery tube relative to the tubing retainer plate and cam followers is established in a manufacturing operation which can be closely controlled. Assemblers are not under the stress of a clinical situation and they specialize in the proper assembly of the disposable administration set. Good manufacturing procedures provide additional checking systems to insure that the tubing is properly loaded and that the administration set properly assembled. These practices are not possible in a clinical environment.
- the pump of the infusion device is non-functional when loaded with an alien disposable administration set.
- Alien administration sets may have characteristics which are not suitable for safe operation of the fluid delivery system, and may operate outside of specified tolerance limits.
- the pump will not operate with a standard piece of delivery tube, because it requires an administration set with cam followers and a pressure plate.
- Another feature of the present invention is a provision for detecting an occlusion in the downstream fluid path.
- the cams which squeeze the tubing are rotated by a DC motor having a predictable torque-to-current transfer function.
- the amount of torque required to maintain a desired camshaft velocity can be measured.
- higher-than-normal pressure in the delivery tube can be sensed. If desired, a calculation can be made to determine the torque normally required to rotate the cam.
- This torque calculation takes into account the pressure exerted by the tube against the cam face, the effective radius of the cam- follower contact point, and the coefficient of friction o the cam-to-follower contact for each cam rotational position. This calculation is undertaken for each cam, to yield a total accumulated torque value. This total torque profile is stored in a memory device to be read out and compared with the actual torque for monitoring abnormally high pumping pressures.
- the memory may be loaded with actual D.C. current data read during a previous operation of the pump with normal pressure.
- This profile is unique to the particular mechanism and instrument in which it is installed.
- the profile is a current waveform sampled at specific angles of revolution of the pumping system.
- the waveform is sampled and stored during the actual operation of the pump under controlled conditions, i.e. specific output pressure, specific temperature, etc.. During later operation of the pump, these stored values are periodically compared to the actual operating current and an alarm is signalled if the difference between these two values exceeds a specified tolerance.
- the control system also has access to the current operating temperature which may be used to adjust the allowable tolerance for changes in the operating temperature.
- the control system may also have access to data stored on the disposable administration set which indicates particular information related to manufacturing variances, such as coefficient of friction, stroke volume, tubing gap, tubing wall thickness and diameter, etc. This information may also be used to determine the appropriate alarm point.
- the information may be stored on the disposable administration set so that it may be read by the instrument during the sliding operation of loading the set.
- the present invention uses a minimal number of parts and dissipates a minimal amount of energy.
- the disposable concept which includes the cam followers and the pressure plate allows for a high precision pump without complicated assembly or loading mechanisms.
- the set loading and retaining channels allow precise positioning of the tubing, followers, and pressure plate without any adjustments or complicated, bulky, or expensive mechanisms.
- the disposable administration set results in an overall fluid delivery system which is small, lightweight, and ambulatory.
- the design of the disposable administration set in combination with the plate referencing channels allows a sliding operation in order to load the set.
- This sliding operation allows for the transfer of information from the disposable administration set to the instrument from fixed sensors. These sensors may be optical, magnetic, or some other technology.
- the preferred embodiment uses optical sensors to read optically coded information from a label on the administration set. This capability permits tlie instrument to be programmed from the information included on the label. The instrument operator is thus free from programming tasks, which would be difficult in a clinical environment. Programming information can be added to the administration set during the preparation or prescription of the medication to be delivered.
- the unique sliding operation makes this programming simple and cost effective in the present invention. Brief Description of the Drawings
- Figure 1 is a perspective, exploded view illustrating an infusion device having a disposable administration set in accordance with the present invention, in particular showing the simple loading and unloading operation of the disposable administration set.
- Figure 2 is a perspective view illustrating the disposable administration set of the present invention.
- Figure 3 is a cross section view taken along the line 3-3 of Figure 1.
- Figure 4 is a plan view illustrating the single-piec cam of the invention.
- Figure 4a is a cross section view taken along the lin a-a of Figure 4 illustrating the contour of the outlet o secondary or downstream pumping cam of the presen invention.
- Figure 4b is a cross section view taken along the lin b-b of Figure 4 illustrating the contour of the outle pinching cam of the present invention.
- Figure 4c is a cross section view taken along the lin c-c of Figure 4 illustrating the contour of the inlet o primary or upstream pumping cam of the present invention.
- Figure 4d is a cross section view taken along the lin d-d of the present invention illustrating the contour o the inlet pinching cam of the present invention.
- Figure 5 is a plan view illustrating a cam followe and spacer assembly of the present invention.
- Figure 6 is a side elevation exploded vie illustrating the cam follower and spacer assembly and th plate assembly.
- Figure 7 is a graphical representation of the ca radii versus the angle of cam rotation of the presen invention.
- Figure 8 is a graphical representation of the tubin ID gap versus the angle of cam rotation of the presen invention.
- Figure 9 is a graphical representation of the tota torque versus the angle of cam rotation of the presen invention.
- Figure 10 is a block diagram of the occlusion detection system of the present invention.
- FIG. 1 illustrates the infusion device 10 of the preferred embodiment of the present invention for administering intravenous fluid at a consistent and uniform rate.
- the infusion device 10 is designed to be small, lightweight and ambulatory.
- the infusion device 10 includes a disposable administration set 12 having a plurality of cam followers 42 which are displaced in a predetermined sequence when depressed by a pumping mechanism 64 to squeeze a delivery tube 36 for dispensing fluid.
- the pumping mechanism 64 is driven by a commercially available motor 11 (not shown) .
- the disposable administration set 12 loads easily into the housing structure 66.
- an optional fluid reservoir 60 which provides a continuous flow of fluid to the inlet of the delivery tube.36 for dispensing and infusing fluid into a patient's body.
- the fluid delivery tube 36 may connect to an external reservoir (not shown) , or the reservoir 60 may be located at other positions on the assembly.
- the housing structure 66 comprises a rectangular chamber 67 surrounded by side walls 68 and a rear wall 69.
- the floor of the rectangular chamber 67 drops into a recess 70 towards the front end.
- the pumping mechanism 64 is located within the recess 70.
- Extending throughout the length and parallel to the base of each of the side walls 68 is a narrow channel 72 having a lower shoulder 73.
- the disposable administration set 12 slides within the channels 72.
- each of the channels 72 includes a spring-biased ball assembly 75.
- the disposable administration set 12 while being manually inserted into the channels 72, depresses the spring assemblies 75. After insertion of the set 12, the spring assemblies on either side bias the disposable administration set 12 against the shoulders 73 of the channels 72, holding the disposable administration set 12 accurately in position.
- the disposable administration set 12 is manually loaded into the infusion device 10 in a simple sliding operation. As the administration set 12 slides into the infusion device, the cam followers 42 are gradually pushed against the delivery tube 36 by the pumping mechanism 64.
- Figures 2 and 6 illustrate the disposabl administration set 12 of the preferred embodiment of th present invention.
- the disposable administration set 12 is formed from rigid plastic or the like, and includes a tubing retainer plate assembly 14 which may advantageously be injection molded as a single piece.
- the tubing retainer plate assembly 14 includes a tubing retainer plate 16 having a flat tube-contacting surface and a cam follower retainer 20 projecting normal to this surface at one end.
- the cam follower retainer 20 terminates in a an overhanging latch 24 projecting substantially parallel to the retainer plate 16.
- the latch 24 serves as a locking mechanism for holding the cam followers 42 in position, adjacent the tube 36 prior to insertion of the administration set 12 into the housing 66.
- the cam followers 42 are depressed by the pumping mechanism 64. This causes the cam followers 42 to move away from the latch 24.
- insertion of the administration set 12 automatically moves the cam followers from a standby position, against the latch 24, to an operating position pushed against the tube 36.
- the disposable administration set 12 further includes a cam follower and spacer assembly 40.
- the cam follower and spacer assembly 40 may also be injection molded as a single piece independent of the tubing retainer plate 16.
- the cam follower and spacer assembly 40 may be molded as one piece with the tubing retainer plate assembly 14 provided that a hinge is molded to connect the cam follower and spacer assembly 40 to the tubing retainer plate assembly 14.
- the cam follower and spacer assembly 40 includes two gap correction spacers 44 in the form of elongated extending finger-like projections which flank the tubing retainer plate 16 on either side (as best seen in Figure 2) .
- the thickness of the cam followers 42 is a critical dimension which directly effects the volume of the delivery tube 36.
- the accurate pinching of the delivery tube 36 is necessary to allow a desired flow of fluid through the available passage.
- the gap correction spacers 44 advantageously counteract for these thickness variations.
- the thickness of both the cam followers 42 and the gap spacers 44 will vary by the same amount, because they are formed in the same mold cavity. Thus, any molding variations, such as those due to mold temperature or pressure, will affect both of these parts identically.
- the gap correction spacer 44 rests between the plate 16 and the shoulder 73 (a ⁇ best seen in Figure 1) .
- the plate 16 will be positioned further from the cam 85 than normal.
- the cam followers 42 will also be thicker than normal, offsetting the effect of the thicker spacer 44. It is advantageous, in accomplishing this self correction, that the thickness of the spacer 44 be the same as that of the active part of the follower 42, so that they will vary identically in thickness.
- the plurality of cam followers 42 as best seen in Figure 5, includes an inlet pincher cam follower 43, a primary, upstream, inlet pumping cam follower 46, an outlet pincher cam follower 48, and a secondary, downstream, outlet pumping cam follower 50.
- Each of the cam follower 42 are attached to the cam follower and spacer assembly 4 by flexible cam follower arms 54.
- Each of the cam follower 42 are displaced toward the delivery tube 36 in predetermined sequence.
- the inlet pincher cam follower 43 and the outlet pincher cam follower 48 deform the fluid delivery tube 36 to close it off, and thus act as valves.
- the primary pumping cam follower 46 and the secondary pumping cam follower 50 pump the fluid through the delivery tube 36.
- the primary pumping cam follower 46 which contacts the upstream segment of the delivery tube 36 is approximately twice the width of the secondary pumping cam follower 50, and it thus squeezes twice the length of tubing. This facilitates displacement of enough fluid during a pumping stroke for delivering fluid external to the pump and at the same time delivering fluid to the downstream segment of the fluid delivery tube 36,beneath the follower 50, to allow it to fill.
- the follower 46 is being advanced toward the tube 36, the follower 50 is being withdrawn.
- the fluid displaced by the follower 46 fills the tube 36 as it is released by the follower 50, and also supplies enough fluid to continue the outflow from the pump.
- the pumping mechanism 64 which provides a continuous and uniform flow will be described.
- the pumping mechanism 64 comprises a cam assembly 84 and an axle shaft 86.
- the cam assembly 84 is preferably formed and machined from a single piece of metal.
- the cam assembly 84 may be cast, and later machined.
- the assembly 84 includes a central aperture 83 to accommodate an axle shaft 86.
- the shaft 86 may include a flat 86a to couple the shaft 86 to a motor.
- the axle shaft 86 rotates within bearings which are in turn mounted in two apertures formed within the walls 68 as best seen in Figure 1.
- the axle shaft 86 driven by the motor provides rotation to the cam assembly 84.
- the cam followers 42 subsequently are displaced in a predetermined sequence, as described below, thereby squeezing the delivery tube 36 and dispensing a specified volume of fluid.
- the cam assembly 84 is specifically designed such that each incremental angle of revolution displaces the same amount of fluid.
- the cam assembly 84 includes the plurality of spaced cams 85.
- the plurality of spaced cams 85 include an inlet pincher cam 87, a primary, upstream, inlet pumping cam 88, an outlet pincher cam 90 and a secondary, downstream, outlet pumping cam 92.
- the inlet pincher cam 87 and the primary pumping cam 88 are operably associated with the inlet pincher cam follower 43 and the primary pumping cam follower 46, respectively.
- the outlet pincher cam 90 and the secondary pumping cam 92 are likewise operably associated with the outlet pincher cam follower 48 and the secondary pumping cam follower 50.
- the inlet pincher cam 87 and outlet pincher cam 90 operate as valves for the pumping action.
- the surfaces of the pincher cams 87,90 are contoured such that between specified rotational positions either the upstream or the downstream segment of the tube 36 is pinched off to obstruct fluid flow.
- the primary pumping cam 88 and the secondary pumping cam 92 include active pumping surfaces which are uniquely contoured so that the fluid delivery tube 36 is squeezed in such a manner that a constant speed of rotation of the axle shaft 86 results in a uniform or constant displacement of fluid volume from the appropriate segment of the fluid delivery . tube 36.
- the equation defining the volume of an elliptical tub with g representing the inside edge diameter or minor ga and L representing the portion of the cam in contact wit the cam follower is as follows:
- V e ⁇ length x area - 1 x te x g x g/4 + L x g Since the circumference of the tube 36 remains relatively constant when the tubing is deformed from a cylindrical shape into an elliptical shape by the cam followers 42, the cylindrical circumference equals the elliptical circumference.
- each incremental area change will occur in 1.8" increments such that the g for the first incremental area will occur at 1.8 degrees, the g for the second incremental area will occur at 3.6 degrees, etc. Finally, the g for the 100th area will occur at 180 degrees.
- the cam radiuses at each increment can then be calculated by subtracting the required g value from the displacement between the center of the cam to the face of the plate assembly minus the cam follower thickness minus 2 times the tubing wall thickness plus the gap spacer thickness.
- the relationship between the cam radius and the tubing gap is algebraically proportional only when the cam radius in constant.
- the effect of the approximately horizontal surface of the follower, contacting the changing cam surface makes it necessary to take the phase and amplitude into consideration.
- a rapidly increasing cam surface results in a gap change that leads the actual radius change.
- a rapidly decreasing cam radius results in a gap change that lags the actual radius change.
- the amount of change in phase is a function of a ratio of the beginning and ending cam radii.
- the present invention utilizes approximate predicte phase changes based on calculations, of the ratio of th beginning and ending cam radii, relative to the rotationa positions of the cam. This effect is more significant i the case of the rapidly changing pincher cams which ar characterized by transitioning phase changes o approximately 35 degrees.
- the actual gaps are numerically computed as described.
- each radius has a vertical component which is computed by multiplying the actual radius length by the cosine of the angle that is formed by that radius relative to a vertical line.
- the vertical line passes through the center of the axle shaft and is approximately normal to the surface of the cam follower. The vertical component of each radius thus changes as the cam rotates about its axis.
- the cam follower Since the follower is formed to contact the cam surface in an approximately downward direction, for a particular degree of rotation of the cam, the cam follower will contact the cam surface at the radius which has the greatest positive vertical component.
- the actual radius of contact at each degree of rotation is determined by numerically computing the radius with the greatest vertical component at each degree of rotation.
- the cam assembly 84 rotates about the axle shaft 86 acts through the cam followers upon the delivery tube 36 positioned directly beneath the cam assembly 84.
- the inlet pincher cam 87 As best seen in Figure 7, between the rotational positions 0 degrees and 200, degrees the inlet pincher cam 87, indicated by a curve trace 87a, forces the inlet cam follower 43 to pinch off the upstream segment of the tube 36 to prevent fluid flow back into the reservoir 60. While the upstream segment of the tube 36 is pinched off, the primary pumping cam 88 progresses through a gradual pumping stroke lasting from 0 degrees to approximately 175 degrees, indicated by the curve 88a.
- the outlet pincher cam 90 closes and remains closed between the rotational angles 200 degrees to 340 degrees, indicated by the curve 90a. This forces the outlet cam
- the upstream segment of the tube 36 is completely pinched off between the rotational positions 340 degrees and 200 degrees.
- the primary pumping cam 88 reduces the gap beneath it to expel fluid until it reaches a rotational angle position of 175 degrees, as indicated by the curve 88b.
- the gap of the tube 36 beneath the cam 92 is gradually increased during this segment between 0 degrees and 180 degrees, so that the tube 36 beneath the secondary pumping cam 92 will slowly fill with fluid.
- the outlet pincher cam 90 causes the downstream segment to be pinched off as indicated by the curve 90b so that the secondary pumping cam 92 can deliver fluid external to the pump.
- the tubing gap beneath the cam 92 varies as indicated by the curve 92b during the pumping stroke (175 degrees to 360 degrees) of the secondary pumping cam 92.
- the total torque required from the motor to rotate the cam depends upon (1) the cam position, and (2) the back-pressure of the fluid being pumped.
- the lower curve 101 shows this total torque with low back pressure
- the curve 103 shows the torque required to pump at a relatively high back pressure.
- the curves of Figure 9 are derived empirically, or may be calculated. In either case when the cam followers 42 have pinched off the tube 36 and actually deform the wall thickness of the tube 36, a torque spike is required. When the tube 36 is released a reverse torque spike is generated. For example, at the rotational position of 200 degrees, when both the inlet pincher cam 87 and the outlet pincher cam 90 are pressed against the tube
- a torque spike 150 is observed.
- a negative spike 152 indicates the torque applied by the tube 36 as a result of the material deformation. If the cam 84 is rotated at a constant speed, the torque spikes of Figure 9 will result in current spikes in the DC current required for motor rotation.
- the DC motor 11 which rotates the axle shaft 86 has a predictable torque-to-current transfer function. By monitoring the current to the motor 11 for a proportional signal thereof, the amount of torque required to maintain a constant velocity of the axle shaft 86 can be measured. With knowledge of the motor current required to advance the pumping mechanism 64 at each position along its rotation, against a normal fluid back-pressure, and comparing this current with the actual measured current, higher-than-normal pressure in the delivery tube 36 can be sensed. A calculation can be made to determine the current normally required to rotate the pumping mechanism 64.
- This current calculation takes into account the pressure exerted by the delivery tube 36 against the cam faces, the effective radius of the cam-to-follower contacts for each cam rotational position. This calculation is undertaken for each cam, to yield a total accumulated torque value.
- the cam can be rotated against a normal back-pressure to empirically measure the current required for normal operation. This current waveform is proportional to the torque shown in Figure 9 as the curve 103.
- the current can be sensed for example at each 1 degree of rotation and stored in a memory 100.
- the actual current required to rotate the motor is monitored by a current sensor 104 and converted to digital format by an A/D converter 105 to be compared by a comparator 106 with the current profile stored in the memory device 100.
- a shaft encoder 101 is used to address the memory 100 to output the appropriate current level for a particular rotational position.
- the difference between the actual current and the stored current profile is subsequently compared with a reference constant indicating a critical situation which is stored in a memory 108.
- the memory 108 may provide the digital equivalent for the current increase which would be expected if the back pressure increased by 5 psi. This level may indicate the likelihood that th output is occluded and an alarm should be sounded. If th error signal from comparator 106 exceeds the referenc value, from the memory 108 a " comparator 110 automaticall may trigger an audio alarm means.
- the memory 108 may stor plural alarm levels which are applicable at differen temperatures. Thus, the allowable tolerance of th reference constant is temperature dependent.
- temperature may affect the pliability of the delivery tub 36, in which case, the reference constant may be adjuste to allow a larger divergence between expected current an actual current when the tube, is cold, and thus more rigid.
- the memory 108 may store a negative threshol reference which can be compared with the error signal i the comparator 110 to sense an abnormally low actua current. Occurrence of such an abnormally low curren indicates failure of the pumping system or associate abnormalities, such as failure to load a delivery tube 3 in the device. Abnormal wall thickness of the tube 36 would also be detected by an abnormal phase of the pinche current spike waveform. Additionally, damaged cam surfaces or faulty bearings or motor would contribute to abnormal behavior and thus would be detected.
- a bar code is advantageously applied to the disposable administration set as a means of directly transferring information regarding the disposable administration set such as the pump stroke volume which relates to the amount of fluid displaced per revolution of the axle shaft, tubing diameter, or the tubing wall thickness, from the disposable administration set to the infusion device 11.
- This information may be, for example, directly applied to the disposable administration set during the manufacturing process.
- the bar code may provide patient and medication specific information, relating to a particular prescription being delivered, such as a dose/time specification. This information likewise may be provided by a pharmacist with the disposable administration set. Using this information, a microprocessor can easily derive an appropriate shaft velocity.
- the sensor may be optical, or magnetic or some other known technology.
Abstract
An infusion device with a disposable administration set (12) which is inexpensive to manufacture. In the preferred embodiment of the present invention the disposable administration set has a plurality of elongated cam followers (42) connected to a plate assembly (14) wherein the cam followers are displaced in a predetermined sequence and force against a delivery tube (36) by cam means (85) driven by rotary drive means (11). The disposable administration set is injection molded as a single integral piece. The disposed administration set includes adjustment spacers (44) disposed between the plate assembly and the cam followers which adjust the distance between them to keep the device accurate. In the preferred embodiment of the present invention the cam means are configured to provide fluid delivery at a consistent and uniform rate.
Description
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INFUSION DEVICE WITH DISPOSABLE ELEMENTS Background of the Invention Field of the Invention
This invention relates generally to a medication infusion device for administering fluid to patients and more particularly to an improved, ambulatory infusion device with a disposable administration set which is inexpensive to manufacture, convenient to operate and which ensures fluid delivery at a consistent and uniform rate. Description of the Prior Art
As a result of the ongoing need for improved health care, there is a continuous effort with regard to administering intravenous fluid to patients. As is well known, medication dispensers and infusion devices are used for infusion of predetermined amounts of medication into the body of a patient. Various types of medication dispensers employing different techniques for a variety of applications are known to exist. Some existing infusion devices utilize a series of diaphragms which roll up and down inside cylinders in response to pistons located within the cylinders. Such devices, for example, as disclosed in U.S.
Patents Nos. 4,236,880, 4,277,226, 4,391,600 and 4,410,322 are characterized by relatively complicated operational procedures and numerous manufacturing and maintenance adjustments to ensure proper operation of the loading and valving functions.
Other existing infusion devices employ a finger type pump unit having fingers which are moved in predetermined sequence to squeeze a feeding tube to infuse predetermined amounts of medication continuously and cyclically into a patient. Such a prior art device is disclosed in U. S. Patent 4,479,797.
In many cases it is of critical importance to provide precisely controlled and consistent flow rates of intravenous fluid to patients. This need for more controlled IV flow rates is only partially fulfilled by the above-mentioned displacement pumps. The finger type
displacement pump unit as disclosed in U.S. Patent 4,479,797 includes a plurality of elongate fingers which are depressed by an equal number of associated cams rotating about a shaft which is driven by a motor. A feeding tube, when placed between the fingers, is squeezed by the fingers to infuse liquid medication into a human body. The elongate fingers comprise a central finger and two side fingers arranged oη either side. In such a device the side fingers completely squeeze or collapse the feeding tube at the designated point of contact on either side, and the central finger is shaped for squeezing the feeding tube and pumping medication over the length of tube between the two points, providing a pulsatile flow of fluid. During the time that the downstream side finger completely squeezes the feeding tube, while the pumping portion of the tube is filling from an upstream supply, the flow of fluid to the patient is completely obstructed.
Completely obstructing the flow of medication for periods of time and providing pulsatile flow is often a clinically unsatisfactory and undesirable condition since a patient is deprived of medication for periods of time. Additionally, fluid is delivered at non-uniform rates. Sometimes, the possibility exists at low flow rates for a catheter to develop a blood clot due to lack of flow. This may also result in an occluded tubing, so that the patient may be deprived of needed medication for several hours. This condition is especially likely in a home environment which seldom has around-the-clock clinical staffing for monitoring patients. Thus, it is desirable to have an infusion device which delivers fluid to a patient at a constant and uniform rate.
Some prior art devices, in an attempt to provide non pulsatile flow of fluid, incorporate additional pulsation correction cams and cam followers. The correction cams are designed to even out overall flow from the pump through simultaneous pumping actions of multiple cams. This solution is undesirable in view of the numerous parts
involved. Infusion devices utilizing piston valves and cylinders are also known to provide uniform flow; however, they do so at the expense of crude valving techniques and complex mechanisms. Thus it is desirable to have an infusion device utilizing a relatively simple technique of providing non-pulsatile flow.
As is well known, disposable equipment for medical applications is desirable so as to maintain a germ-free environment to prevent the transfer of infection especially where cost prohibits cleaning and sterilization after each use. Prior art devices employing a series of diaphragms rolling within cylinders have utilized disposable diaphragms. The disposable diaphragms, however, are flimsy and thus require a very complex loading mechanism. Prior art devices having finger type pump units, for example, as disclosed in U.S. Patent 3,658,445, have only a disposable tube assembly. This has limited advantages, since the cam followers, which are not a part of the disposable assembly, are not renewed with each replacement. U.S. Patent 4,479,797 discloses other disposable elements. Since the cam followers are repeatedly flexed and fatigued as a result of being depressed by the rotating cams, it is desirable to have them renewed with every new installation to ensure proper functioning. Thus, it is desirable to have a disposable administration set, including the pumping tube itself, a base plate against which the tube is depressed, and the cam followers. With such an arrangement, the system operates reliably and accurately over a longer period of time because its major pumping components are replaced with each use. Another important consideration for disposable elements is cost, since clinical application of disposable administration sets requires that the administration sets be regularly replaced. Typically, such sets are replaced every 24 to 48 hours, and seldom remain in use longer than one week. This frequent replacement interval should ideally be fulfilled by an inexpensively molded.
disposable, mechanism which would normally not last the years of service life expected from the pump itself.
Furthermore, it is desireable to have a disposable administration set which is easy to load and unload to minimize operator errors. These factors can be very important in a clinical situation when a few extra seconds may be critical to a patient's life. Typically, prior art devices require several steps to accomplish the task of loading and unloading. Additionally, it is beneficial to pinch off the delivery tube and obstruct fluid flow prior to loading or unloading the administration set.
It is also desireable to have an efficient but inexpensive occlusion detection system. Some prior art devices incorporate a pressure transducer and diaphragm assembly to monitor fluid pressure as an indication of occlusion. Such an occlusion detection technique is undesirable in view of the complexities and cost involved. Prior art devices utilizing pistons and cylinders detect occlusion by utilizing a switch mounted within the cylinder. When the pressure reaches a certain value the rotating diaphragm causes the switch to be depressed. The switch may also be mounted against the tubing such that the switch is activated when the tubing expands as a result of increased pressure due to an occlusion. Summary of the Invention
Briefly stated, the present invention is an improved, ambulatory infusion device having a disposable administration set which is inexpensive to manufacture and a pumping mechanism which provides a consistent and uniform fluid flow.
The infusion device comprises an administration set having a plurality of cam followers which are depressed in a predetermined sequence by a plurality of associated rotating cams. The cam followers squeeze a delivery tube to dispense fluid which is intravenously infused into a patient's body. The rotating cams are mounted to an axle shaft driven by a motor. The disposable administration set
further comprises a plate assembly to which the ca followers are attached. The cam followers force th delivery tube against the plate assembly to pinch off th delivery tube or force fluid to flow through it. In th preferred embodiment of the present invention th administration set is advantageously disposable an inexpensive to manufacture. In accordance with one featur of the present invention the cam followers are all molde together as one piece. Alternatively, the cam follower may also be molded as one piece with the plate assembly, provided that a hinge is molded to connect the ca followers with the plate assembly. This provides a cos effective assembling technique which allows the ca followers and plate to be replaced regularly at minima cost.
Since the cam followers are instrumental i controlling the amount of fluid dispensed, the thickness o the cam followers is a critical dimension which directl affects the degree of tube compression, and thus the cross sectional area of the delivery tube. Because some variations in thickness can be expected from one molded part to the next due to normal molding process variations, the invention utilizes gap correction spacers which counteract these thickness variations. The gap correction spacers fit between the plate and the support for the rotating cam, and thus adjust the distance between the cam and the plate. If the cam follower assembly varies in thickness, for example due to change in the pressure of an injection molding machine, both the cam followers and the gap correction spacers vary by the same amount, because they are molded as a single unit. Since an increase in thickness of the gap correction spacers results in an increase in the delivery tube gap, while an increase in the thickness of the cam followers results in a decrease in the delivery tube gap, the net effect is no change in the delivery tube gap. It is this correction technique that allows the followers to be injection molded without
sacrificing the accuracy of the fluid delivery.
An additional feature of the invention allows the use of a low cost molded pressure plate assembly. Springs are used to force the face of the tubing retainer plate against the gap correction spacers. These springs, of course, must be stiff enough to be unyielding as the cams squeeze the delivery tube. By floating the plate on such springs, changes in thickness from plate to plate due to molding variations do not change the tubing gap from part to part. This is another important part of the invention which allows an easily loaded and inexpensive disposable administration set to be used without sacrificing performance or accuracy.
The plate referencing system and the gap correction spacers described above are adapted to increase the accuracy of the delivery system. In cooperation with the gap correction spacers, a channel in the pumping system receives the retainer plate and the spacers. The springs mentioned above are mounted in this channel and force the disposable assembly against a reference shoulder within the channel. This shoulder allows an easily manufactured dimensional precision to accurately define the tubing gap. The critical dimensions are the cam radius itself and the distance between the cam axis and the plate referencing shoulder. These two dimensions can be precisely controlled in the manufacturing process and they will not change significantly with time or usage.
Another feature of the present invention exists in the ability to deliver fluid at a consistent and uniform rate. The pumping mechanism includes an axle shaft and a plurality of cams mounted thereto. As the axle shaft rotates, the cams force the cam followers -to squeeze the tubing and thereby displace a certain volume of fluid which is then forced out of the pump. The cams are structurally adapted such the each incremental angle of revolution displaces the same amount of fluid. This is facilitated by a non-linear cam design which provides a non-linear change in the delivery tube gap. The change in cross sectional
area of the delivery tube caused by a given change in th gap depends on the tube gap at the start of the change. The cam non-linearity is designed to correlate with thi change. The present invention utilizes two pumping cams an two pumping cam followers, which function such that, at an point in time, one of the two pumping cams is alway pumping. The two pumping cams comprise a primary pumpin cam associated with an upstream segment of the deliver tube and a secondary pumping cam associated with downstream segment of the delivery tube. The primar pumping cam is wider than the secondary pumping cam, so that it can displace sufficient fluid during its pumping stroke to deliver fluid external to the pump and at the same time deliver fluid to the section of the tubing beneath the secondary pumping cam to allow it to fill. The secondary pumping cam is narrower, since it only needs to deliver fluid external to the pump. The present invention additionally utilizes pinching cams and pinching cam followers, which open and close the delivery tube to allow the pumping action to function properly. The pinching cams comprise an inlet pinching cam associated with the upstream segment of the tube and an outlet pinching cam associated with the downstream segment of the tube. Thus the pumping cam followers, acted upon by the pumping cams, control the rate of fluid flow, while the pinching cam followers acted upon by the pinching cams, operate as valves for the pump. Such a configuration allows one segment of the delivery tube to fill with fluid while another segment of the delivery tube is pumping, thus providing a continuous and uniform fluid flow.
In still another feature of the present invention the disposable administration set of the infusion device is less prone to operator loading errors. This is accomplished through a reduced number of required operations and a reduction in the complexity of the operations. This is facilitated by providing channels extending along the length
of the walls of a housing structure of the infusion device. These channels slidingly receive the disposable administration set in a simple, single insertion step. Additionally, since the disposable administration set includes the delivery tube retainer plate and cam followers, the position of the delivery tube relative to the tubing retainer plate and cam followers is established in a manufacturing operation which can be closely controlled. Assemblers are not under the stress of a clinical situation and they specialize in the proper assembly of the disposable administration set. Good manufacturing procedures provide additional checking systems to insure that the tubing is properly loaded and that the administration set properly assembled. These practices are not possible in a clinical environment.
The pump of the infusion device is non-functional when loaded with an alien disposable administration set. Alien administration sets may have characteristics which are not suitable for safe operation of the fluid delivery system, and may operate outside of specified tolerance limits. The pump will not operate with a standard piece of delivery tube, because it requires an administration set with cam followers and a pressure plate.
Another feature of the present invention is a provision for detecting an occlusion in the downstream fluid path. The cams which squeeze the tubing are rotated by a DC motor having a predictable torque-to-current transfer function. By monitoring the current to the motor, the amount of torque required to maintain a desired camshaft velocity can be measured. With knowledge of the motor torque required to advance the cam at each position along its rotation, against a normal fluid back-pressure, and comparing this torque with the actual measured torque, higher-than-normal pressure in the delivery tube can be sensed. If desired, a calculation can be made to determine the torque normally required to rotate the cam. This torque calculation takes into account the pressure exerted by the
tube against the cam face, the effective radius of the cam- follower contact point, and the coefficient of friction o the cam-to-follower contact for each cam rotational position. This calculation is undertaken for each cam, to yield a total accumulated torque value. This total torque profile is stored in a memory device to be read out and compared with the actual torque for monitoring abnormally high pumping pressures.
Alternatively, the memory may be loaded with actual D.C. current data read during a previous operation of the pump with normal pressure. This profile is unique to the particular mechanism and instrument in which it is installed. The profile is a current waveform sampled at specific angles of revolution of the pumping system. The waveform is sampled and stored during the actual operation of the pump under controlled conditions, i.e. specific output pressure, specific temperature, etc.. During later operation of the pump, these stored values are periodically compared to the actual operating current and an alarm is signalled if the difference between these two values exceeds a specified tolerance.
The control system also has access to the current operating temperature which may be used to adjust the allowable tolerance for changes in the operating temperature. The control system may also have access to data stored on the disposable administration set which indicates particular information related to manufacturing variances, such as coefficient of friction, stroke volume, tubing gap, tubing wall thickness and diameter, etc. This information may also be used to determine the appropriate alarm point. The information may be stored on the disposable administration set so that it may be read by the instrument during the sliding operation of loading the set.
The present invention uses a minimal number of parts and dissipates a minimal amount of energy. The disposable concept which includes the cam followers and the pressure plate allows for a high precision pump without complicated
assembly or loading mechanisms. The set loading and retaining channels allow precise positioning of the tubing, followers, and pressure plate without any adjustments or complicated, bulky, or expensive mechanisms. The disposable administration set results in an overall fluid delivery system which is small, lightweight, and ambulatory.
The design of the disposable administration set in combination with the plate referencing channels allows a sliding operation in order to load the set. This sliding operation allows for the transfer of information from the disposable administration set to the instrument from fixed sensors. These sensors may be optical, magnetic, or some other technology. The preferred embodiment uses optical sensors to read optically coded information from a label on the administration set. This capability permits tlie instrument to be programmed from the information included on the label. The instrument operator is thus free from programming tasks, which would be difficult in a clinical environment. Programming information can be added to the administration set during the preparation or prescription of the medication to be delivered. The unique sliding operation makes this programming simple and cost effective in the present invention. Brief Description of the Drawings
The preferred embodiment of the present invention is illustrated in and by the following drawings in which like reference numerals indicate like parts and in which:
Figure 1 is a perspective, exploded view illustrating an infusion device having a disposable administration set in accordance with the present invention, in particular showing the simple loading and unloading operation of the disposable administration set.
Figure 2 is a perspective view illustrating the disposable administration set of the present invention.
Figure 3 is a cross section view taken along the line 3-3 of Figure 1.
Figure 4 is a plan view illustrating the single-piec cam of the invention.
Figure 4a is a cross section view taken along the lin a-a of Figure 4 illustrating the contour of the outlet o secondary or downstream pumping cam of the presen invention.
Figure 4b is a cross section view taken along the lin b-b of Figure 4 illustrating the contour of the outle pinching cam of the present invention. Figure 4c is a cross section view taken along the lin c-c of Figure 4 illustrating the contour of the inlet o primary or upstream pumping cam of the present invention.
Figure 4d is a cross section view taken along the lin d-d of the present invention illustrating the contour o the inlet pinching cam of the present invention.
Figure 5 is a plan view illustrating a cam followe and spacer assembly of the present invention.
Figure 6 is a side elevation exploded vie illustrating the cam follower and spacer assembly and th plate assembly.
Figure 7 is a graphical representation of the ca radii versus the angle of cam rotation of the presen invention.
Figure 8 is a graphical representation of the tubin ID gap versus the angle of cam rotation of the presen invention.
Figure 9 is a graphical representation of the tota torque versus the angle of cam rotation of the presen invention. Figure 10 is a block diagram of the occlusion detection system of the present invention.
Detailed Description of a Preferred Embodiment
Figure 1 illustrates the infusion device 10 of the preferred embodiment of the present invention for administering intravenous fluid at a consistent and uniform rate. The infusion device 10 is designed to be small, lightweight and ambulatory. The infusion device 10
includes a disposable administration set 12 having a plurality of cam followers 42 which are displaced in a predetermined sequence when depressed by a pumping mechanism 64 to squeeze a delivery tube 36 for dispensing fluid. The pumping mechanism 64 is driven by a commercially available motor 11 (not shown) . Mounted within a housing structure 66, the disposable administration set 12 loads easily into the housing structure 66. Oriented directly above the housing structure 66 is an optional fluid reservoir 60 which provides a continuous flow of fluid to the inlet of the delivery tube.36 for dispensing and infusing fluid into a patient's body. Alternatively, the fluid delivery tube 36 may connect to an external reservoir (not shown) , or the reservoir 60 may be located at other positions on the assembly.
The housing structure 66 comprises a rectangular chamber 67 surrounded by side walls 68 and a rear wall 69. The floor of the rectangular chamber 67 drops into a recess 70 towards the front end. The pumping mechanism 64 is located within the recess 70. Extending throughout the length and parallel to the base of each of the side walls 68 is a narrow channel 72 having a lower shoulder 73. The disposable administration set 12 slides within the channels 72. As best seen in Figure 3, each of the channels 72 includes a spring-biased ball assembly 75. The disposable administration set 12, while being manually inserted into the channels 72, depresses the spring assemblies 75. After insertion of the set 12, the spring assemblies on either side bias the disposable administration set 12 against the shoulders 73 of the channels 72, holding the disposable administration set 12 accurately in position. In operation, the disposable administration set 12 is manually loaded into the infusion device 10 in a simple sliding operation. As the administration set 12 slides into the infusion device, the cam followers 42 are gradually pushed against the delivery tube 36 by the pumping mechanism 64.
Figures 2 and 6 illustrate the disposabl administration set 12 of the preferred embodiment of th present invention. The disposable administration set 12 is formed from rigid plastic or the like, and includes a tubing retainer plate assembly 14 which may advantageously be injection molded as a single piece.
The tubing retainer plate assembly 14 includes a tubing retainer plate 16 having a flat tube-contacting surface and a cam follower retainer 20 projecting normal to this surface at one end. The cam follower retainer 20 terminates in a an overhanging latch 24 projecting substantially parallel to the retainer plate 16. The latch 24 serves as a locking mechanism for holding the cam followers 42 in position, adjacent the tube 36 prior to insertion of the administration set 12 into the housing 66. During insertion of the administration set 12 into the channels 72, the cam followers 42 are depressed by the pumping mechanism 64. This causes the cam followers 42 to move away from the latch 24. Thus insertion of the administration set 12 automatically moves the cam followers from a standby position, against the latch 24, to an operating position pushed against the tube 36.
As best seen in Figures 2, 5 and 6 the disposable administration set 12 further includes a cam follower and spacer assembly 40. In the preferred embodiment of the present invention the cam follower and spacer assembly 40 may also be injection molded as a single piece independent of the tubing retainer plate 16. Alternatively, the cam follower and spacer assembly 40 may be molded as one piece with the tubing retainer plate assembly 14 provided that a hinge is molded to connect the cam follower and spacer assembly 40 to the tubing retainer plate assembly 14. The cam follower and spacer assembly 40 includes two gap correction spacers 44 in the form of elongated extending finger-like projections which flank the tubing retainer plate 16 on either side (as best seen in Figure 2) . Since the cam followers 42 are instrumental in controlling the
amount of fluid dispensed, the thickness of the cam followers 42 is a critical dimension which directly effects the volume of the delivery tube 36. The accurate pinching of the delivery tube 36 is necessary to allow a desired flow of fluid through the available passage. However, due to typical molding process variations such accuracy may not be possible. The gap correction spacers 44 advantageously counteract for these thickness variations. During the molding process, the thickness of both the cam followers 42 and the gap spacers 44 will vary by the same amount, because they are formed in the same mold cavity. Thus, any molding variations, such as those due to mold temperature or pressure, will affect both of these parts identically.
Referring to Figure 3, it will be seen that, after insertion of the administration set 12 into the housing 66, the dispensing tube 36 is positioned immediately below ttie spring-biased retainer 75. The spring-biased retainer 75 holds the administration set accurately in place against the shoulders 73 (as best seen in Figure 1) as described earlier. The cam followers 42 are pushed against the tube 36 by a plurality of cams 85, one of which is shown in Figure 3. Pumping is accomplished, as will be described below, by squeezing the tube 36.
The gap correction spacer 44 rests between the plate 16 and the shoulder 73 (a≤ best seen in Figure 1) . Thus, if the spacer 44 is thicker than normal, the plate 16 will be positioned further from the cam 85 than normal. However, in this case, as explained above, the cam followers 42 will also be thicker than normal, offsetting the effect of the thicker spacer 44. It is advantageous, in accomplishing this self correction, that the thickness of the spacer 44 be the same as that of the active part of the follower 42, so that they will vary identically in thickness. The plurality of cam followers 42 as best seen in Figure 5, includes an inlet pincher cam follower 43, a primary, upstream, inlet pumping cam follower 46, an outlet
pincher cam follower 48, and a secondary, downstream, outlet pumping cam follower 50. Each of the cam follower 42 are attached to the cam follower and spacer assembly 4 by flexible cam follower arms 54. Each of the cam follower 42 are displaced toward the delivery tube 36 in predetermined sequence. The inlet pincher cam follower 43 and the outlet pincher cam follower 48 deform the fluid delivery tube 36 to close it off, and thus act as valves. The primary pumping cam follower 46 and the secondary pumping cam follower 50 pump the fluid through the delivery tube 36. The primary pumping cam follower 46 which contacts the upstream segment of the delivery tube 36 is approximately twice the width of the secondary pumping cam follower 50, and it thus squeezes twice the length of tubing. This facilitates displacement of enough fluid during a pumping stroke for delivering fluid external to the pump and at the same time delivering fluid to the downstream segment of the fluid delivery tube 36,beneath the follower 50, to allow it to fill. Thus, as the follower 46 is being advanced toward the tube 36, the follower 50 is being withdrawn. The fluid displaced by the follower 46 fills the tube 36 as it is released by the follower 50, and also supplies enough fluid to continue the outflow from the pump. Referring now to Figure 4, the pumping mechanism 64 which provides a continuous and uniform flow will be described. The pumping mechanism 64 comprises a cam assembly 84 and an axle shaft 86. In the preferred embodiment, the cam assembly 84 is preferably formed and machined from a single piece of metal. Alternatively, the cam assembly 84 may be cast, and later machined. As shown, the assembly 84 includes a central aperture 83 to accommodate an axle shaft 86. The shaft 86 may include a flat 86a to couple the shaft 86 to a motor. The axle shaft 86 rotates within bearings which are in turn mounted in two apertures formed within the walls 68 as best seen in Figure 1. The axle shaft 86 driven by the motor provides rotation
to the cam assembly 84. The cam followers 42 subsequently are displaced in a predetermined sequence, as described below, thereby squeezing the delivery tube 36 and dispensing a specified volume of fluid. The cam assembly 84 is specifically designed such that each incremental angle of revolution displaces the same amount of fluid. The cam assembly 84 includes the plurality of spaced cams 85. The plurality of spaced cams 85 include an inlet pincher cam 87, a primary, upstream, inlet pumping cam 88, an outlet pincher cam 90 and a secondary, downstream, outlet pumping cam 92. The inlet pincher cam 87 and the primary pumping cam 88 are operably associated with the inlet pincher cam follower 43 and the primary pumping cam follower 46, respectively. Similarly, the outlet pincher cam 90 and the secondary pumping cam 92 are likewise operably associated with the outlet pincher cam follower 48 and the secondary pumping cam follower 50.
Referring to Figures 4b and 4d the inlet pincher cam
87 and the outlet pincher cam 90 are described. The inlet pincher cam 87 and outlet pincher cam 90 operate as valves for the pumping action. The surfaces of the pincher cams 87,90 are contoured such that between specified rotational positions either the upstream or the downstream segment of the tube 36 is pinched off to obstruct fluid flow. Referring to Figures 4a and 4c, the primary pumping cam 88 and the secondary pumping cam 92 include active pumping surfaces which are uniquely contoured so that the fluid delivery tube 36 is squeezed in such a manner that a constant speed of rotation of the axle shaft 86 results in a uniform or constant displacement of fluid volume from the appropriate segment of the fluid delivery . tube 36. To accomplish this result, the primary pumping cam 88 and the secondary pumping cam 92 surfaces are contoured based upon the following principles and calculations. The equation defining the volume of a cylindrical tube with 1 representing the length and d the inside diameter is as follows:
VCyi = length x area = 1 x - d x d/4 The equation defining the volume of an elliptical tub with g representing the inside edge diameter or minor ga and L representing the portion of the cam in contact wit the cam follower is as follows:
Veϋ = length x area - 1 x te x g x g/4 + L x g Since the circumference of the tube 36 remains relatively constant when the tubing is deformed from a cylindrical shape into an elliptical shape by the cam followers 42, the cylindrical circumference equals the elliptical circumference. celi = ccyl Additionally the circumference of a cylinder and an ellipse are defined as CCyi — πd and Ceϋ = 2 x L + π x g, respectively.
Thus since the circumference remains constant throughout the deformation process of the delivery tube 36, the two circumferences may be equated as follows: π x d = 2 x L + π x g
+ JΓ x g x g/4 area ■ (*/2) x g x d - (π/4) x g x g considering that g = d as the total area displaced and breaking that total area into 100 equal area increments total area = π x d x d/4 and the incremental area change = «■ x d x /400 and then solving for the 100 g values corresponding to each of the 100 incremental area increments area 1 = (*/2) x g x d - (r/4) x g x g = -τ x d x d/ 0o
and solving for g given the constant cylinder d value and letting
K - - x d x d/400 for simplification and letting τr/4 = c for simplification 2 x c x d x g - c x g x g - k = 0 and solving for the second incremental area 2 x c x d x g - c x g x g - 2 x k = 0 and calculating the remaining 98 equal area increments. An incremental part of the cam rotation is selected for filling and the remaining part of the rotation will be for pumping. For example, if 180" is selected for pumping, then each incremental area change will occur in 1.8" increments such that the g for the first incremental area will occur at 1.8 degrees, the g for the second incremental area will occur at 3.6 degrees, etc. Finally, the g for the 100th area will occur at 180 degrees. The cam radiuses at each increment can then be calculated by subtracting the required g value from the displacement between the center of the cam to the face of the plate assembly minus the cam follower thickness minus 2 times the tubing wall thickness plus the gap spacer thickness.
Using this derivation, it is possible to generate the proper cam pumping profile for any combination of tube diameter, cam spacing, tube wall thickness, and cam-degrees of pumping rotation.
The relationship between the cam radius and the tubing gap is algebraically proportional only when the cam radius in constant. As the cam radius changes, the effect of the approximately horizontal surface of the follower, contacting the changing cam surface makes it necessary to take the phase and amplitude into consideration. For example, a rapidly increasing cam surface results in a gap change that leads the actual radius change. Likewise, a rapidly decreasing cam radius results in a gap change that lags the actual radius change. The amount of change in phase is a function of a ratio of the beginning and ending
cam radii.
The present invention utilizes approximate predicte phase changes based on calculations, of the ratio of th beginning and ending cam radii, relative to the rotationa positions of the cam. This effect is more significant i the case of the rapidly changing pincher cams which ar characterized by transitioning phase changes o approximately 35 degrees. Thus, once the cam profiles and approximate rotational positions of each cam are selected, the actual gaps are numerically computed as described. For each degree of rotation, each radius has a vertical component which is computed by multiplying the actual radius length by the cosine of the angle that is formed by that radius relative to a vertical line. The vertical line passes through the center of the axle shaft and is approximately normal to the surface of the cam follower. The vertical component of each radius thus changes as the cam rotates about its axis. Since the follower is formed to contact the cam surface in an approximately downward direction, for a particular degree of rotation of the cam, the cam follower will contact the cam surface at the radius which has the greatest positive vertical component. The actual radius of contact at each degree of rotation is determined by numerically computing the radius with the greatest vertical component at each degree of rotation.
Referring to Figures 4 and 7 the operation of the cams 85 relative to the gap of the delivery tube 36 will be described. The cam assembly 84, as seen in Figure 4, rotates about the axle shaft 86 acts through the cam followers upon the delivery tube 36 positioned directly beneath the cam assembly 84. As best seen in Figure 7, between the rotational positions 0 degrees and 200, degrees the inlet pincher cam 87, indicated by a curve trace 87a, forces the inlet cam follower 43 to pinch off the upstream segment of the tube 36 to prevent fluid flow back into the reservoir 60. While the upstream segment of the tube 36 is pinched off, the primary pumping cam 88 progresses through
a gradual pumping stroke lasting from 0 degrees to approximately 175 degrees, indicated by the curve 88a. This displaces the inlet pumping cam follower 46 against the tube 36 to squeeze enough fluid to the downstream 5 segment as well as external to the pump to continue to provide a uniform and consistent flow while the tube 36 beneath the secondary pumping cam 92 is filling. This filling is caused by a reduction in the diameter of the cam 92 through this rotational segment, as shown by curve 92a.
10. Once the downstream segment of the tube has been filled with fluid (at approximately the 180 degree rotation point) , the outlet pincher cam 90 closes and remains closed between the rotational angles 200 degrees to 340 degrees, indicated by the curve 90a. This forces the outlet cam
15 follower 48 to pinch off the downstream segment of the delivery tube 36. When the cam 90 pinches the tube 36 at approximately the 180 degree rotational position, the cam 87 rotates to a reduced diameter region which extends between approximately 220 degrees and 340 degrees. This
20 opens the tube 36 beneath the cam 87, as shown by curve 87a, to allow fluid to flow from the reservoir 60 to the portion of the tube 36 which underlies the cam 88, so that this tube portion may fill. This allows the upstream segment to fill in response to a gradual reduction in the
25 radius of the cam 88, as shown by the curve 88a between 220 degrees and 340 degrees. During this segment, the secondary pumping cam 92, indicated by the curve 92a, depresses the secondary cam follower 50 against the tube 36 dispensing fluid external to the pump.
30 Referring to Figure 8, the affect of the cams 85 on the tubing gap during their rotational movement is shown. The curves of Figure 8 are thus somewhat inversely proportional to the curves of Figure 7, since an increase in cam radii causes a decrease in the corresponding tube
35 gap, taking into account the fact that the gap change leads the actual radius change. The upstream segment of the tube 36, indicated by the curve 87b is completely pinched off
between the rotational positions 340 degrees and 200 degrees. The primary pumping cam 88, as described above, reduces the gap beneath it to expel fluid until it reaches a rotational angle position of 175 degrees, as indicated by the curve 88b. The gap of the tube 36 beneath the cam 92 is gradually increased during this segment between 0 degrees and 180 degrees, so that the tube 36 beneath the secondary pumping cam 92 will slowly fill with fluid.
Once the downstream segment of the tube 36 has been filled, the outlet pincher cam 90 causes the downstream segment to be pinched off as indicated by the curve 90b so that the secondary pumping cam 92 can deliver fluid external to the pump. The tubing gap beneath the cam 92 varies as indicated by the curve 92b during the pumping stroke (175 degrees to 360 degrees) of the secondary pumping cam 92.
Referring to Figure 9, it can be seen that the total torque required from the motor to rotate the cam depends upon (1) the cam position, and (2) the back-pressure of the fluid being pumped. The lower curve 101 shows this total torque with low back pressure, while the curve 103 shows the torque required to pump at a relatively high back pressure. The curves of Figure 9 are derived empirically, or may be calculated. In either case when the cam followers 42 have pinched off the tube 36 and actually deform the wall thickness of the tube 36, a torque spike is required. When the tube 36 is released a reverse torque spike is generated. For example, at the rotational position of 200 degrees, when both the inlet pincher cam 87 and the outlet pincher cam 90 are pressed against the tube
36, a torque spike 150 is observed. A negative spike 152 indicates the torque applied by the tube 36 as a result of the material deformation. If the cam 84 is rotated at a constant speed, the torque spikes of Figure 9 will result in current spikes in the DC current required for motor rotation.
Referring to Figure 10, a block diagram of the
occlusion detection system used in the infusion device 10 will be described. The DC motor 11 which rotates the axle shaft 86 has a predictable torque-to-current transfer function. By monitoring the current to the motor 11 for a proportional signal thereof, the amount of torque required to maintain a constant velocity of the axle shaft 86 can be measured. With knowledge of the motor current required to advance the pumping mechanism 64 at each position along its rotation, against a normal fluid back-pressure, and comparing this current with the actual measured current, higher-than-normal pressure in the delivery tube 36 can be sensed. A calculation can be made to determine the current normally required to rotate the pumping mechanism 64. This current calculation takes into account the pressure exerted by the delivery tube 36 against the cam faces, the effective radius of the cam-to-follower contacts for each cam rotational position. This calculation is undertaken for each cam, to yield a total accumulated torque value. Alternatively, the cam can be rotated against a normal back-pressure to empirically measure the current required for normal operation. This current waveform is proportional to the torque shown in Figure 9 as the curve 103. The current can be sensed for example at each 1 degree of rotation and stored in a memory 100. During subsequent clinical use of the pump, the actual current required to rotate the motor is monitored by a current sensor 104 and converted to digital format by an A/D converter 105 to be compared by a comparator 106 with the current profile stored in the memory device 100. A shaft encoder 101 is used to address the memory 100 to output the appropriate current level for a particular rotational position. The difference between the actual current and the stored current profile, is subsequently compared with a reference constant indicating a critical situation which is stored in a memory 108. For example, the memory 108 may provide the digital equivalent for the current increase which would be expected if the back pressure increased by 5
psi. This level may indicate the likelihood that th output is occluded and an alarm should be sounded. If th error signal from comparator 106 exceeds the referenc value, from the memory 108 a" comparator 110 automaticall may trigger an audio alarm means. The memory 108 may stor plural alarm levels which are applicable at differen temperatures. Thus, the allowable tolerance of th reference constant is temperature dependent. For example, temperature may affect the pliability of the delivery tub 36, in which case, the reference constant may be adjuste to allow a larger divergence between expected current an actual current when the tube, is cold, and thus more rigid. Additionally, the memory 108 may store a negative threshol reference which can be compared with the error signal i the comparator 110 to sense an abnormally low actua current. Occurrence of such an abnormally low curren indicates failure of the pumping system or associate abnormalities, such as failure to load a delivery tube 3 in the device. Abnormal wall thickness of the tube 36 would also be detected by an abnormal phase of the pinche current spike waveform. Additionally, damaged cam surfaces or faulty bearings or motor would contribute to abnormal behavior and thus would be detected.
In the preferred embodiment of the present invention a bar code is advantageously applied to the disposable administration set as a means of directly transferring information regarding the disposable administration set such as the pump stroke volume which relates to the amount of fluid displaced per revolution of the axle shaft, tubing diameter, or the tubing wall thickness, from the disposable administration set to the infusion device 11. This information may be, for example, directly applied to the disposable administration set during the manufacturing process. Alternatively, the bar code may provide patient and medication specific information, relating to a particular prescription being delivered, such as a dose/time specification. This information likewise may be
provided by a pharmacist with the disposable administration set. Using this information, a microprocessor can easily derive an appropriate shaft velocity. The sensor may be optical, or magnetic or some other known technology.
Claims
1. A device for pumping fluid, comprising:
A) a disposable administration set, comprising:
1) at least one follower; and 2) a gap correction spacer formed integrally with said follower;
B) a delivery tube disposed adjacent said follower; and
C) a pumping mechanism comprising: 1) an actuator adjacent said follower, said actuator contacting said follower to force said follower to squeeze a portion of said delivery tube by an amount which is regulated by said gap correction spacer.
2. A device as defined in Claim 1, wherein said follower gradually advances a first wall of said portion toward a second wall.
3. A device as defined in Claim 1, wherein said disposable administration set further comprises a pressure plate, and wherein said second wall contacts said pressure plate.
4. A device as defined in Claim 3, wherein said follower, spacer, and pressure plate are formed as one integral piece.
5. A device as defined in Claim 3, wherein said follower and spacer are connected to said pressure plate by a hinge, said follower, spacer, pressure plate and hinge formed as one integral piece.
6. A device as defined in Claim 3, wherein said gap correction spacer adjusts the distance between said pressure plate and said follower.
7. A device as defined in Claim 1, additionally comprising a plurality of said actuators and a plurality of said followers, comprising: a primary pumping actuator positioned adjacent a first follower which is adjacent an upstream section of said delivery tube, and a secondary pumping actuator positioned adjacent a second follower which is adjacent a downstream section of said delivery tube.
8. A device as defined in Claim 7, wherein said first follower has a width which is twice the width of said second follower.
9. A device as defined in Claim 7, additionally comprising: an inlet pincher actuator; an outlet pincher actuator; a third follower associated with said inlet pincher actuator; and a fourth follower associated with said outlet pincher actuator.
10. A device as defined in Claim 1, additionally comprising: a housing, comprising: a channel; and a spring, said spring forcing said disposable administration set against one side of said channel.
11. A device as defined in Claim 10, wherein said spring forces said gap correction spacer against said one side of said channel.
12. A device as defined in Claim 1, additionally comprising: means for monitoring the actual force generated by said pumping mechanism; and means for comparing said force with an •expected force level to determine whether said delivery tube is occluded.
13. A device as defined in claim 12, wherein said means for comparing comprises: means for storing the value of force expected to be generated by said pumping mechanism, a comparator for subtracting said expected force from said actual force to provide a difference value, and means for comparing said difference value with a alarm value to monitor for occlusion of said delivery tube.
14. A disposable administration set for use with a pum for dispensing fluid through a delivery tube, sai disposable administration set comprising: a follower for pressing against a portion of said tub in response to operation of said pump, and an adjustment spacer for positioning said tub relative said pump, variations in the thickness of sai follower being offset by variations in the thickness o said adjustment spacer, said adjustment spacer forme integral with said follower.
15. A disposable administration set as defined i Claim 14, additionally comprising a pressure plat connected to said follower said pressure plate, adjustmen spacer, and follower all formed as a single, integral unit.
16. A device as defined in Claim 15, wherein sai adjustment spacer adjusts the distance between sai pressure plate and said pump.
17. A device as defined in Claim 16, additionall comprising a plurality of said followers, comprising: a primary follower which is adjacent an upstrea section of said delivery tube, and a secondary follower which is adjacent a downstrea section of said delivery tube.
18. A device as defined in Claim 17, wherein said primar follower has a width which is twice the width of sai secondary follower.
19. A device as defined in Claim 17, additionally comprising: an inlet pincher follower; and an outlet pincher follower.
20. A method of adjusting the gap within a delivery tube of a pump, wherein the pump includes an actuator for pressing a follower against a portion of said tube to narrow said gap, said method comprising: forming a spacer integral with said follower, so that thickness variations of said follower will be matched by thickness variations of said spacer; and positioning said spacer in said pump to separate a lower wall of said tube from said actuator.
21. A method as defined in Claim 20, wherein said forming step comprises: injection molding said spacer and said follower in a single mold cavity.
22. A method as defined in Claim 20, wherein said forming step includes the step of forming a pressure plate, and wherein said forming step further comprises: connecting said pressure plate to said spacer with a hinge, and forming said follower, spacer, pressure plate and hinge as one integral piece.
23. A method as defined in Claim 22, wherein said forming step comprises: injection molding said follower, spacer, pressure plate and hinge.
24. A method as defined in Claim 20, additionally comprising: forming a plurality of said actuators and a plurality of said followers, and pressing a first of said plural actuators against a first of said followers to squeeze an upstream section of said delivery tube, and pressing a second of said plural actuators against a second of said followers to squeeze a downstream section of said, delivery tube.
25. A method as defined in Claim 24, wherein said first pressing step squeezes an upstream section of said delivery tube which has a width which is twice the width of said downstream section of said delivery tube squeezed in said second pressing step.
26. A method as defined in Claim 24, additionally comprising: pressing an inlet actuator against a third follower t close said tube upstream of said first of said followers; and pressing an outlet actuator against a fourth followe to close said tube between said first and second followers.
27. A method as defined in Claim 20, additionall comprising: providing a housing having a channel for supporting said tube, and biasing said tube for accurate positioning relative to one surface of said channel with a spring.
28. A method as defined in Claim 26, wherein said biasing step comprises: forcing said spacer against said one surface of said channel.
29. A method as defined in Claim 20, additionally comprising: monitoring the actual force generated by said pump; and comparing said force with an expected force level to determine whether said delivery tube is occluded.
30. A method as defined in Claim 29, wherein said comparing step comprises: storing the value of force expected to be generated by said pump at plural rotational positions, subtracting said expected force from said actual force to provide a difference value for each of said plural rotational positions, and comparing said difference values with an alarm value to monitor for occlusion of said delivery tube.
31. A method as defined in Claim 30, additionally comprising: adjusting said alarm value in accordance with temperature.
32. A method as defined in Claim 30, additionally comprising: comparing said difference value with a second alarm value to monitor pump failure.
33. A method for loading a disposable administration set within a pump housing comprising: sliding said disposable administration set within 5 a channel formed in the housing, and simultaneously urging said disposable administration set against one surface of said channel to accurately position said disposable administration set relative to said pump housing. 103
34... A- method as defined in Claim 33, wherein said disposable, administration set includes a tube which is squeezed by a pump, wherein said urging step comprises: biasing said tube toward said pump.
35. A method as defined in Claim 34, wherein said 15 disposable administration set includes a spacer, and wherein said urging step forces said spacer against said one surface.
36. A method of programming a pump for cooperation with a disposable administration set comprising:
20 sliding said disposable administration set within a channel formed in said pump, and simultaneously transferring coded data regarding said disposable administration set from said administration set to said pump, and 25 storing said data in said pump.
37. A method as defined in Claim 36, wherein said transferring step comprises: optically reading a bar code from an administration set label. 30
38. Am apparatus for pumping fluid at a uniform rate, comprising: a delivery tube; an upstream cam positioned over an upstream portion of said delivery tube; 35.-. a. downstream cam positioned over a downstream portion of said delivery tube; a first valve for closing said tube between said upstream portion and said downstream portion; a second valve for closing said tube upstream of said upstream portion; said downstream cam configured to pump fluid at a first rate when said first valve is closed and said second valve is open; said upstream cam configured to pump fluid at a second rate when said second valve is closed and said first valve is open; said downstream cam configured to draw fluid into said downstream portion of said tube at a third rate when said second valve is closed and said first valve is open; said second rate equal to the sum of said first and third rates.
39. An apparatus as defined in Claim 38, wherein said first valve comprises: a cam for pinching said tube to close.
40. An apparatus as defined in Claim 39, wherein said second valve comprises: a cam for pinching said tube to close.
41. A method for pumping fluid from a tube at a uniform rate in a pump which includes an upstream pumping cam and a downstream pumping cam positioned to squeeze said tube, said tube including two valves, one between said pumping cams, and one upstream of both of said pumping cams, comprising: squeezing fluid from said tube adjacent said downstream cam at a first rate when said first valve is closed and said second valve is open; squeezing fluid from said tube adjacent said upstream cam at a second rate when said second valve is closed and said first valve is open; drawing fluid into said tube adjacent said downstream cam at a third rate when said second valve is closed and said first valve is open, said third rate equal to the difference between said second rate and said first rate.
42. A method of shaping the contour of a cam to squeeze fluid from a tube at a uniform rate, comprising: calculating the differential volume of said tube caused by an incremental decrease in the width of said tube at each of plural tube widths; calculating the radius of a cam at each of plural, equally spaced angular positions, to provide an incremental decrease in the width of said tube which, at the tube's , current width, will provide identical differential volumes, and shaping the contour of said cam in accordance with the radius calculated for each of said plural, equally spaced angular positions.
44. A method of sensing occlusion in a tube which conducts fluid from a pump, comprising: operating said pump to pump fluid through said tube at a normal pressure level, measuring the current required to operate said pump at said normal pressure level, and recording said current as a function of rotational position of said pump, and comparing the current required to operate said pump at an unknown pressure with said recorded current, as a function of the rotational position of said pump, to monitor unexpectedly high current.
45. A device for pumping fluid, comprising: a disposable administration set having at least one follower; a delivery tube disposed adjacent said follower; a pumping mechanism having a non-disposable actuator adjacent said follower, said actuator contacting said follower to force said follower to squeeze a portion of said delivery tube.
46. A device as defined in Claim 45, wherein said disposable administration set further comprises a pressure plate, said follower and pressure plate formed as one integral piece.
47. A method of programming a pump for cooperation with a disposable administration set comprising: sliding said disposable administration set within a channel formed in said pump, and simultaneously transferring coded data regarding a prescribed infusion profile from said administration set to said pump, and storing said data in said pump.
48. A method of detecting an operating condition in an infusion device resulting from a malfunction, comprising: empirically determining an expected force required to operate a pump for increments of one revolution for said operating condition; storing said expected force; comparing an actual operating force with said stored expected force; and generating an indication in response to said comparison to indicate said operating condition to the user.
49. A method as defined in Claim 48, wherein said determining step determines an expected electrical current, said storing step stores said expected electrical current, and said comparing step compares an actual electrical current with said stored expected electrical current.
50. A method as defined in Claim 48, wherein said indicator is an audible alarm.
51. A method as defined in Claim 48, wherein said indicator is a visual display.
52. A method of programming a pump for cooperation with a disposable administration set comprising: sliding said disposable administration set within a channel formed in said pump, and simultaneously transferring coded data regarding a specific characteristic of said disposable administration set to said pump, and storing said data in said pump.
53. A method as defined in Claim 52, wherein said specific characteristic is a tubing diameter.
54. A method as defined in Claim 52, wherein said specific characteristic is a tubing wall thickness.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP89906892A EP0418306B1 (en) | 1988-05-17 | 1989-05-17 | Infusion device with disposable elements |
DE68916643T DE68916643T2 (en) | 1988-05-17 | 1989-05-17 | INFUSION ARRANGEMENT WITH DISPOSABLE ELEMENTS. |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US194,865 | 1988-05-17 | ||
US07/194,865 US5074756A (en) | 1988-05-17 | 1988-05-17 | Infusion device with disposable elements |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1989011302A1 true WO1989011302A1 (en) | 1989-11-30 |
Family
ID=22719181
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1989/002131 WO1989011302A1 (en) | 1988-05-17 | 1989-05-17 | Infusion device with disposable elements |
Country Status (9)
Country | Link |
---|---|
US (3) | US5074756A (en) |
EP (1) | EP0418306B1 (en) |
JP (1) | JPH03504208A (en) |
AT (1) | ATE108070T1 (en) |
AU (1) | AU633004B2 (en) |
CA (1) | CA1322924C (en) |
DE (1) | DE68916643T2 (en) |
NZ (1) | NZ228977A (en) |
WO (1) | WO1989011302A1 (en) |
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---|---|---|---|---|
US5011378A (en) * | 1988-07-08 | 1991-04-30 | I-Flow Corporation | Pump tube mount and cartridge for infusion pump |
US5131816A (en) * | 1988-07-08 | 1992-07-21 | I-Flow Corporation | Cartridge fed programmable ambulatory infusion pumps powered by DC electric motors |
US5201636A (en) * | 1991-02-19 | 1993-04-13 | Milton Roy Company | Stator current based malfunction detecting system in a variable flow delivery pump |
AU739019B2 (en) * | 1996-04-10 | 2001-10-04 | Baxter International Inc. | A method of loading a tube into a volumetric infusion pump |
US7471994B2 (en) | 1992-10-15 | 2008-12-30 | The General Hospital Corporation | Infusion pump with an electronically loadable drug library and label reader |
US8864739B2 (en) | 1998-10-29 | 2014-10-21 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
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US9011371B2 (en) | 1998-10-29 | 2015-04-21 | Medtronic Minimed, Inc. | Method and apparatus for detecting occlusions in an ambulatory infusion pump |
US9463280B2 (en) | 2012-03-26 | 2016-10-11 | Medimop Medical Projects Ltd. | Motion activated septum puncturing drug delivery device |
US9744297B2 (en) | 2015-04-10 | 2017-08-29 | Medimop Medical Projects Ltd. | Needle cannula position as an input to operational control of an injection device |
US10335545B2 (en) | 2012-01-31 | 2019-07-02 | West Pharma. Services IL, Ltd. | Time dependent drug delivery apparatus |
US10668213B2 (en) | 2012-03-26 | 2020-06-02 | West Pharma. Services IL, Ltd. | Motion activated mechanisms for a drug delivery device |
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US11730892B2 (en) | 2016-08-01 | 2023-08-22 | West Pharma. Services IL, Ltd. | Partial door closure prevention spring |
US11819673B2 (en) | 2016-06-02 | 2023-11-21 | West Pharma. Services, IL, Ltd. | Three position needle retraction |
US11819666B2 (en) | 2017-05-30 | 2023-11-21 | West Pharma. Services IL, Ltd. | Modular drive train for wearable injector |
US11857767B2 (en) | 2017-12-22 | 2024-01-02 | West Pharma. Services IL, Ltd. | Injector usable with different dimension cartridges |
US11931552B2 (en) | 2015-06-04 | 2024-03-19 | West Pharma Services Il, Ltd. | Cartridge insertion for drug delivery device |
Families Citing this family (97)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5935099A (en) | 1992-09-09 | 1999-08-10 | Sims Deltec, Inc. | Drug pump systems and methods |
US6241704B1 (en) | 1901-11-22 | 2001-06-05 | Sims Deltec, Inc. | Drug pump systems and methods |
US5803712A (en) | 1988-05-17 | 1998-09-08 | Patient Solutions, Inc. | Method of measuring an occlusion in an infusion device with disposable elements |
AU634811B2 (en) * | 1989-10-10 | 1993-03-04 | Carefusion 303, Inc. | Two-cycle peristaltic pump |
WO1992005830A1 (en) * | 1990-10-05 | 1992-04-16 | Macnaught Pty. Limited | Controlled pressure fluid delivery device |
US5278072A (en) * | 1990-04-26 | 1994-01-11 | Minnesota Mining And Manufacturing Company | Calibration system and housing |
US5057278A (en) * | 1990-04-26 | 1991-10-15 | Minnesota Mining And Manufacturing Company | Sterile loop calibration system |
US5213483A (en) * | 1991-06-19 | 1993-05-25 | Strato Medical Corporation | Peristaltic infusion pump with removable cassette and mechanically keyed tube set |
US5217355A (en) * | 1991-08-05 | 1993-06-08 | Imed Corporation | Two-cycle peristaltic pump with occlusion detector |
CA2137772A1 (en) * | 1992-06-09 | 1993-12-23 | Shan Padda | Programmable infusion pump with interchangeable tubing |
US5626563A (en) * | 1993-01-12 | 1997-05-06 | Minnesota Mining And Manufacturing Company | Irrigation system with tubing cassette |
US5403277A (en) * | 1993-01-12 | 1995-04-04 | Minnesota Mining And Manufacturing Company | Irrigation system with tubing cassette |
US5423749A (en) * | 1993-11-18 | 1995-06-13 | Minnesota Mining And Manufacturing Company | Cardioplegia administration system and method |
US5772409A (en) * | 1993-11-22 | 1998-06-30 | Sims Deltec, Inc. | Drug infusion device with pressure plate |
US5531697A (en) * | 1994-04-15 | 1996-07-02 | Sims Deltec, Inc. | Systems and methods for cassette identification for drug pumps |
FR2714293B1 (en) * | 1993-12-29 | 1996-02-02 | Zambon Spa | Method for controlled injection of liquid into a tube and application to infusion pumps. |
US5658133A (en) * | 1994-03-09 | 1997-08-19 | Baxter International Inc. | Pump chamber back pressure dissipation apparatus and method |
US5482446A (en) * | 1994-03-09 | 1996-01-09 | Baxter International Inc. | Ambulatory infusion pump |
US5511951A (en) * | 1994-08-08 | 1996-04-30 | O'leary; Stephen H. | IV fluid delivery system |
US5513957A (en) * | 1994-08-08 | 1996-05-07 | Ivac Corporation | IV fluid delivery system |
US5549460A (en) * | 1994-08-08 | 1996-08-27 | Ivac Corporation | IV fluid delivery system |
US5499906A (en) * | 1994-08-08 | 1996-03-19 | Ivac Corporation | IV fluid delivery system |
US5716194A (en) * | 1994-09-12 | 1998-02-10 | Ivac Medical Systems, Inc. | System for increasing flow uniformity |
US5601420A (en) * | 1994-09-12 | 1997-02-11 | Ivac Medical Systems, Inc. | Interlock, latching, and retaining mechanism for an infusion pump |
US6234773B1 (en) | 1994-12-06 | 2001-05-22 | B-Braun Medical, Inc. | Linear peristaltic pump with reshaping fingers interdigitated with pumping elements |
US5628619A (en) * | 1995-03-06 | 1997-05-13 | Sabratek Corporation | Infusion pump having power-saving modes |
US5904668A (en) * | 1995-03-06 | 1999-05-18 | Sabratek Corporation | Cassette for an infusion pump |
US5795327A (en) * | 1995-03-06 | 1998-08-18 | Sabratek Corporation | Infusion pump with historical data recording |
US5637093A (en) * | 1995-03-06 | 1997-06-10 | Sabratek Corporation | Infusion pump with selective backlight |
US5620312A (en) * | 1995-03-06 | 1997-04-15 | Sabratek Corporation | Infusion pump with dual-latching mechanism |
JPH09299479A (en) * | 1996-05-15 | 1997-11-25 | Kyowa Sangyo Kk | Drip monitoring apparatus |
US5853386A (en) * | 1996-07-25 | 1998-12-29 | Alaris Medical Systems, Inc. | Infusion device with disposable elements |
US5848988A (en) * | 1996-07-26 | 1998-12-15 | Alaris Medical Systems, Inc. | Infusion device with audible data output |
US5823746A (en) * | 1996-08-14 | 1998-10-20 | Sims Deltec, Inc. | Reusable pressure plates and methods |
US5879144A (en) * | 1996-08-14 | 1999-03-09 | Sims Deltec, Inc. | Pressure plate adaptors and methods |
US5954485A (en) * | 1996-08-14 | 1999-09-21 | Sims Deltec, Inc. | Free-flow protection devices and methods |
US5788671A (en) * | 1996-08-14 | 1998-08-04 | Sims Deltec, Inc. | Reusable cassette housings and methods |
US5928196A (en) * | 1996-08-14 | 1999-07-27 | Sims Deltec, Inc. | Control module cassette locks and methods |
EP0986709A4 (en) | 1997-01-17 | 2001-05-02 | Niagara Pump Corp | Linear peristaltic pump |
US6719779B2 (en) | 2000-11-07 | 2004-04-13 | Innercool Therapies, Inc. | Circulation set for temperature-controlled catheter and method of using the same |
US6383210B1 (en) | 2000-06-02 | 2002-05-07 | Innercool Therapies, Inc. | Method for determining the effective thermal mass of a body or organ using cooling catheter |
US6585752B2 (en) | 1998-06-23 | 2003-07-01 | Innercool Therapies, Inc. | Fever regulation method and apparatus |
US6468242B1 (en) | 1998-03-06 | 2002-10-22 | Baxter International Inc. | Medical apparatus with patient data recording |
US6056522A (en) * | 1998-05-13 | 2000-05-02 | Sims Deltec, Inc. | Reusable cassette with a moveable door |
US6193480B1 (en) | 1998-08-03 | 2001-02-27 | Alaris Medical Systems, Inc. | System and method for increased flow uniformity |
US6719723B2 (en) | 2000-12-06 | 2004-04-13 | Innercool Therapies, Inc. | Multipurpose catheter assembly |
US6523414B1 (en) * | 2001-04-16 | 2003-02-25 | Zevex, Inc. | Optical pressure monitoring system |
DE10120543A1 (en) * | 2001-04-26 | 2002-11-07 | Ruediger Groening | Drug pump with programmed delivery rate |
US8504179B2 (en) | 2002-02-28 | 2013-08-06 | Smiths Medical Asd, Inc. | Programmable medical infusion pump |
US8250483B2 (en) | 2002-02-28 | 2012-08-21 | Smiths Medical Asd, Inc. | Programmable medical infusion pump displaying a banner |
US7059840B2 (en) * | 2002-04-05 | 2006-06-13 | Sigma International | Energy-saving, anti-free flow portable pump for use with standard PVC IV tubing |
US7300453B2 (en) * | 2003-02-24 | 2007-11-27 | Innercool Therapies, Inc. | System and method for inducing hypothermia with control and determination of catheter pressure |
EP1603462B1 (en) * | 2003-02-25 | 2015-07-15 | Devicor Medical Products, Inc. | Biopsy device with variable speed cutter advance |
US7367358B2 (en) * | 2005-02-02 | 2008-05-06 | Universal Infusion Technology, Llc | Medical fluid delivery system and method relating to the same |
US8954336B2 (en) | 2004-02-23 | 2015-02-10 | Smiths Medical Asd, Inc. | Server for medical device |
IL165365A0 (en) | 2004-11-24 | 2006-01-15 | Q Core Ltd | Finger-type peristaltic pump |
US8308457B2 (en) | 2004-11-24 | 2012-11-13 | Q-Core Medical Ltd. | Peristaltic infusion pump with locking mechanism |
US7572113B2 (en) * | 2005-03-21 | 2009-08-11 | Lancer Partnership, Ltd. | Methods and apparatus for pumping and dispensing |
DE102005017240A1 (en) * | 2005-04-14 | 2006-10-19 | Alldos Eichler Gmbh | Method and device for monitoring a pumped by a pump fluid flow |
JP2007226175A (en) * | 2006-01-26 | 2007-09-06 | Epson Imaging Devices Corp | Liquid crystal device and electronic equipment |
ES2751017T3 (en) * | 2006-06-08 | 2020-03-30 | Hoffmann La Roche | System to detect an occlusion in a tube |
JP4924235B2 (en) * | 2006-08-01 | 2012-04-25 | セイコーエプソン株式会社 | Fluid transport system, fluid transport device |
US8965707B2 (en) | 2006-08-03 | 2015-02-24 | Smiths Medical Asd, Inc. | Interface for medical infusion pump |
US8435206B2 (en) | 2006-08-03 | 2013-05-07 | Smiths Medical Asd, Inc. | Interface for medical infusion pump |
US8149131B2 (en) | 2006-08-03 | 2012-04-03 | Smiths Medical Asd, Inc. | Interface for medical infusion pump |
US8858526B2 (en) | 2006-08-03 | 2014-10-14 | Smiths Medical Asd, Inc. | Interface for medical infusion pump |
US8535025B2 (en) | 2006-11-13 | 2013-09-17 | Q-Core Medical Ltd. | Magnetically balanced finger-type peristaltic pump |
IL179234A0 (en) * | 2006-11-13 | 2007-03-08 | Q Core Ltd | An anti-free flow mechanism |
IL179231A0 (en) | 2006-11-13 | 2007-03-08 | Q Core Ltd | A finger-type peristaltic pump comprising a ribbed anvil |
US20140039343A1 (en) | 2006-12-13 | 2014-02-06 | Devicor Medical Products, Inc. | Biopsy system |
US20130324882A1 (en) | 2012-05-30 | 2013-12-05 | Devicor Medical Products, Inc. | Control for biopsy device |
JPWO2009119519A1 (en) | 2008-03-24 | 2011-07-21 | オリンパス株式会社 | Drug administration device |
US8133197B2 (en) | 2008-05-02 | 2012-03-13 | Smiths Medical Asd, Inc. | Display for pump |
JP5298699B2 (en) | 2008-08-20 | 2013-09-25 | セイコーエプソン株式会社 | Control unit, tube unit, micro pump |
JP5282508B2 (en) | 2008-09-29 | 2013-09-04 | セイコーエプソン株式会社 | Control unit, tube unit, micro pump |
JP5195368B2 (en) * | 2008-12-05 | 2013-05-08 | セイコーエプソン株式会社 | Tube unit, control unit, micro pump |
US8197235B2 (en) | 2009-02-18 | 2012-06-12 | Davis David L | Infusion pump with integrated permanent magnet |
US8353864B2 (en) | 2009-02-18 | 2013-01-15 | Davis David L | Low cost disposable infusion pump |
EP2448614B1 (en) | 2009-07-01 | 2018-10-10 | Fresenius Medical Care Holdings, Inc. | Drug delivery devices and related systems and methods |
US8241018B2 (en) * | 2009-09-10 | 2012-08-14 | Tyco Healthcare Group Lp | Compact peristaltic medical pump |
US8371832B2 (en) | 2009-12-22 | 2013-02-12 | Q-Core Medical Ltd. | Peristaltic pump with linear flow control |
DE102010003218A1 (en) * | 2010-03-24 | 2011-09-29 | Prominent Dosiertechnik Gmbh | Method for controlling and / or regulating a metering pump |
EP2558147A4 (en) | 2010-04-12 | 2014-12-17 | Q Core Medical Ltd | Air trap for intravenous pump |
AU2011308782B2 (en) | 2010-10-01 | 2014-11-06 | Zevex, Inc. | Method for improving accuracy in a peristaltic pump system based on tubing material properties |
US9674811B2 (en) | 2011-01-16 | 2017-06-06 | Q-Core Medical Ltd. | Methods, apparatus and systems for medical device communication, control and localization |
US10064987B2 (en) | 2011-01-31 | 2018-09-04 | Fresenius Medical Care Holdings, Inc. | Preventing over-delivery of drug |
EP2673018B1 (en) | 2011-02-08 | 2019-04-10 | Fresenius Medical Care Holdings, Inc. | Magnetic sensors and related systems and methods |
US9726167B2 (en) | 2011-06-27 | 2017-08-08 | Q-Core Medical Ltd. | Methods, circuits, devices, apparatuses, encasements and systems for identifying if a medical infusion system is decalibrated |
DK2729200T3 (en) * | 2011-07-06 | 2017-01-02 | Hoffmann La Roche | AUTOMATIC INJECTION DEVICE INCLUDING TWO OCCLUSION SENSORS |
US9144644B2 (en) | 2011-08-02 | 2015-09-29 | Baxter International Inc. | Infusion pump with independently controllable valves and low power operation and methods thereof |
US9144646B2 (en) | 2012-04-25 | 2015-09-29 | Fresenius Medical Care Holdings, Inc. | Vial spiking devices and related assemblies and methods |
CN105073159A (en) | 2013-01-28 | 2015-11-18 | 史密斯医疗Asd公司 | Medication safety devices and methods |
US9855110B2 (en) | 2013-02-05 | 2018-01-02 | Q-Core Medical Ltd. | Methods, apparatus and systems for operating a medical device including an accelerometer |
WO2014164136A1 (en) | 2013-03-13 | 2014-10-09 | Thoratec Corporation | Fluid handling system |
US11033728B2 (en) | 2013-03-13 | 2021-06-15 | Tc1 Llc | Fluid handling system |
USD746975S1 (en) | 2013-03-14 | 2016-01-05 | Thoratec Corporation | Catheter pump console |
ES2933693T3 (en) | 2019-11-18 | 2023-02-13 | Eitan Medical Ltd | Rapid test for medical pump |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3778195A (en) * | 1972-07-20 | 1973-12-11 | G Bamberg | Pump for parenteral injections and the like |
US4131399A (en) * | 1975-07-08 | 1978-12-26 | Rhone-Poulenc Industries | Peristaltic tube pump with means preventing complete occlusion of tube |
US4256437A (en) * | 1978-02-01 | 1981-03-17 | Stewart Naumann Laboratories, Inc. | Peristaltic infusion pump and method |
US4277226A (en) * | 1979-03-09 | 1981-07-07 | Avi, Inc. | IV Pump with empty supply reservoir and occlusion detector |
US4479797A (en) * | 1981-07-04 | 1984-10-30 | Terumo Corporation | Medication infusion device |
US4573994A (en) * | 1979-04-27 | 1986-03-04 | The Johns Hopkins University | Refillable medication infusion apparatus |
US4650469A (en) * | 1984-10-19 | 1987-03-17 | Deltec Systems, Inc. | Drug delivery system |
US4657490A (en) * | 1985-03-27 | 1987-04-14 | Quest Medical, Inc. | Infusion pump with disposable cassette |
Family Cites Families (159)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1615140A (en) * | 1922-01-13 | 1927-01-18 | Rusdell William Joseph | Pump or motor |
US1676114A (en) * | 1924-10-03 | 1928-07-03 | Rusdell William Joseph | Pump for liquids or hydraulic motor |
GB369037A (en) * | 1931-04-22 | 1932-03-17 | Yoshinobu Wada | Improvements in or relating to a pumping apparatus for medical treatments |
US1922196A (en) * | 1932-03-17 | 1933-08-15 | Nordberg Manufacturing Co | Pump |
US2105200A (en) * | 1934-04-25 | 1938-01-11 | Hugh G Phelps | Surgical pump |
US2412397A (en) * | 1943-12-31 | 1946-12-10 | Lyndus E Harper | Flexible tube pump |
US2483924A (en) * | 1946-06-10 | 1949-10-04 | Moulinier Edmond Jean | Pump |
US2546852A (en) * | 1947-01-27 | 1951-03-27 | Corneil Ernest Ruckle | Pumping means |
US2689530A (en) * | 1950-06-26 | 1954-09-21 | Leo M Harvey | Machine for dispensing liquids |
US2703084A (en) * | 1953-07-17 | 1955-03-01 | Fay M Tomlinson | Liquid dispenser |
US2925814A (en) * | 1956-10-30 | 1960-02-23 | Foster L Vibber | Transfusion apparatus |
US2922379A (en) * | 1957-06-06 | 1960-01-26 | Eugene L Schultz | Heart action multi-line pump constructions |
US2877714A (en) * | 1957-10-30 | 1959-03-17 | Standard Oil Co | Variable displacement tubing pump |
US3091239A (en) * | 1958-08-25 | 1963-05-28 | Moeller Wilhelm | Apparatus for intravasal injection of gaseous and liquid media |
US3048121A (en) * | 1960-04-14 | 1962-08-07 | John M Sheesley | Hydraulic actuated pump |
US3199511A (en) * | 1961-04-26 | 1965-08-10 | Kulick George | Apparatus for precise administration of parenteral fluids |
US3143969A (en) * | 1961-05-11 | 1964-08-11 | Roy S Sanford & Company | Liquid pump and meter |
US3198385A (en) * | 1962-09-06 | 1965-08-03 | Palmer M Maxwell | High pressure medical injection direct from a fluid containing ampule |
US3227092A (en) * | 1963-10-28 | 1966-01-04 | Jr Leland C Clark | Fluid pump |
NL301824A (en) * | 1963-12-13 | |||
US3335724A (en) * | 1964-07-24 | 1967-08-15 | Erich M Gienapp | Remote control, repeating, variable stroke hypodermic syringe device |
US3428042A (en) * | 1964-08-10 | 1969-02-18 | United Aircraft Corp | Heart pump actuator |
US3295458A (en) * | 1964-08-13 | 1967-01-03 | Adam P G Steffes | Pump |
US3384080A (en) * | 1964-10-16 | 1968-05-21 | Us Catheter & Instr Corp | Portable spring powered infusion device having escapement means controlling speed ofinfusion |
US3359910A (en) * | 1965-06-10 | 1967-12-26 | Little Inc A | Apparatus for programming fluid flow |
US3391644A (en) * | 1965-10-21 | 1968-07-09 | John F. Taplin | Double acting actuator or pump having a pair of rolling diaphragms |
US3451393A (en) * | 1966-02-07 | 1969-06-24 | Stanley J Sarnoff | Automatic infusion device |
US3375759A (en) * | 1966-05-18 | 1968-04-02 | Bourns Inc | Rolling-diaphragm pump |
US3427986A (en) * | 1967-06-27 | 1969-02-18 | Ernest R Corneil | Fluid pump with controlled variable flow |
US3464359A (en) * | 1967-11-13 | 1969-09-02 | Medimeter Corp The | Apparatus for moving fluid from one system to a second system |
US3559644A (en) * | 1967-12-14 | 1971-02-02 | Robert F Shaw | Liquid infusion apparatus |
US3488763A (en) * | 1968-02-16 | 1970-01-06 | Alden A Lofquist Jr | Rolling seal pump |
US3640277A (en) * | 1968-12-09 | 1972-02-08 | Marvin Adelberg | Medical liquid administration device |
GB1287951A (en) * | 1969-06-12 | 1972-09-06 | ||
US3518033A (en) * | 1969-08-22 | 1970-06-30 | Robert M Anderson | Extracorporeal heart |
US3670926A (en) * | 1969-09-11 | 1972-06-20 | Power Technology Corp | Intravenous feeding apparatus |
US3896741A (en) * | 1970-04-20 | 1975-07-29 | Evans Prod Co | Freight carrying device |
US3704080A (en) * | 1970-07-22 | 1972-11-28 | Grosvenor M Cross | Fluid engine |
US3730650A (en) * | 1970-09-14 | 1973-05-01 | Technicon Instr | Peristaltic pump and system therefor |
US3731679A (en) * | 1970-10-19 | 1973-05-08 | Sherwood Medical Ind Inc | Infusion system |
CH535897A (en) * | 1970-11-23 | 1973-04-15 | Papillon Ets | Displacement pump driven mechanically, hydraulically or pneumatically |
US3737251A (en) * | 1971-02-08 | 1973-06-05 | Alphamedics Mfg Cop | Peristaltic pump |
DE2108757C3 (en) * | 1971-02-24 | 1974-01-17 | Egon Georg 8000 Muenchen Weishaar | Device for suctioning blood from a surgical wound and feeding it to a heart-lung machine |
US3769879A (en) * | 1971-12-09 | 1973-11-06 | A Lofquist | Self-compensating diaphragm pump |
CH562604A5 (en) * | 1972-02-22 | 1975-06-13 | Kaltenbach & Voigt | |
US3809507A (en) * | 1972-03-01 | 1974-05-07 | B Baglai | Nonpulsating fluid-flow pump |
US3811800A (en) * | 1972-07-12 | 1974-05-21 | K Shill | Blood pump |
NL7210087A (en) * | 1972-07-21 | 1974-01-23 | ||
US3874826A (en) * | 1973-02-05 | 1975-04-01 | Ingemar H Lundquist | Intravenous delivery pump |
US4042153A (en) * | 1973-03-14 | 1977-08-16 | Standard Oil Company | Liquid dropping device |
US3993069A (en) * | 1973-03-26 | 1976-11-23 | Alza Corporation | Liquid delivery device bladder |
US3798982A (en) * | 1973-04-25 | 1974-03-26 | Origo | Pump actuator including rotatable cams |
US3886938A (en) * | 1973-10-23 | 1975-06-03 | Scala Anthony | Power operated fluid infusion device |
US3895631A (en) * | 1974-02-04 | 1975-07-22 | Alza Corp | Liquid infusion unit |
US3901231A (en) * | 1974-02-07 | 1975-08-26 | Baxter Laboratories Inc | Infusion pump apparatus |
US3884228A (en) * | 1974-02-26 | 1975-05-20 | Lynkeus Corp | Intravenous feeding system |
US3923060A (en) * | 1974-04-23 | 1975-12-02 | Jr Everett H Ellinwood | Apparatus and method for implanted self-powered medication dispensing having timing and evaluator means |
US3985133A (en) * | 1974-05-28 | 1976-10-12 | Imed Corporation | IV pump |
US3888239A (en) * | 1974-06-21 | 1975-06-10 | Morton K Rubinstein | Fluid injection system |
SE387162B (en) * | 1974-06-25 | 1976-08-30 | Ljungmans Verkstader Ab | HOSE PUMP |
US4037598A (en) * | 1974-08-12 | 1977-07-26 | Ivac Corporation | Method and apparatus for fluid flow control |
US4065230A (en) * | 1975-01-17 | 1977-12-27 | Hart Associates, Inc. | Reciprocating infusion pump and directional adapter set for use therewith |
US3993061A (en) * | 1975-02-28 | 1976-11-23 | Ivac Corporation | Syringe pump drive system and disposable syringe cartridge |
US4137913A (en) * | 1975-02-28 | 1979-02-06 | Ivac Corporation | Fluid flow control system |
US3994294A (en) * | 1975-02-28 | 1976-11-30 | Ivac Corporation | Syringe pump valving and motor direction control system |
US3969991A (en) * | 1975-03-03 | 1976-07-20 | Bellofram Corporation | Rolling diaphragm and rolling diaphragm devices |
FR2302753A1 (en) * | 1975-03-04 | 1976-10-01 | Ucc Union Chimique Continental | NEW METHOD AND DEVICE FOR REGULATING THE INFUSION RATE |
DE2513467C3 (en) * | 1975-03-26 | 1979-10-31 | Siemens Ag, 1000 Berlin Und 8000 Muenchen | Device for infusing liquids into the human or animal body |
US3993065A (en) * | 1975-05-20 | 1976-11-23 | Szabo Anthony W | Fluid infusion apparatus |
US4126132A (en) * | 1975-07-28 | 1978-11-21 | Andros Incorporated | Intravenous and intra arterial delivery system |
US4030495A (en) * | 1975-11-07 | 1977-06-21 | Baxter Travenol Laboratories, Inc. | Twin check valve pump system having fail-safe characteristic |
US4139008A (en) * | 1975-11-21 | 1979-02-13 | Wolfgang Wagner | Controlled-dose injection apparatus |
US4039269A (en) * | 1976-01-19 | 1977-08-02 | The Lynkeus Corporation | Flexible tube pump having linear cam actuation of distributor means |
US4155362A (en) * | 1976-01-26 | 1979-05-22 | Baxter Travenol Laboratories, Inc. | Method and apparatus for metered infusion of fluids |
FR2351081A1 (en) * | 1976-05-11 | 1977-12-09 | Rhone Poulenc Ind | PROCESS FOR MANUFACTURING TEREPHTHALIC ACID FROM DIPOTASIC TEREPHTHALATE, CONSTRUCTION IN ONE STAGE |
CA1110137A (en) | 1976-05-24 | 1981-10-06 | Ingemar H. Lundquist | Intravenous liquid pumping system and method |
US4094318A (en) * | 1976-07-09 | 1978-06-13 | Burron Medical Products, Inc. | Electronic control means for a plurality of intravenous infusion sets |
DE2636290A1 (en) * | 1976-08-12 | 1978-02-16 | Fresenius Chem Pharm Ind | DEVICE FOR CONTROLLING AND MONITORING BLOOD FLOW DURING BLOOD DIALYSIS, PERFUSION AND DIAFILTRATION USING ONLY ONE CONNECTION POINT TO THE PATIENT'S BLOOD CIRCUIT (SINGLE NEEDLE TECHNOLOGY) |
US4121584A (en) * | 1976-10-15 | 1978-10-24 | R. Scott Turner | Method and apparatus for controlling the dispensing of fluid |
US4067334A (en) * | 1976-10-29 | 1978-01-10 | Haller J Gilbert | Self-injecting hypodermic syringe device |
US4101057A (en) * | 1976-12-02 | 1978-07-18 | Ethyl Corporation | Trigger actuated pump |
US4152098A (en) * | 1977-01-03 | 1979-05-01 | Clark Ivan P | Micropump |
US4191184A (en) * | 1977-01-06 | 1980-03-04 | Carlisle Jeffrey A | Intravenous infusion regulation system with reciprocal metering means |
US4184815A (en) * | 1977-03-14 | 1980-01-22 | Extracorporeal Medical Specialties, Inc. | Roller pump rotor with integral spring arms |
US4142524A (en) * | 1977-06-02 | 1979-03-06 | Andros Incorporated | Cassette for intravenous delivery system |
US4199307A (en) * | 1977-07-05 | 1980-04-22 | Andros Incorporated | Medical infusion system |
US4210138A (en) * | 1977-12-02 | 1980-07-01 | Baxter Travenol Laboratories, Inc. | Metering apparatus for a fluid infusion system with flow control station |
US4217993A (en) * | 1977-12-02 | 1980-08-19 | Baxter Travenol Laboratories, Inc. | Flow metering apparatus for a fluid infusion system |
US4177810A (en) * | 1977-12-23 | 1979-12-11 | Damon Corporation | Pneumatic injection apparatus |
US4187057A (en) * | 1978-01-11 | 1980-02-05 | Stewart-Naumann Laboratories, Inc. | Peristaltic infusion pump and disposable cassette for use therewith |
ZA78674B (en) * | 1978-02-09 | 1979-09-26 | Ethor Ltd | Dispensing of fluent materials |
US4273121A (en) * | 1978-02-17 | 1981-06-16 | Andros Incorporated | Medical infusion system |
US4181245A (en) * | 1978-02-17 | 1980-01-01 | Baxter Travenol Laboratories, Inc. | Casette for use with an I.V. infusion controller |
CH633352A5 (en) | 1978-11-29 | 1982-11-30 | Doltron Ag | Hose pump. |
US4236880A (en) * | 1979-03-09 | 1980-12-02 | Archibald Development Labs, Inc. | Nonpulsating IV pump and disposable pump chamber |
US4391600A (en) | 1979-03-09 | 1983-07-05 | Avi, Inc. | Nonpulsating IV pump and disposable pump chamber |
US4410322A (en) | 1979-03-09 | 1983-10-18 | Avi, Inc. | Nonpulsating TV pump and disposable pump chamber |
US4265240A (en) * | 1979-04-16 | 1981-05-05 | Imed Corporation | Apparatus for providing a controlled introduction of intravenous fluid to a patient |
US4373527B1 (en) | 1979-04-27 | 1995-06-27 | Univ Johns Hopkins | Implantable programmable medication infusion system |
US4290346A (en) | 1979-04-30 | 1981-09-22 | Abbott Laboratories | Intravenous pump chamber |
US4280494A (en) | 1979-06-26 | 1981-07-28 | Cosgrove Robert J Jun | System for automatic feedback-controlled administration of drugs |
NL7905463A (en) | 1979-07-12 | 1981-01-14 | Noord Nederlandsche Maschf | PUMP. |
US4319568A (en) | 1979-10-29 | 1982-03-16 | Vickers Limited | Liquid dispensing apparatus |
US4278085A (en) * | 1979-12-13 | 1981-07-14 | Baxter Travenol Laboratories, Inc. | Method and apparatus for metered infusion of fluids |
JPS56113084A (en) * | 1980-02-12 | 1981-09-05 | Terumo Corp | Pulsation preventing method and device for peristaltic finger pump |
JPS56113083A (en) | 1980-02-12 | 1981-09-05 | Terumo Corp | Choke detection method and device for peristaltic liquid pump |
DE3018641C2 (en) | 1980-05-16 | 1986-05-28 | Hans 8228 Freilassing Rodler | Automatic infusion pump |
CA1169323A (en) | 1980-06-03 | 1984-06-19 | Anthony M. Albisser | Insulin infusion device |
US4332246A (en) | 1980-06-30 | 1982-06-01 | Staodynamics, Inc. | Positive displacement intravenous infusion pump device and method |
US4460358A (en) | 1980-11-07 | 1984-07-17 | Ivac Corporation | Combined load and latch mechanism for fluid flow control apparatus |
US4396385A (en) | 1980-12-05 | 1983-08-02 | Baxter Travenol Laboratories, Inc. | Flow metering apparatus for a fluid infusion system |
US4367435A (en) | 1980-12-15 | 1983-01-04 | Ivac Corporation | Motor control system |
US4416595A (en) | 1981-03-13 | 1983-11-22 | Baxter Travenol Laboratories, Inc. | Miniature rotary infusion pump with slide latch and detachable power source |
US4515589A (en) | 1981-03-23 | 1985-05-07 | Austin Jon W | Peristaltic pumping method and apparatus |
US4447233A (en) | 1981-04-10 | 1984-05-08 | Parker-Hannifin Corporation | Medication infusion pump |
NZ200222A (en) | 1981-04-15 | 1985-12-13 | Wellcome Australia | Elastic chamber pump:controlling pumping rate and indicating faults in fluid line |
US4411651A (en) | 1981-05-26 | 1983-10-25 | Pacesetter Systems, Inc. | Device and method useful in monitoring fluid flow in a drug injector |
US4409966A (en) | 1981-05-29 | 1983-10-18 | Lambrecht Richard M | Method and apparatus for injecting a substance into the bloodstream of a subject |
IT1144743B (en) | 1981-07-09 | 1986-10-29 | Mario Cane | PERFECTED INSULIN INFUSER APPARATUS |
US4392849A (en) | 1981-07-27 | 1983-07-12 | The Cleveland Clinic Foundation | Infusion pump controller |
US4437859A (en) | 1981-08-03 | 1984-03-20 | Drs Infusion Systems, Inc. | Hydraulic syringe drive |
PH18142A (en) | 1981-09-03 | 1985-04-03 | Unilever Nv | Hair dye composition |
US4380236A (en) | 1981-09-14 | 1983-04-19 | Baxter Travenol Laboratories, Inc. | Fluid pump |
US4472117A (en) | 1982-03-01 | 1984-09-18 | Air-Shields, Inc. | Infusion pumping apparatus |
US4397542A (en) | 1982-03-03 | 1983-08-09 | Xerox Corporation | Xerographic envelope printing |
US4449893A (en) | 1982-05-04 | 1984-05-22 | The Abet Group | Apparatus and method for piezoelectric pumping |
US4432699A (en) | 1982-05-04 | 1984-02-21 | The Abet Group | Peristaltic piezoelectric pump with internal load sensor |
US4460355A (en) | 1982-06-11 | 1984-07-17 | Ivac Corporation | Fluid pressure monitoring system |
US4493706A (en) * | 1982-08-12 | 1985-01-15 | American Hospital Supply Corporation | Linear peristaltic pumping apparatus and disposable casette therefor |
US4482347A (en) | 1982-08-12 | 1984-11-13 | American Hospital Supply Corporation | Peristaltic fluid-pumping apparatus |
US4494285A (en) | 1982-08-16 | 1985-01-22 | Windsor Medical, Inc. | Method of making a member defining a lumen for a peristaltic pump and member produced by said method |
US4490135A (en) | 1982-09-24 | 1984-12-25 | Extracorporeal Medical Specialties, Inc. | Single needle alternating blood flow system |
US4624661A (en) | 1982-11-16 | 1986-11-25 | Surgidev Corp. | Drug dispensing system |
US4519792A (en) | 1982-12-06 | 1985-05-28 | Abbott Laboratories | Infusion pump system |
US4544329A (en) | 1983-01-14 | 1985-10-01 | Windsor Medical, Inc. | Peristaltic pump having a spiral cam and straight peristaltic tube |
US4537561A (en) * | 1983-02-24 | 1985-08-27 | Medical Technology, Ltd. | Peristaltic infusion pump and disposable cassette for use therewith |
US4501405A (en) | 1983-06-21 | 1985-02-26 | Bunnell Life Systems, Inc. | Frictionless valve/pump |
US4648872A (en) | 1983-11-15 | 1987-03-10 | Kamen Dean L | Volumetric pump with replaceable reservoir assembly |
US4544369A (en) | 1983-11-22 | 1985-10-01 | C. R. Bard, Inc. | Battery operated miniature syringe infusion pump |
DE3347307A1 (en) | 1983-12-28 | 1985-07-11 | Speck-Kolbenpumpen-Fabrik Otto Speck Kg, 8192 Geretsried | PLUNGER PUMP |
US4657486A (en) | 1984-01-13 | 1987-04-14 | Stempfle Julius E | Portable infusion device |
US4551133A (en) | 1984-04-16 | 1985-11-05 | American Hospital Supply Corporation | Patient controlled medication infusion system |
US4673334A (en) * | 1984-05-25 | 1987-06-16 | Isco, Inc. | Peristaltic pump |
US4653987A (en) | 1984-07-06 | 1987-03-31 | Tsuyoshi Tsuji | Finger peristaltic infusion pump |
US4561830A (en) | 1984-10-01 | 1985-12-31 | Ivac Corporation | Linear peristaltic pump |
US4559038A (en) | 1984-10-19 | 1985-12-17 | Deltec Systems, Inc. | Drug delivery system |
US4559040A (en) | 1984-10-30 | 1985-12-17 | Pancretec, Inc. | Segmented peristaltic pump chamber |
US4586882A (en) | 1984-12-06 | 1986-05-06 | Baxter Travenol Laboratories, Inc. | Tubing occluder pump |
US4652260A (en) | 1985-03-11 | 1987-03-24 | Strato Medical Corporation | Infusion device |
US4627835A (en) | 1985-03-11 | 1986-12-09 | Strato Medical Corporation | Tubing assembly for infusion device |
US4564542A (en) | 1985-03-20 | 1986-01-14 | The B. F. Goodrich Company | Belt and method of splicing the same |
US4624847A (en) | 1985-04-22 | 1986-11-25 | Alza Corporation | Drug delivery device for programmed delivery of beneficial drug |
US4617014A (en) | 1985-11-26 | 1986-10-14 | Warner-Lambert Company | Dual mode I. V. infusion device |
US4735558A (en) * | 1986-04-08 | 1988-04-05 | Staar Surgical Company | Peristaltic pump latching mechanism |
DE3923457A1 (en) | 1989-07-15 | 1991-01-17 | Fresenius Ag | DEVICE FOR INJECTING LIQUIDS |
JP2859306B2 (en) | 1989-07-24 | 1999-02-17 | テルモ株式会社 | Infusion pump |
US5165873A (en) | 1989-10-10 | 1992-11-24 | Imed Corporation | Two-cycle peristaltic pump |
US5092749A (en) | 1990-05-07 | 1992-03-03 | Imed Corporation | Fluid pump drive mechanism |
US5217355A (en) | 1991-08-05 | 1993-06-08 | Imed Corporation | Two-cycle peristaltic pump with occlusion detector |
-
1988
- 1988-05-17 US US07/194,865 patent/US5074756A/en not_active Expired - Lifetime
-
1989
- 1989-05-02 CA CA000598427A patent/CA1322924C/en not_active Expired - Lifetime
- 1989-05-03 NZ NZ22897789A patent/NZ228977A/en unknown
- 1989-05-17 EP EP89906892A patent/EP0418306B1/en not_active Expired - Lifetime
- 1989-05-17 AT AT89906892T patent/ATE108070T1/en not_active IP Right Cessation
- 1989-05-17 AU AU37600/89A patent/AU633004B2/en not_active Expired
- 1989-05-17 DE DE68916643T patent/DE68916643T2/en not_active Expired - Lifetime
- 1989-05-17 JP JP1506473A patent/JPH03504208A/en active Pending
- 1989-05-17 WO PCT/US1989/002131 patent/WO1989011302A1/en active IP Right Grant
-
1991
- 1991-02-26 US US07/661,806 patent/US5320502A/en not_active Expired - Lifetime
-
1993
- 1993-09-23 US US08/126,056 patent/US5320503A/en not_active Expired - Lifetime
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3778195A (en) * | 1972-07-20 | 1973-12-11 | G Bamberg | Pump for parenteral injections and the like |
US4131399A (en) * | 1975-07-08 | 1978-12-26 | Rhone-Poulenc Industries | Peristaltic tube pump with means preventing complete occlusion of tube |
US4256437A (en) * | 1978-02-01 | 1981-03-17 | Stewart Naumann Laboratories, Inc. | Peristaltic infusion pump and method |
US4277226A (en) * | 1979-03-09 | 1981-07-07 | Avi, Inc. | IV Pump with empty supply reservoir and occlusion detector |
US4573994A (en) * | 1979-04-27 | 1986-03-04 | The Johns Hopkins University | Refillable medication infusion apparatus |
US4479797A (en) * | 1981-07-04 | 1984-10-30 | Terumo Corporation | Medication infusion device |
US4650469A (en) * | 1984-10-19 | 1987-03-17 | Deltec Systems, Inc. | Drug delivery system |
US4657490A (en) * | 1985-03-27 | 1987-04-14 | Quest Medical, Inc. | Infusion pump with disposable cassette |
Cited By (30)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5011378A (en) * | 1988-07-08 | 1991-04-30 | I-Flow Corporation | Pump tube mount and cartridge for infusion pump |
US5131816A (en) * | 1988-07-08 | 1992-07-21 | I-Flow Corporation | Cartridge fed programmable ambulatory infusion pumps powered by DC electric motors |
US5201636A (en) * | 1991-02-19 | 1993-04-13 | Milton Roy Company | Stator current based malfunction detecting system in a variable flow delivery pump |
US7471994B2 (en) | 1992-10-15 | 2008-12-30 | The General Hospital Corporation | Infusion pump with an electronically loadable drug library and label reader |
AU739019B2 (en) * | 1996-04-10 | 2001-10-04 | Baxter International Inc. | A method of loading a tube into a volumetric infusion pump |
US9107999B2 (en) | 1998-10-29 | 2015-08-18 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US9011371B2 (en) | 1998-10-29 | 2015-04-21 | Medtronic Minimed, Inc. | Method and apparatus for detecting occlusions in an ambulatory infusion pump |
US9033925B2 (en) | 1998-10-29 | 2015-05-19 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US9327073B2 (en) | 1998-10-29 | 2016-05-03 | Medtronic Minimed, Inc. | Method and apparatus for detecting occlusions in an ambulatory infusion pump |
US9364608B2 (en) | 1998-10-29 | 2016-06-14 | Medtronic Minimed, Inc. | Method and apparatus for detecting occlusions in an ambulatory infusion pump |
US9433733B2 (en) | 1998-10-29 | 2016-09-06 | Medtronic Minimed, Inc | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US9433732B2 (en) | 1998-10-29 | 2016-09-06 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US8864739B2 (en) | 1998-10-29 | 2014-10-21 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US11167086B2 (en) | 2008-09-15 | 2021-11-09 | West Pharma. Services IL, Ltd. | Stabilized pen injector |
US10335545B2 (en) | 2012-01-31 | 2019-07-02 | West Pharma. Services IL, Ltd. | Time dependent drug delivery apparatus |
US9463280B2 (en) | 2012-03-26 | 2016-10-11 | Medimop Medical Projects Ltd. | Motion activated septum puncturing drug delivery device |
US10668213B2 (en) | 2012-03-26 | 2020-06-02 | West Pharma. Services IL, Ltd. | Motion activated mechanisms for a drug delivery device |
US10159785B2 (en) | 2012-03-26 | 2018-12-25 | West Pharma. Services IL, Ltd. | Motion activated septum puncturing drug delivery device |
US10179204B2 (en) | 2012-03-26 | 2019-01-15 | West Pharma. Services IL, Ltd. | Motion-activated septum puncturing drug delivery device |
US9878091B2 (en) | 2012-03-26 | 2018-01-30 | Medimop Medical Projects Ltd. | Motion activated septum puncturing drug delivery device |
US9889256B2 (en) | 2013-05-03 | 2018-02-13 | Medimop Medical Projects Ltd. | Sensing a status of an infuser based on sensing motor control and power input |
WO2014179210A1 (en) * | 2013-05-03 | 2014-11-06 | Medimop Medical Projects Ltd. | Sensing a status of an infuser based on sensing motor control and power input |
US10398837B2 (en) | 2013-05-03 | 2019-09-03 | West Pharma. Services IL, Ltd. | Sensing a status of an infuser based on sensing motor control and power input |
US10617819B2 (en) | 2015-04-10 | 2020-04-14 | West Pharma. Services IL, Ltd. | Needle cannula position as an input to operational control of an injection device |
US9744297B2 (en) | 2015-04-10 | 2017-08-29 | Medimop Medical Projects Ltd. | Needle cannula position as an input to operational control of an injection device |
US11931552B2 (en) | 2015-06-04 | 2024-03-19 | West Pharma Services Il, Ltd. | Cartridge insertion for drug delivery device |
US11819673B2 (en) | 2016-06-02 | 2023-11-21 | West Pharma. Services, IL, Ltd. | Three position needle retraction |
US11730892B2 (en) | 2016-08-01 | 2023-08-22 | West Pharma. Services IL, Ltd. | Partial door closure prevention spring |
US11819666B2 (en) | 2017-05-30 | 2023-11-21 | West Pharma. Services IL, Ltd. | Modular drive train for wearable injector |
US11857767B2 (en) | 2017-12-22 | 2024-01-02 | West Pharma. Services IL, Ltd. | Injector usable with different dimension cartridges |
Also Published As
Publication number | Publication date |
---|---|
US5320503A (en) | 1994-06-14 |
AU633004B2 (en) | 1993-01-21 |
EP0418306B1 (en) | 1994-07-06 |
EP0418306A1 (en) | 1991-03-27 |
JPH03504208A (en) | 1991-09-19 |
US5320502A (en) | 1994-06-14 |
DE68916643D1 (en) | 1994-08-11 |
US5074756A (en) | 1991-12-24 |
AU3760089A (en) | 1989-12-12 |
NZ228977A (en) | 1994-07-26 |
ATE108070T1 (en) | 1994-07-15 |
CA1322924C (en) | 1993-10-12 |
EP0418306A4 (en) | 1991-05-22 |
DE68916643T2 (en) | 1995-02-16 |
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