US3923426A - Electroosmotic pump and fluid dispenser including same - Google Patents
Electroosmotic pump and fluid dispenser including same Download PDFInfo
- Publication number
- US3923426A US3923426A US497685A US49768574A US3923426A US 3923426 A US3923426 A US 3923426A US 497685 A US497685 A US 497685A US 49768574 A US49768574 A US 49768574A US 3923426 A US3923426 A US 3923426A
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- United States
- Prior art keywords
- fluid
- pump
- porous body
- electrodes
- power source
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 239000012530 fluid Substances 0.000 title claims abstract description 194
- 239000012528 membrane Substances 0.000 claims abstract description 35
- 238000005341 cation exchange Methods 0.000 claims abstract description 21
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- 239000003814 drug Substances 0.000 claims abstract description 12
- 238000005192 partition Methods 0.000 claims abstract description 11
- 239000000919 ceramic Substances 0.000 claims abstract description 7
- 229910052751 metal Inorganic materials 0.000 claims description 22
- 239000002184 metal Substances 0.000 claims description 22
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- 150000002500 ions Chemical class 0.000 claims description 11
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- VYPSYNLAJGMNEJ-UHFFFAOYSA-N silicon dioxide Inorganic materials O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 3
- 239000011593 sulfur Substances 0.000 claims description 3
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- 230000032258 transport Effects 0.000 description 31
- 210000001787 dendrite Anatomy 0.000 description 12
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- PLAZTCDQAHEYBI-UHFFFAOYSA-N 2-nitrotoluene Chemical compound CC1=CC=CC=C1[N+]([O-])=O PLAZTCDQAHEYBI-UHFFFAOYSA-N 0.000 description 1
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- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
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Images
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
- B01D61/42—Electrodialysis; Electro-osmosis ; Electro-ultrafiltration; Membrane capacitive deionization
- B01D61/56—Electro-osmotic dewatering
-
- 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
- F04B15/00—Pumps adapted to handle specific fluids, e.g. by selection of specific materials for pumps or pump parts
-
- 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
- F04B17/00—Pumps characterised by combination with, or adaptation to, specific driving engines or motors
- F04B17/003—Pumps characterised by combination with, or adaptation to, specific driving engines or motors driven by piezoelectric means
-
- 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
- F04B19/00—Machines or pumps having pertinent characteristics not provided for in, or of interest apart from, groups F04B1/00 - F04B17/00
- F04B19/006—Micropumps
-
- 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
- F04B19/00—Machines or pumps having pertinent characteristics not provided for in, or of interest apart from, groups F04B1/00 - F04B17/00
- F04B19/20—Other positive-displacement pumps
-
- 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
- F04B19/00—Machines or pumps having pertinent characteristics not provided for in, or of interest apart from, groups F04B1/00 - F04B17/00
- F04B19/20—Other positive-displacement pumps
- F04B19/22—Other positive-displacement pumps of reciprocating-piston type
Definitions
- the pump comprises a plexiglass housing having a fluid inlet and outlet, a pair of spaced silver-silver chloride electrodes disposed in the housing and connected to a d.c. power source, a porous ceramic plug which has a high zeta potential relative to the fluid interposed between the electrodes, a cation exchange membrane positioned on each side of the ceramic plug between it and the electrode facing it and a fluid passageway in the housing extending from the fluid inlet to one side of the plug and from the other side of the plug to the outlet.
- the fluid dispenser is a modularized, self-contained unit consisting of the pump and a multicavitied fluid reservoir which contains both the fluid to be pumped and the fluid to be dispensed.
- Fluid is pumped from a first reservior cavity into a second cavity which already is fllled with fluid.
- the second cavity adjoins a third cavity filled with fluid. such as drug, to be dispensed and is sealingly spearated from the third cavity by a flexible partition.
- the increase in volume in the second cavity distends the flexible partition into the third cavity forcing fluid therefrom.
- FIG. 8 PUMP ELECTROOSMOTIC PUMP AND FLUID DISPENSER INCLUDING SAME BACKGROUND OF THE INVENTION 1.
- This invention relates to an electroosmotic pump and a fluid dispenser incorporating an electroosmotic pump.
- Electroosmosis is the opposite of electrophoresis.
- a stationary solid body through which a fluid will pass such as a porous body, has a matrix of fixed electrical charges and a fluid carries mobile electrical charges of opposite polarity relative to the fixed charges of the body.
- Electrophoresis involves the movement of charged particles through a stationary body of fluid.
- This invention is an electroosmotic pump and a fluid dispenser including the pump.
- the pump pumps a fluid susceptible to electroosmotic transport and comprises: a housing having an inlet for the fluid and an outlet for the fluid; a pair of spaced electrodes within the housing; a d.c.
- a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid; a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body; and a fluid passageway in the housing extending from the inlet to the fluid entrance surface of the body and from the fluid exit surface of the body to the outlet.
- the pump is structured symmetrically so that the fluid flow therethrough may be reversed by reversing the electrode polarity.
- a cation exchange membrane is interposed between the porous body and both of the electrodes.
- the dispenser is a self-contained unit and in addition to the pump comprises: a source ofthe fluid pumped by the pump connected to the pump inlet; and a vessel having a first chamber for containing the fluid to be dispensed, the first chamber having an outlet port, a second chamber for receiving the fluid pumped by the pump connected to the pump outlet and a movable barrier sealingly separating the first chamber from the second chamber. Fluid is dispensed from the first chamber as fluid is pumped into the second chamber from the pump causing the fluid volume in the second chamber to increase and move the barrier into the first chamber thereby forcing a corresponding volume of fluid from the first chamber therefrom via the outlet port.
- the above described pump and dispenser have several very advantageous features.
- the pump has no moving parts and thus is not susceptible to frictional wear.
- the elements of the pump which are the limiting elements in the pumps lifetime, namely the electrodes, membranes and porus body, may be modularized for easy replacement.
- the dispenser is readily miniaturized and is thus capable of being used as a portable unit which may be strapped or otherwise affixed to the desired dispensing site. Since the pump is driven electrically and has no moving parts it may be instantaneously turned on and off and therefore may be programmed to dispense fluid in an infinite variety of time patterns. The flow rate and output pressure may be varied by varying the electrical input to the pump. And, the dispenser is capable of being controlled remotely if desired.
- Embodiments of the pump/dispenser in which the electrode polarity may be reversed have the additional advantage of being long-lived].
- FIG. 1 is an enlarged, sectional view of the pump
- FIG. 2 is an enlarged, exploded view of the pump of FIG. 1;
- FIG. 3 is an enlarged plan view of the pump of FIG.
- FIG. 4 is an enlarged side elevational view of the pump of FIG. 1;
- FIG. 5 is a partly schematic, sectional view of the basic elements of the pump of FIG. 1;
- FIG. 6 is a perspective view, in actual scale, of the fluid dispenser.
- the cylindrical member is the pump of FIG. 1 and the parallelipiped member is a reservoir module which contains the fluid to be pumped (transport fluid) and the fluid to be dispensed;
- FIG. 7 is an enlarged, longitudinal sectional view of the reservoir module of the dispenser of FIG. 6;
- FIG. 8 is a sectional view taken along line 8-8 of FIG. 7;
- FIG. 9 is a schematic view illustrating the power and control elements for activating and driving the pump and dispenser.
- FIG. 5 The basic innards of the electroosmotic pump are shown in FIG. 5. They are a cathode 10 connected to the negative pole of a d.c. power source, an anode 11 connected to the positive pole. of the d.c. power source, a pair of cation exchange membranes 12, I3 interposed between cathode l0 and anode 11 and a porous plug 14 interposed between membranes l2, l3. Briefly this pump transports a transport fluid (indicated by arrows in FIG. 3) by the phenomenon of electroosmosis.
- Porous plug 14 carries a negative surface charge relative to the transport fluid and the transport fluid carries a positive surface charge relative to the porous plug 14.
- the transport fluid When a voltage difference is applied across anode 11 and cathode 10 the transport fluid will flow through porous plug 14 generally in the direction from anode to cathode as shown by the arrows.
- the transport fluid flow may be reversed by simply reversing the polarity of the electrodes.
- Membranes 12, 13 inhibit dendrite growth of electrode material and thus increase the pumps lifetime.
- Cathode 10 and anode 11 may be made of conventionally used metal electrode materials such as silver, platinum, copper and the like. Electrodes should be selected which do not produce appreciable amounts of gas through electrolysis and which do not polarize.
- the cation exchange materials from which membranes 12, 13 may be made are well known in the art and do not require extensive elaboration.
- these materials are cross-linked polymer resins of the strong acid type.
- Preferred resins are the sulfonated crosslinked polystyrene variety which have a high selectivity for ions of the metal forming the electrodes.
- the electrodes are silver
- the resin preferably has a high selectivity for silver.
- the ion exchange resin be in a salt form corresponding to the metal forming the electrodes, e.g. in the case of silver, in the silver salt form.
- Commercial resins are normally supplied in an alkali metal salt form and may be transformed to other salt forms by treatment with solutions of such salts, e.g. aqueous silver nitrate in the case of silver.
- the composition, porosity, pore size and the thickness of porous plug 14 significantly affect the operation of the pump, namely the potential required to drive the pump, the flow rate and output pressure.
- a composition which exhibits a high zeta potential relative to the transport fluid is desired. Generally speaking, the higher the zeta potential between the plug and transport fluid the lesser the potential'required to produce a given pressure and flow rate. Quartz, glass, ceramics and sulfur are suitable materials for making the plug when used with the transport fluids described below.
- Plugs of such materials may be in the form of an integral, interconnected porous network, a porous walled container packed with particles of such materials, a porous matrix in which particles of such materials are dispersed, such as beads of the material in a porous polymer matrix, and the like.
- the pore size of the plug will usually be between about 0.004 p. and about 1 [.L.
- the porosity of the plug is not critical and will usually be between about 10 and about 70 percent.
- the transport fluid should have a high zeta potential with respect to the plug, high dielectric constant, low viscosity and high specific resistance.
- the conductivity of the fluid has an inverse relationship to the specific resistance. For this reason the conductivity should be low, that is, less than about l millimho/cm, preferably less than 25 micromho/cm. It follows that the transport fluid should be essentially free of even small concentrations of conducting species such as various ions. It is desirable that the zeta potential between the fluid and plug be in the range of about I to 100 millivolts, the dielectric constant be between about l and 90, the viscosity between about 0.5 and centipoises and the specific resistance about 10 to 10 ohm cm.
- fluids which may be used are distilled water. 1,2- propanediol cyclic carbonate, ethyl alcohol and ethyl alcohol-water mixtures, formamide, furfuraldehyde, nitrobenzene, o-nitrotoluene.
- acetone n-propyl alcohol, n-butyl alcohol, benzaldehyde, aniline, propionic acid, chloroform, ether, methyl alcohol, iso-butyl alcohol, methyl ethyl ketone, methyl propyl ketone, methyl acetate, ethylene bromide, benzene, glycerine, allyl alcohol, amyl alcohol, ethyl acetate, ethyl butyrate, amyl acetate, carbon tetrachloride, xylene and turpentine oil.
- the electrodes, transport fluid and porous plug have been selected, they together with the voltage applied across the electrodes determine the flow rate and the electroosmotic pressure (the actual output pressure of the pump or dispenser is equal to the electroosmotic pressure less any back pressure inherent in the pump or dispenser).
- the flow rate and osmotic pressure for any given system may be calculated from the basic linear electroosmotic phenomenological equations defining the volume flow of fluid and electrical current through the porus plug 14, the Onsager relations, the Helmholz- Smoluchowski theorems, Poisseuilles Law, Ohms Law, the characteristics of the porous plug 14 and the characteristics of the transport fluid.
- a flow rate of 0.001 to 1.0 ml/hr at an actual output pressure on the order of at least one atmosphere is desired.
- the voltage required to produce such flow rates and pressures may also be calculated from the above listed equations, etc. Voltages in the range of l to volts will normally be sufficient to generate the above flow rates and pressures.
- FIGS. 1-4 show an entire pump unit, generally designated 15, which embodies the basic elements shown in FIG. 5.
- the housing of pump 15 consists of two cylindrical electrode/membrane housing members l6, 17 which are identical in structure and a pair of cylindrical porous plug housing members 18, 19 which are also identical in structure (FIG. 2). All of these housing members should be made of materials from which the transport fluid cannot leach conducting species. Various plastics from which ionic species have been preleached, such as preleached plexiglass, or metals such as stainless steel may be used.
- conducting metal Housing member 16 has a cylindrical recess 22 in its inner face 23 into which disc-shaped cathode l0 and disc-shaped membrane 12 snugly fit face-to-face (FIGS. 1 and 2).
- a thin ring 24 of a conducting metal such as silver is permanently imbedded in housing member 16 at the periphery of the bottom surface 25 of recess 22 such that ring 24 contacts the entire periphery of cathode 10 when the latter is fit into recess 22.
- Inner face 23 is also provided with an O-ring slot 26 for receiving an O-ring 27.
- Housing member 16 also has a pair of axial, diametrically opposed bores 28, 29 extending through it.
- a hollow sleeve 32 made of a conducting metal such as silver, platinum or gold is press fit partially into bore 29.
- Sleeve 32 has an integral radial collar 33 which is pressed into contact with a lead wire 34, also formed of a conductingmetal such as platinum or silver, which is permanently imbedded in member 16 and extends therein from bore 29 to contact with ring 24.
- the hollow of sleeve 32 is adapted to receive a lead wire (not shown) from the negative pole ofa dc. power source (also not shown in FIGS. l-4).
- Sleeve 32, lead wire 34 and ring 24 interconnect cathode 10 with the negative pole of the dc. power source.
- Housing member l6 is further provided with an L- shaped transport fluid flow channel 35 which extends axially into member 16 from face 23 and then radially outwardly therein opening at the radial surface thereof (FIGS. 3, 4).
- housing member 17 is identical in structure to member :16.
- Member 17 has a cylindrical recess 36 for receiving anode 11 and membrane 13, a pair of axial bores 37, 38 which register with bores 29,28 respectively, an O-ring slot 39 for receiving an O-ring 42 and an L-shaped transport fluid flow channel 43.
- Member 17 is providedwith an .imbedded anode contacting ring 44, animbedded lead wire 45 and a metal sleeve 46 within bore 38 forinterconnecting anode 11 with the positive pole. of the dc power source.
- Housing members l8, 19 (FIGS. 1 and 2) hold porous plug 14.
- Member 18 has a cylindrical central axial bore 47 extending through it and an inner counterbore 48 thereto. As shown in .FIG. 1 one side of the porous plugfits within counterbore 48 and is seated against a shoulder49 which definesthe transition between bore 47 and counterbore 48.
- the inner face 52 of member 18 is provided with an O-ring slot 53 for receiving 0: ring 54 and the outer face 55 thereof is provided with an O-ring slot 56 for receiving O-ring 27.
- Outer face 55 also has a slot at 57 which opens through shoulder 49 into bore 47 and extends radially therefrom into registry (FIG. 1.) with the axial portion of fluid flow channel 35 in housing member 16.
- Housing member 18 also has a pair of axial, diametrically opposed bores 58, 59 extending through it which align with bores 28, 29 respectively in member 16 and receive portionsofmetal sleeves 32, 46 when the pump isassembled (FIG. 1). i
- housing member 19 is identical to that of-member l8.'Thus it too has a central axial bore 62 and counterbore 63 thereto which receive the other side of porous'plug 14. Likewise, it is provided with an O-ring slot 64 for O- ring 54, an O-ring slot 65 for O-ring 42 and a pair of diametrically opposed axial bores 66, 67. It also has a slot at 68 which opens into bore '62" and extends radially therefrominto registry with the axial portionof fluid flow channel 43 to provide a flow path therefrom to the entrance side of porous plug '14.
- FIG. 3 pump is assembled and held together in fluid tight engagement by means of six stainless steel bolts 69 (the corresponding 'nuts are not shown) which are spaced circumferentially about the edge of pump 15 and'extend axially therethrough from one side of pump 15 through to its other side.
- pump 15 is'fitted with a pair of stainless steel transport fluid conduits 72, 73 whi ch are received in the other ends of fluid flow channels 35, 43 respectively, in fluid tight engagement therewith and extend outwardly from the pump.
- t Y 7 FIG. 6 shows pump 15 connected to a fluid reservoir, generally designated 74.
- Conduits 72, 73 interconnect reservoir 74 and pump 15.
- the housing ofreservoir 74 consists of three housing members 75, 76, 77 the'latter two of which are identical in structure. Members 76, 77
- three members may be made from the same materials as the housing members of the pump.
- member 76 has an elongated, bowl-shaped cavity 78 formed in its inner surface which contains the transport fluid to be pumped by pump 15.
- a flow passageway 79 extends from cavity 78 to a fitting 82 which is adapted to receive an end of conduit 73 in fluid tight engagement.
- Fitting 82 has a channel 83 which interconnects passageway 79 and conduit 73.
- member 77 is provided with an elongated, bowl-shaped cavity 84 which is filled with transport fluid and aflow passageway 85 extending from cavity 84 to a fitting 86 which receives an end of conduit 72 in fluid tight engagement.
- Fitting 86 has a channel 87 which interconnects passageway 85 and conduit 72.
- Member'75 has a pair of cavities 88, 89 which are identical in shape and volume to cavities 78, 84,,respectively, and which adjoin therewith.
- the two sets of adjoined cavities (.78/88 and,84/89) are separated by a pair of fluid impermeable, fliud tight, flexible partitions 92, 93 respectively.
- Partitions 92, 93 should be made from materials which are compatible with and do not contaminate the transport fluid or the fluid t'o be dispensed. These partitions may be flexible by virtue of their composition (e.g.
- a fluid passageway 94 leads from cavity 88 to a channeled fitting 95 adapted to receive a dispensing conduit 96.
- a fluid'passageway 97 leads from cavity 89 to a channeled fitting 98 adapted to receive a dispensing conduit 99.
- the outer surfaces of member 75 which face members 76, 77 are provided with seal channels 102, 103 which hold seals 104, 105 respectively.
- the reservoir 74 is assembled and held tightly together by eight stainless steel bolts 106 (and nuts not shown) (FIG. 6) which extend transversely through elements 77, 75, 76 from one side of reservoir 74 to the opposite side thereof.
- Dispensing conduits 96, 99 may be fitted with conventional administration means such as valves, needles, nozzles, catheters and the like.
- FIG. 9 illustrates power and control elements which may beu'sed to run the dispenser of FIG. 4. Everything illustrated with the exceptions of the pump and co'ntroller are electronic elements of the type'well known or readily designed by persons skilled in the art.
- the controller may be a human being or a machine which functions-to activate the command transmitter.
- the command transmitter is simply a signal generator which responds to the input from the controller and generates a signal, usually electrical, which is capable of being received by the command-receiver,
- the command transmitter may be integral with the command receiver or remote therefrom (indicated by a curvilineararrow in FIG. 9).
- a remote element might be analogized to the commonly used manually operated remote controls used with television receivers.
- the command receiver is powered by the same low voltage d.c.' battery which, serves as the power source for, ,the pump. (A low voltage battery is employed merely to conserve space.) Both the battery and command receiver are connected to a power. (off/on) switch. The command receiver activates the power switch in response to the signal transmitted to it by the command transmitter.
- the signal may of course be continuous or intermittent with the pattern of intermittency being infinitely variable. With such variety the dispenser may be made to dispense in an infinite variety of patterns.
- a d.c.-d.c. converter is interposed between the power switch and the pump.
- the function of that converter is to take the low voltage power it receives from the low voltage battery via the switch and convert it to a higher voltage. It does this by converting the low voltage d.c. to ac, transforming the a.c. up to a higher voltage and converting the higher voltage ac. to d.c.
- the low voltage battery/d.c. d.c. converter combination is employed rather than a higher voltage battery because it is easier to make a small version of that combination than to make a small version of a higher voltage battery.
- the output from the converter is transmitted to the pump by appropriate wiring which is engaged by the metal sleeves 32, 46.
- pump 15 may be used to pump transport fluid in a direction reverse to that shown in FIG. 5. This may be done by simply reversing the polarity of the electrodes, i.e.. making cathode 10 an anode and anode 11 a cathode. It is solely for this reason that pump 15 is provided with membrane 13. Membrane l3 inhibits dendrite growth from electrode 11 towards electrode 10 when the electrode polarity and transport fluid flow are reversed. Otherwise it serves no function and could be eliminated if the pump was intended to pump in one direction only. When the electrode polarity is reversed transport fluid is pumped from cavity 84 of reservoir 74 via passageway 85, channel 87 and conduit 72 into fluid flow channel 35.
- membrane 12 inhibits electrode dendrite growth and prolongs and pumps lifetime.
- 'system-metal from'the-anode deposits on the cathode.
- current distribution on the cathode is not uniform but is localized in spots on the cathode surface.
- Metal deposits more rapidly on these spots of higher current density to form the needle like dendrites.
- Dendrite growth occurs in the direction of least resistance between the electrodes and if left unhindered initially occurs axially between the cathode l0 and plug 11. 'At the plug the dendrite growth is through the plugs pores-which of course blocks the pores making the plug less porous and less efficient. The dendrite will grow entirely through the 'plug and then axially therefrom into contact with the anode-which of course short circuits the pump and renders it inoperable.
- the dendrite growth is substantiallyinhibited.
- an increase in membrane thickness increased the inhibition and pump lifetime.
- the thickness of the membrane in pump embodiments such as for use in the drug dispenser of the drawings will usually be.between about 200 microns and 2,000 microns.
- dendrite growth may be controlled by periodically reversing the electrode polarity in the manner described above. Such reversal also effects a reversal of dendrite growth, thereby shrinking and eroding the dendrites formed during operation of the pump with the original electrode polarity and vice versa. Accordingly it is desirable to periodically reverse the electrode potential if such operation is compatible with other aspects of the pump operation and use.
- Denorite growth also may be controlled by operating the pump in an on/off mode. Such control may be effected by limiting the on mode to approximately the time it takes the current distribution to localize suffrciently to initiate dendrite growth (this time may be determinedempirically forany given system) and maintaining the off mode for a time sufflcientto permit ion concentration gradients at the electrodes to randomize to a significant extent.
- any flowable liquid, gas or slurry may be charged to the reservoir and dispensed therefrom by the pump 15 as described above.
- the device illustrated in the drawings wasdesigned particularly for dispensing liquid drugs, solutions of drugs or dispersions of drugs.
- the pump may be used as a suction pump such as in a fluid sampling device. In such a device the pump is used to create a pressure differential across a moveable barrier contained within a sampling vessel, the differential being employed to suck the desired sample into the vessel.
- An electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising:
- a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid;
- a fluid passageway in the housing extending from the inlet to said fluid entrance surface and from said fluid exit surface to the outlet.
- the electroosmotic pump of claim 1 wherein the pore size of the porous body is between about 0.004 and about in.
- porous body is made from quartz, glass, ceramic or sulfur.
- the electroosmotic pump of claim 1 wherein the cation exchange membrane is made of a cross-linked polymer resin of the strong acid type.
- cross-linked polymer resin is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
- the electroosmotic pump of claim 1 including:
- a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body.
- the electroosmotic pump of claim 8 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversedby reversing the electrode polarity.
- the electroosmotic pump of claim 1 including:
- g. means connected to said power source for switching said power. source on and off in a predetermined sequence.
- the electroosmotic pump of claim 1 wherein the potential applied across the electrodes from the power source is in the range of 1 volt to volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
- the electroosmotic pump of claim 9 including:
- h. means connected to said power source for switching said power source on and off in a predetermined sequence and wherein the pore size of the porous body is between about 0.004;. and about
- the zeta potential between the porous body and the fluid is in the range of l millivolt to 100 millivolts
- the ion exchange membrane is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about l.0 ml/hr.
- a dispenser for dispensing a fluid comprising:
- an electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising:
- a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid;
- a movable barrier sealingly separating the first chamber from the second chamber and adapted to move in response to an increase in the volume of fluid received in the first chamber so as to dispense a correspoding volume of fluid contained in the second chamber therefrom via the outlet port.
- the dispenser of claim 16 wherein the zeta potential between the porous body and the fluid is in the range of about 1 millivolt to 100 millivolts.
- the cation exchange membrane is made of sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
- electroosmotic pump includes:
- g. means connected to said power source for switching said power source on and off in a predetermined sequence.
- the dispenser of claim 13 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversed by reversing the electrode polarity, and pore size of the porous body is between about 0.004p/and about l,u., the zeta potential between the porous body and the fluid is in the range of l millivolt to I00 millivolts.
- the cation ion exchange membrane is made of a sulfonated crosslinked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr and the pump includes:
- a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body
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Abstract
A miniature electroosmotic pump and fluid dispenser including the pump are disclosed. The pump comprises a plexiglass housing having a fluid inlet and outlet, a pair of spaced silver-silver chloride electrodes disposed in the housing and connected to a d.c. power source, a porous ceramic plug which has a high zeta potential relative to the fluid interposed between the electrodes, a cation exchange membrane positioned on each side of the ceramic plug between it and the electrode facing it and a fluid passageway in the housing extending from the fluid inlet to one side of the plug and from the other side of the plug to the outlet. The fluid dispenser is a modularized, self-contained unit consisting of the pump and a multicavitied fluid reservoir which contains both the fluid to be pumped and the fluid to be dispensed. Fluid is pumped from a first reservior cavity into a second cavity which already is filled with fluid. The second cavity adjoins a third cavity filled with fluid, such as drug, to be dispensed and is sealingly spearated from the third cavity by a flexible partition. The increase in volume in the second cavity distends the flexible partition into the third cavity forcing fluid therefrom.
Description
United States Patent [191 Theeuwes Dec. 2, 1975 ELECTROOSMOTIC PUMP AND FLUID DISPENSER INCLUDING SAME [75] Inventor: Felix Theeuwes, Los Altos, Calif.
[73] Assignee: Alza Corporation, Palo Alto, Calif.
[22] Filed: Aug. 15, 1974 [21] Appl. N0.: 497,685
[52] U.S. C1 417/48; 417/389; 204/180 R; 204/301 [51] Int. Cl. F04B 37/02; FO4F 11/00 [58] Field of Search 204/180 R, 299, 301; 417/48, 389
[56] References Cited UNITED STATES PATENTS 2,981,671 4/1961 Griffiths 204/301 3,016,840 l/1962 Frick 417/389 3,427,978 2/1969 Hanneman et a1 417/48 3,510,418 5/1970 Mizutani et a1 204/301 3,544,237 12/1970 Walz 417/48 3,553,092 1/1971 Mund et al. 204/301 3,568,214 3/1971 Goldschmied 417/389 3,829,370 8/1974 Bourat 204/301 Primary Examiner-C. J. Husar Assistant Examiner-Robert E. Garrett Attorney, Agent, or Firm-Thomas E. Ciotti; Paul L. Sabatine; Edward L. Mandell [57 I ABSTRACT A miniature electroosmotic pump and fluid dispenser including the pump are disclosed. The pump comprises a plexiglass housing having a fluid inlet and outlet, a pair of spaced silver-silver chloride electrodes disposed in the housing and connected to a d.c. power source, a porous ceramic plug which has a high zeta potential relative to the fluid interposed between the electrodes, a cation exchange membrane positioned on each side of the ceramic plug between it and the electrode facing it and a fluid passageway in the housing extending from the fluid inlet to one side of the plug and from the other side of the plug to the outlet. The fluid dispenser is a modularized, self-contained unit consisting of the pump and a multicavitied fluid reservoir which contains both the fluid to be pumped and the fluid to be dispensed. Fluid is pumped from a first reservior cavity into a second cavity which already is fllled with fluid. The second cavity adjoins a third cavity filled with fluid. such as drug, to be dispensed and is sealingly spearated from the third cavity by a flexible partition. The increase in volume in the second cavity distends the flexible partition into the third cavity forcing fluid therefrom.
21 Claims, 9 Drawing Figures US. Patent Dec. 2, 1975 Sheet 1 of 3 3,923,426
I5 55 2 29 2.2 41/ P1 5 f 38 EA/le Km MW MW US. Patent Dec. 2, 1975 Sheet 2 of3 3,923,426
CONTROLLER COMMAND TRANSMITTER COMMAND RECEIVER LOW VOLTAGE BATTERY SWITCH F I G.. 9
I04 M75 00 0c CONVERTER FIG. 8 PUMP ELECTROOSMOTIC PUMP AND FLUID DISPENSER INCLUDING SAME BACKGROUND OF THE INVENTION 1. Field of the Invention This invention relates to an electroosmotic pump and a fluid dispenser incorporating an electroosmotic pump.
2. Description of the Prior Art The electroosmotic phenomenon and the physics and mathematics defining it have been known for many years. Perhaps the best review of electroosmosis in the Electrokinetic Phenomenon and Their Application to Biology and Medicine, H.A. Abramson, American Chemical Society Monograph Series, the Chemical Catalog Company, Inc., NY. (1934). Electroosmosis is the opposite of electrophoresis. Generally, in electroosmosis a stationary solid body through which a fluid will pass, such as a porous body, has a matrix of fixed electrical charges and a fluid carries mobile electrical charges of opposite polarity relative to the fixed charges of the body. By applying a sufficient potential difference to the system one can cause the fluid to move through the body and exit therefrom at a predetermined positive pressure. Electrophoresis, on the other hand, involves the movement of charged particles through a stationary body of fluid.
While many practical applications of electrophoresis have been made in the separation and purification arts, little practical use of the electroosmotic phenomenon has been reported. Irreversible Thermodynamics of Electro-osmotic Effects, R.P. Rastogi, J. Scient. Ind. Res., Vol. 28, pp. 284-292 (August, 1969) says applications of electroosmosis to pump fluids, generate electricity and measure pressure or flow have been proposed and investigated. And Colloid Science I, H.R. Kruyt, Elsevier Pub. Co., (1952) p. 234 reports that several vintage German patents exist on the removal of water from porous substances by electroosmosis.
STATEMENT OF THE INVENTION This invention is an electroosmotic pump and a fluid dispenser including the pump. The pump pumps a fluid susceptible to electroosmotic transport and comprises: a housing having an inlet for the fluid and an outlet for the fluid; a pair of spaced electrodes within the housing; a d.c. electrical power source connected to the electrodes; a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid; a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body; and a fluid passageway in the housing extending from the inlet to the fluid entrance surface of the body and from the fluid exit surface of the body to the outlet.
In a preferred embodiment the pump is structured symmetrically so that the fluid flow therethrough may be reversed by reversing the electrode polarity. In such an embodiment a cation exchange membrane is interposed between the porous body and both of the electrodes.
The dispenser is a self-contained unit and in addition to the pump comprises: a source ofthe fluid pumped by the pump connected to the pump inlet; and a vessel having a first chamber for containing the fluid to be dispensed, the first chamber having an outlet port, a second chamber for receiving the fluid pumped by the pump connected to the pump outlet and a movable barrier sealingly separating the first chamber from the second chamber. Fluid is dispensed from the first chamber as fluid is pumped into the second chamber from the pump causing the fluid volume in the second chamber to increase and move the barrier into the first chamber thereby forcing a corresponding volume of fluid from the first chamber therefrom via the outlet port.
The above described pump and dispenser have several very advantageous features. The pump has no moving parts and thus is not susceptible to frictional wear. The elements of the pump which are the limiting elements in the pumps lifetime, namely the electrodes, membranes and porus body, may be modularized for easy replacement. The dispenser is readily miniaturized and is thus capable of being used as a portable unit which may be strapped or otherwise affixed to the desired dispensing site. Since the pump is driven electrically and has no moving parts it may be instantaneously turned on and off and therefore may be programmed to dispense fluid in an infinite variety of time patterns. The flow rate and output pressure may be varied by varying the electrical input to the pump. And, the dispenser is capable of being controlled remotely if desired.
Embodiments of the pump/dispenser in which the electrode polarity may be reversed have the additional advantage of being long-lived].
BRIEF DESCRIPTION OF THE DRAWINGS The drawings illustrate a small electroosmotic pump and a fluid dispenser including the pump such as might be used as a portable unit for dispensing drugs to pa tients. In the drawings:
FIG. 1 is an enlarged, sectional view of the pump;
FIG. 2 is an enlarged, exploded view of the pump of FIG. 1;
FIG. 3 is an enlarged plan view of the pump of FIG.
FIG. 4 is an enlarged side elevational view of the pump of FIG. 1;
FIG. 5 is a partly schematic, sectional view of the basic elements of the pump of FIG. 1;
FIG. 6 is a perspective view, in actual scale, of the fluid dispenser. The cylindrical member is the pump of FIG. 1 and the parallelipiped member is a reservoir module which contains the fluid to be pumped (transport fluid) and the fluid to be dispensed;
FIG. 7 is an enlarged, longitudinal sectional view of the reservoir module of the dispenser of FIG. 6;
FIG. 8 is a sectional view taken along line 8-8 of FIG. 7; and
FIG. 9 is a schematic view illustrating the power and control elements for activating and driving the pump and dispenser.
DETAILED DESCRIPTION OF PUMP AND DISPENSER OF DRAWINGS The basic innards of the electroosmotic pump are shown in FIG. 5. They are a cathode 10 connected to the negative pole of a d.c. power source, an anode 11 connected to the positive pole. of the d.c. power source, a pair of cation exchange membranes 12, I3 interposed between cathode l0 and anode 11 and a porous plug 14 interposed between membranes l2, l3. Briefly this pump transports a transport fluid (indicated by arrows in FIG. 3) by the phenomenon of electroosmosis. Porous plug 14 carries a negative surface charge relative to the transport fluid and the transport fluid carries a positive surface charge relative to the porous plug 14. When a voltage difference is applied across anode 11 and cathode 10 the transport fluid will flow through porous plug 14 generally in the direction from anode to cathode as shown by the arrows. The transport fluid flow may be reversed by simply reversing the polarity of the electrodes. Membranes 12, 13 inhibit dendrite growth of electrode material and thus increase the pumps lifetime.
The cation exchange materials from which membranes 12, 13 may be made are well known in the art and do not require extensive elaboration. In brief these materials are cross-linked polymer resins of the strong acid type. Preferred resins are the sulfonated crosslinked polystyrene variety which have a high selectivity for ions of the metal forming the electrodes. For instance, ifthe electrodes are silver, the resin preferably has a high selectivity for silver. It is also desirable that the ion exchange resin be in a salt form corresponding to the metal forming the electrodes, e.g. in the case of silver, in the silver salt form. Commercial resins are normally supplied in an alkali metal salt form and may be transformed to other salt forms by treatment with solutions of such salts, e.g. aqueous silver nitrate in the case of silver.
I The composition, porosity, pore size and the thickness of porous plug 14 significantly affect the operation of the pump, namely the potential required to drive the pump, the flow rate and output pressure. A composition which exhibits a high zeta potential relative to the transport fluid is desired. Generally speaking, the higher the zeta potential between the plug and transport fluid the lesser the potential'required to produce a given pressure and flow rate. Quartz, glass, ceramics and sulfur are suitable materials for making the plug when used with the transport fluids described below.
Plugs of such materials may be in the form of an integral, interconnected porous network, a porous walled container packed with particles of such materials, a porous matrix in which particles of such materials are dispersed, such as beads of the material in a porous polymer matrix, and the like.
, The pore size of the plug will usually be between about 0.004 p. and about 1 [.L. The porosity of the plug is not critical and will usually be between about 10 and about 70 percent.
The transport fluid should have a high zeta potential with respect to the plug, high dielectric constant, low viscosity and high specific resistance. The conductivity of the fluid has an inverse relationship to the specific resistance. For this reason the conductivity should be low, that is, less than about l millimho/cm, preferably less than 25 micromho/cm. It follows that the transport fluid should be essentially free of even small concentrations of conducting species such as various ions. It is desirable that the zeta potential between the fluid and plug be in the range of about I to 100 millivolts, the dielectric constant be between about l and 90, the viscosity between about 0.5 and centipoises and the specific resistance about 10 to 10 ohm cm. Examples of fluids which may be used are distilled water. 1,2- propanediol cyclic carbonate, ethyl alcohol and ethyl alcohol-water mixtures, formamide, furfuraldehyde, nitrobenzene, o-nitrotoluene. acetone, n-propyl alcohol, n-butyl alcohol, benzaldehyde, aniline, propionic acid, chloroform, ether, methyl alcohol, iso-butyl alcohol, methyl ethyl ketone, methyl propyl ketone, methyl acetate, ethylene bromide, benzene, glycerine, allyl alcohol, amyl alcohol, ethyl acetate, ethyl butyrate, amyl acetate, carbon tetrachloride, xylene and turpentine oil.
Once the electrodes, transport fluid and porous plug have been selected, they together with the voltage applied across the electrodes determine the flow rate and the electroosmotic pressure (the actual output pressure of the pump or dispenser is equal to the electroosmotic pressure less any back pressure inherent in the pump or dispenser). The flow rate and osmotic pressure for any given system may be calculated from the basic linear electroosmotic phenomenological equations defining the volume flow of fluid and electrical current through the porus plug 14, the Onsager relations, the Helmholz- Smoluchowski theorems, Poisseuilles Law, Ohms Law, the characteristics of the porous plug 14 and the characteristics of the transport fluid. For an embodiment such as the one illustrated in the drawings a flow rate of 0.001 to 1.0 ml/hr at an actual output pressure on the order of at least one atmosphere is desired. The voltage required to produce such flow rates and pressures may also be calculated from the above listed equations, etc. Voltages in the range of l to volts will normally be sufficient to generate the above flow rates and pressures.
FIGS. 1-4 show an entire pump unit, generally designated 15, which embodies the basic elements shown in FIG. 5. The housing of pump 15 consists of two cylindrical electrode/membrane housing members l6, 17 which are identical in structure and a pair of cylindrical porous plug housing members 18, 19 which are also identical in structure (FIG. 2). All of these housing members should be made of materials from which the transport fluid cannot leach conducting species. Various plastics from which ionic species have been preleached, such as preleached plexiglass, or metals such as stainless steel may be used. conducting metal Housing member 16 has a cylindrical recess 22 in its inner face 23 into which disc-shaped cathode l0 and disc-shaped membrane 12 snugly fit face-to-face (FIGS. 1 and 2). A thin ring 24 of a conducting metal such as silver is permanently imbedded in housing member 16 at the periphery of the bottom surface 25 of recess 22 such that ring 24 contacts the entire periphery of cathode 10 when the latter is fit into recess 22. Inner face 23 is also provided with an O-ring slot 26 for receiving an O-ring 27. Housing member 16 also has a pair of axial, diametrically opposed bores 28, 29 extending through it. A hollow sleeve 32 made of a conducting metal such as silver, platinum or gold is press fit partially into bore 29. Sleeve 32 has an integral radial collar 33 which is pressed into contact with a lead wire 34, also formed of a conductingmetal such as platinum or silver, which is permanently imbedded in member 16 and extends therein from bore 29 to contact with ring 24. The hollow of sleeve 32 is adapted to receive a lead wire (not shown) from the negative pole ofa dc. power source (also not shown in FIGS. l-4). Sleeve 32, lead wire 34 and ring 24 interconnect cathode 10 with the negative pole of the dc. power source.
Housing member l6is further provided with an L- shaped transport fluid flow channel 35 which extends axially into member 16 from face 23 and then radially outwardly therein opening at the radial surface thereof (FIGS. 3, 4). i
As indicated previously housing member 17 is identical in structure to member :16. Member 17 has a cylindrical recess 36 for receiving anode 11 and membrane 13, a pair of axial bores 37, 38 which register with bores 29,28 respectively, an O-ring slot 39 for receiving an O-ring 42 and an L-shaped transport fluid flow channel 43. Likewise it is providedwith an .imbedded anode contacting ring 44, animbedded lead wire 45 and a metal sleeve 46 within bore 38 forinterconnecting anode 11 with the positive pole. of the dc power source.
Housing members l8, 19 (FIGS. 1 and 2) hold porous plug 14. Member 18 has a cylindrical central axial bore 47 extending through it and an inner counterbore 48 thereto. As shown in .FIG. 1 one side of the porous plugfits within counterbore 48 and is seated against a shoulder49 which definesthe transition between bore 47 and counterbore 48. The inner face 52 of member 18 is provided with an O-ring slot 53 for receiving 0: ring 54 and the outer face 55 thereof is provided with an O-ring slot 56 for receiving O-ring 27. Outer face 55 also has a slot at 57 which opens through shoulder 49 into bore 47 and extends radially therefrom into registry (FIG. 1.) with the axial portion of fluid flow channel 35 in housing member 16. Said slot at 57 and bore 47 are part of the fluid flow passageway through the pump and provide a flow path for fluid exiting fromplug 14 to channel 35. Housing member 18 also has a pair of axial, diametrically opposed bores 58, 59 extending through it which align with bores 28, 29 respectively in member 16 and receive portionsofmetal sleeves 32, 46 when the pump isassembled (FIG. 1). i
As indicated previously the structure of housing member 19 is identical to that of-member l8.'Thus it too hasa central axial bore 62 and counterbore 63 thereto which receive the other side of porous'plug 14. Likewise, it is provided with an O-ring slot 64 for O- ring 54, an O-ring slot 65 for O-ring 42 and a pair of diametrically opposed axial bores 66, 67. It also has a slot at 68 which opens into bore '62" and extends radially therefrominto registry with the axial portionof fluid flow channel 43 to provide a flow path therefrom to the entrance side of porous plug '14.
As seen in FIG. 3 pump is assembled and held together in fluid tight engagement by means of six stainless steel bolts 69 (the corresponding 'nuts are not shown) which are spaced circumferentially about the edge of pump 15 and'extend axially therethrough from one side of pump 15 through to its other side. Also as seen in FIGS. 3 and 4' pump 15 is'fitted with a pair of stainless steel transport fluid conduits 72, 73 whi ch are received in the other ends of fluid flow channels 35, 43 respectively, in fluid tight engagement therewith and extend outwardly from the pump. t Y 7 FIG. 6 shows pump 15 connected to a fluid reservoir, generally designated 74. Conduits 72, 73 interconnect reservoir 74 and pump 15. The housing ofreservoir 74 consists of three housing members 75, 76, 77 the'latter two of which are identical in structure. Members 76, 77
hold the transport fluid which is pumped by pump 15 and member 75 holds the fluid to be dispensed. All
three members may be made from the same materials as the housing members of the pump.
As seen in FIGS. 7 and 8 member 76 has an elongated, bowl-shaped cavity 78 formed in its inner surface which contains the transport fluid to be pumped by pump 15. A flow passageway 79 extends from cavity 78 to a fitting 82 which is adapted to receive an end of conduit 73 in fluid tight engagement. Fitting 82 has a channel 83 which interconnects passageway 79 and conduit 73. Similarly member 77 is provided with an elongated, bowl-shaped cavity 84 which is filled with transport fluid and aflow passageway 85 extending from cavity 84 to a fitting 86 which receives an end of conduit 72 in fluid tight engagement. Fitting 86 has a channel 87 which interconnects passageway 85 and conduit 72.
Member'75 has a pair of cavities 88, 89 which are identical in shape and volume to cavities 78, 84,,respectively, and which adjoin therewith. The two sets of adjoined cavities (.78/88 and,84/89) are separated by a pair of fluid impermeable, fliud tight, flexible partitions 92, 93 respectively. Partitions 92, 93 should be made from materials which are compatible with and do not contaminate the transport fluid or the fluid t'o be dispensed. These partitions may be flexible by virtue of their composition (e.g. the use of deformable or elastomeric polymers such as natural rubber, polyisoprene, polyethylene, vinyl chloride/vinylidene chloride copolymers and the like) and/or their mechanical design (e.g. the use of bellows structures and other conventional mechanically flexible configurations). A fluid passageway 94 leads from cavity 88 to a channeled fitting 95 adapted to receive a dispensing conduit 96. Likewise a fluid'passageway 97 leads from cavity 89 to a channeled fitting 98 adapted to receive a dispensing conduit 99.
The outer surfaces of member 75 which face members 76, 77 are provided with seal channels 102, 103 which hold seals 104, 105 respectively. The reservoir 74 is assembled and held tightly together by eight stainless steel bolts 106 (and nuts not shown) (FIG. 6) which extend transversely through elements 77, 75, 76 from one side of reservoir 74 to the opposite side thereof.
FIG. 9 illustrates power and control elements which may beu'sed to run the dispenser of FIG. 4. Everything illustrated with the exceptions of the pump and co'ntroller are electronic elements of the type'well known or readily designed by persons skilled in the art. The controller may be a human being or a machine which functions-to activate the command transmitter. The command transmitter is simplya signal generator which responds to the input from the controller and generates a signal, usually electrical, which is capable of being received by the command-receiver, The command transmitter may be integral with the command receiver or remote therefrom (indicated by a curvilineararrow in FIG. 9). A remote element might be analogized to the commonly used manually operated remote controls used with television receivers.
The command receiver is powered by the same low voltage d.c.' battery which, serves as the power source for, ,the pump. (A low voltage battery is employed merely to conserve space.) Both the battery and command receiver are connected to a power. (off/on) switch. The command receiver activates the power switch in response to the signal transmitted to it by the command transmitter. The signal may of course be continuous or intermittent with the pattern of intermittency being infinitely variable. With such variety the dispenser may be made to dispense in an infinite variety of patterns.
A d.c.-d.c. converter is interposed between the power switch and the pump. The function of that converter is to take the low voltage power it receives from the low voltage battery via the switch and convert it to a higher voltage. It does this by converting the low voltage d.c. to ac, transforming the a.c. up to a higher voltage and converting the higher voltage ac. to d.c. The low voltage battery/d.c. d.c. converter combination is employed rather than a higher voltage battery because it is easier to make a small version of that combination than to make a small version of a higher voltage battery. The output from the converter is transmitted to the pump by appropriate wiring which is engaged by the metal sleeves 32, 46.
By way of example a pump and dispenser as shown in the drawings were constructed according to the following specifications:
pump housing porous plug electrodes electrode backing ring lead wire metal sleeves (battery contact) cation exchange membrane membrane-plug spacing reservoir housing reservoir cavity volumes (individual) reservoir membranes transport fluid fluid dispensed applied potential flow rate output pressure preleached lexan porcelain, 0.1 p, pore diameter. 21% porosity. 0.2 cm thick silver-silver chloride silver platinum gold plated sulfonated polystyrene (IONAC MC 3470) treated with AgNO l3.5 mils thick preleached lexan 3 ml Once a sufficient potential drop is applied across the electrodes, pumping of transport fluid will begin by the electroosmotic phenomenon described above. Specifically transport fluid will be pumped from cavity 78 via passage 79, channel 83 and conduit 73 (FIG. 7) into flow passageway 43 in pump 15 (FIG. 3, 4). From passageway 43 it flows through the slot at 68 into bore 62, through plug 14 and into bore 47 (FIG. 1). It then flows out of bore 47 via the slot at 57 into flow passageway 35. It exits from the pump via passageway 35 into conduit 72 (FIGS. 3 and 4) then into cavity 84 in reservoir 74 by way of channel 87 and passage 85 (FIG. 7). Since cavity 84 is already filled with fluid, the fluid being pumped into it causes flexible partition 93 to deform and displace into adjacent cavity 89 which is filled with the fluid (drug) to be dispensed. Such displacement squeezes the fluid in cavity 89 out of the reservoir via passage 99, channeled fitting 98 and dispensing conduit 99. From there it may be administered to a patient or other administration site using well known administration means and techniques.
Because of its symmetry pump 15 may be used to pump transport fluid in a direction reverse to that shown in FIG. 5. This may be done by simply reversing the polarity of the electrodes, i.e.. making cathode 10 an anode and anode 11 a cathode. It is solely for this reason that pump 15 is provided with membrane 13. Membrane l3 inhibits dendrite growth from electrode 11 towards electrode 10 when the electrode polarity and transport fluid flow are reversed. Otherwise it serves no function and could be eliminated if the pump was intended to pump in one direction only. When the electrode polarity is reversed transport fluid is pumped from cavity 84 of reservoir 74 via passageway 85, channel 87 and conduit 72 into fluid flow channel 35. It then passes through the slot at 57 into bore 47 and through plug 14, exiting into bore 62 on the opposite side of the plug. From bore 62 it flows through the slot at 68 into flow channel 43 and out of pump 15 by way of conduit 73. Conduit 73 carries it to reservoir 74 where it flows into cavity 78 via channel '83 and passageway 79. The increase in fluid volume in cavity 78 will ultimately cause partition 92 to distend and displace into cavity 88 thereby displacing fluid (drug) contained therein out of the reservoir by way of passage 94, channeled fitting 95 and dispensing conduit 96. Thus, by reversing the electrode polarity the entire charge, that is the contents of both of cavities 88, 89,- may be dispensed.
As mentioned briefly above membrane 12 (and membrane 13 when polarity is reversed) inhibits electrode dendrite growth and prolongs and pumps lifetime. In the 'system-metal from'the-anode deposits on the cathode. In a low conductivity fluid current distribution on the cathode is not uniform but is localized in spots on the cathode surface. Metal deposits more rapidly on these spots of higher current density to form the needle like dendrites. Dendrite growth occurs in the direction of least resistance between the electrodes and if left unhindered initially occurs axially between the cathode l0 and plug 11. 'At the plug the dendrite growth is through the plugs pores-which of course blocks the pores making the plug less porous and less efficient. The dendrite will grow entirely through the 'plug and then axially therefrom into contact with the anode-which of course short circuits the pump and renders it inoperable.
By .placing a cation exchange membrane between cathode l0 and plug 14 the dendrite growth is substantiallyinhibited. Generally it was found that an increase in membrane thickness increased the inhibition and pump lifetime. The thickness of the membrane in pump embodiments such as for use in the drug dispenser of the drawings will usually be.between about 200 microns and 2,000 microns.
It was also found that dendrite growth may be controlled by periodically reversing the electrode polarity in the manner described above. Such reversal also effects a reversal of dendrite growth, thereby shrinking and eroding the dendrites formed during operation of the pump with the original electrode polarity and vice versa. Accordingly it is desirable to periodically reverse the electrode potential if such operation is compatible with other aspects of the pump operation and use.
Denorite growth also may be controlled by operating the pump in an on/off mode. Such control may be effected by limiting the on mode to approximately the time it takes the current distribution to localize suffrciently to initiate dendrite growth (this time may be determinedempirically forany given system) and maintaining the off mode for a time sufflcientto permit ion concentration gradients at the electrodes to randomize to a significant extent.
In the above described dispenser the nature of the fluid being dispensed is not critical. Any flowable liquid, gas or slurry may be charged to the reservoir and dispensed therefrom by the pump 15 as described above. As indicated previously the device illustrated in the drawingswasdesigned particularly for dispensing liquid drugs, solutions of drugs or dispersions of drugs.
Various modifications of the specific embodiments of the invention described above will be obvious to those of skill in the art. For instance other porous plug materials and/or other cation exchange membranes might be employed. Also, the flexible membranes 92, 93 might be replaced with other types of movable barriers such as pistons. Or the pump may be used as a suction pump such as in a fluid sampling device. In such a device the pump is used to create a pressure differential across a moveable barrier contained within a sampling vessel, the differential being employed to suck the desired sample into the vessel. These and other obvious variations are intended to be within the scope and spirit of the following claims.
I claim:
1. An electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising:
a. a housing having an inlet for the fluid and an outlet for the fluid;
b. a pair of spaced electrodes disposed within the housing;
0. a d.c. electrical power source connected to the electrodes;
d. a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid;
e. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of said porous body; and
f. a fluid passageway in the housing extending from the inlet to said fluid entrance surface and from said fluid exit surface to the outlet.
2. The electroosmotic pump of claim 1 wherein the pore size of the porous body is between about 0.004 and about in.
3. The electroosmotic pump of claim 2 wherein the zeta potential between the porous body and the fluid is in the range of about 1 millivolt to 100 millivolts.
4. The.electroosmotic pump of claim 2 wherein the porous body is made from quartz, glass, ceramic or sulfur.
5. The electroosmotic pump of claim 1 wherein the cation exchange membrane is made of a cross-linked polymer resin of the strong acid type.
6. The electroosmotic pump of claim 5 wherein the cross-linked polymer resin is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
7. The electroosmotic pump of claim 6 wherein the resin is in a salt form corresponding to the metal forming the electrodes.
8. The electroosmotic pump of claim 1 including:
g. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body.
9. The electroosmotic pump of claim 8 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversedby reversing the electrode polarity.
10. The electroosmotic pump of claim 1 including:
g. means connected to said power source for switching said power. source on and off in a predetermined sequence.
11. The electroosmotic pump of claim 1 wherein the potential applied across the electrodes from the power source is in the range of 1 volt to volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
12. The electroosmotic pump of claim 9 including:
h. means connected to said power source for switching said power source on and off in a predetermined sequence and wherein the pore size of the porous body is between about 0.004;. and about In, the zeta potential between the porous body and the fluid is in the range of l millivolt to 100 millivolts, the ion exchange membrane is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about l.0 ml/hr.
13. A dispenser for dispensing a fluid comprising:
A. an electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising:
a. a housing having an inlet for the fluid and an outlet for the fluid;
b. a pair of spaced electrodes disposed within the housing;
0. a d.c. electrical power source connected to the electrodes;
d. a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid;
e. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of said porous body; and
f. a fluid passageway in the housing extending from the inlet of said fluid entrance surface and from said fluid exit surface to the outlet;
B. a source of the fluid to be pumped by the electroosmotic pump connected tosaid inlet; and
C. a vessel having a. a first chamber for containing the fluid to be dis pensed having an outlet port therefor;
b. a second chamber for receiving the fluid to be pumped by the electroosmotic pump connected to the outlet of the pump housing. and
c. a movable barrier sealingly separating the first chamber from the second chamber and adapted to move in response to an increase in the volume of fluid received in the first chamber so as to dispense a correspoding volume of fluid contained in the second chamber therefrom via the outlet port.
14. The dispenser of claim 13 wherein the movable barrier is a flexible partition.
15. The dispenser of claim 13 wherein the fluid to be dispensed is a drug.
16. The dispenser of claim 13 wherein the pore size of the porous body is between about 0.00411, and about lg.
17. The dispenser of claim 16 wherein the zeta potential between the porous body and the fluid is in the range of about 1 millivolt to 100 millivolts.
18. The dispenser of claim 13 wherein the cation exchange membrane is made of sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
19. The dispenser of claim 13 wherein the electroosmotic pump includes:
g. means connected to said power source for switching said power source on and off in a predetermined sequence.
20. The dispenser of claim 13 wherein the potential applied across the electrodes from the power source is in the range of 1 volt to lOO volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
21. The dispenser of claim 13 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversed by reversing the electrode polarity, and pore size of the porous body is between about 0.004p/and about l,u., the zeta potential between the porous body and the fluid is in the range of l millivolt to I00 millivolts. the cation ion exchange membrane is made of a sulfonated crosslinked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr and the pump includes:
g. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body; and
h. means connected to said power source for switching said power source on and off in predetermined sequence.
Claims (21)
1. An electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising: a. a housing having an inlet for the fluid and an outlet for the fluid; b. a pair of spaced electrodes disposed within the housing; c. a d.c. electrical power source connected to the electrodes; d. a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid; e. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of said porous body; and f. a fluid passageway in the housing extending from the inlet to said fluid entrance surface and from said fluid exit surface to the outlet.
2. The electroosmotic pump of claim 1 wherein the pore size of the porous body is between about 0.004 Mu and about 1 Mu .
3. The electroosmotic pump of claim 2 wherein the zeta potential between the porous body and the fluid is in the range of about 1 millivolt to 100 millivolts.
4. The electroosmotic pump of claim 2 wherein the porous body is mAde from quartz, glass, ceramic or sulfur.
5. The electroosmotic pump of claim 1 wherein the cation exchange membrane is made of a cross-linked polymer resin of the strong acid type.
6. The electroosmotic pump of claim 5 wherein the cross-linked polymer resin is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
7. The electroosmotic pump of claim 6 wherein the resin is in a salt form corresponding to the metal forming the electrodes.
8. The electroosmotic pump of claim 1 including: g. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body.
9. The electroosmotic pump of claim 8 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversed by reversing the electrode polarity.
10. The electroosmotic pump of claim 1 including: g. means connected to said power source for switching said power source on and off in a predetermined sequence.
11. The electroosmotic pump of claim 1 wherein the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
12. The electroosmotic pump of claim 9 including: h. means connected to said power source for switching said power source on and off in a predetermined sequence and wherein the pore size of the porous body is between about 0.004 Mu and about 1 Mu , the zeta potential between the porous body and the fluid is in the range of 1 millivolt to 100 millivolts, the ion exchange membrane is a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
13. A dispenser for dispensing a fluid comprising: A. an electroosmotic pump for pumping a fluid susceptible to electroosmotic transport comprising: a. a housing having an inlet for the fluid and an outlet for the fluid; b. a pair of spaced electrodes disposed within the housing; c. a d.c. electrical power source connected to the electrodes; d. a porous body interposed between the electrodes in spaced relationship thereto, the porous body having a fluid entrance surface and a fluid exit surface and being capable of carrying a surface charge of opposite polarity relative to the surface charge of the fluid; e. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of said porous body; and f. a fluid passageway in the housing extending from the inlet of said fluid entrance surface and from said fluid exit surface to the outlet; B. a source of the fluid to be pumped by the electroosmotic pump connected to said inlet; and C. a vessel having a. a first chamber for containing the fluid to be dispensed having an outlet port therefor; b. a second chamber for receiving the fluid to be pumped by the electroosmotic pump connected to the outlet of the pump housing, and c. a movable barrier sealingly separating the first chamber from the second chamber and adapted to move in response to an increase in the volume of fluid received in the first chamber so as to dispense a correspoding volume of fluid contained in the second chamber therefrom via the outlet port.
14. The dispenser of claim 13 wherein the movable barrier is a flexible partition.
15. The dispenser of claim 13 wherein the fluid to be dispensed is a drug.
16. The dispenser of claim 13 wherein the pore size of the porous body is between about 0.004 Mu and about 1 Mu .
17. The dispenser of claiM 16 wherein the zeta potential between the porous body and the fluid is in the range of about 1 millivolt to 100 millivolts.
18. The dispenser of claim 13 wherein the cation exchange membrane is made of sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes.
19. The dispenser of claim 13 wherein the electroosmotic pump includes: g. means connected to said power source for switching said power source on and off in a predetermined sequence.
20. The dispenser of claim 13 wherein the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr.
21. The dispenser of claim 13 wherein the pump is generally symmetrical about the porous body whereby the fluid flow through the pump may be reversed by reversing the electrode polarity, and pore size of the porous body is between about 0.004 Mu and about 1 Mu , the zeta potential between the porous body and the fluid is in the range of 1 millivolt to 100 millivolts, the cation ion exchange membrane is made of a sulfonated cross-linked polystyrene which has a high selectivity for ions of the metal forming the electrodes and the potential applied across the electrodes from the power source is in the range of 1 volt to 100 volts and the flow rate of fluid through the pump is in the range of about 0.001 ml/hr to about 1.0 ml/hr and the pump includes: g. a cation exchange membrane interposed between the porous body and the electrode on the fluid exit surface side of the porous body; and h. means connected to said power source for switching said power source on and off in predetermined sequence.
Priority Applications (1)
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US497685A US3923426A (en) | 1974-08-15 | 1974-08-15 | Electroosmotic pump and fluid dispenser including same |
Applications Claiming Priority (1)
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US497685A US3923426A (en) | 1974-08-15 | 1974-08-15 | Electroosmotic pump and fluid dispenser including same |
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US3923426A true US3923426A (en) | 1975-12-02 |
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US497685A Expired - Lifetime US3923426A (en) | 1974-08-15 | 1974-08-15 | Electroosmotic pump and fluid dispenser including same |
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Cited By (180)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4381006A (en) * | 1980-11-10 | 1983-04-26 | Abbott Laboratories | Continuous low flow rate fluid dispenser |
US4484923A (en) * | 1982-03-25 | 1984-11-27 | Alza Corporation | Method for administering immunopotentiator |
US4593534A (en) * | 1985-02-21 | 1986-06-10 | Analytic Power Corporation | Electrochemically driven heat pump |
WO1987002593A1 (en) * | 1985-10-28 | 1987-05-07 | California Institute Of Technology | Method and apparatus using a solid electrolyte in the form of a disk for the separation or pumping of oxygen |
US4687423A (en) * | 1985-06-07 | 1987-08-18 | Ivac Corporation | Electrochemically-driven pulsatile drug dispenser |
US4715850A (en) * | 1984-12-06 | 1987-12-29 | Controlled Release Technologies, Inc. | Therapeutic agent delivery system and method |
US4822339A (en) * | 1984-12-06 | 1989-04-18 | Controlled Release Technologies, Inc. | Therapeutic agent delivery system and method |
US4978337A (en) * | 1988-09-08 | 1990-12-18 | Alza Corporation | Formulation chamber with exterior electrotransport delivery device |
US5041107A (en) * | 1989-10-06 | 1991-08-20 | Cardiac Pacemakers, Inc. | Electrically controllable, non-occluding, body implantable drug delivery system |
US5080559A (en) * | 1990-01-23 | 1992-01-14 | The United States Of America As Represented By The United States Department Of Energy | Liquid metal electric pump |
US5533995A (en) * | 1991-11-13 | 1996-07-09 | Elan Corporation, Plc | Passive transdermal device with controlled drug delivery |
WO1999016162A1 (en) * | 1997-09-25 | 1999-04-01 | Caliper Technologies Corporation | Micropump |
US5964997A (en) * | 1997-03-21 | 1999-10-12 | Sarnoff Corporation | Balanced asymmetric electronic pulse patterns for operating electrode-based pumps |
US6001251A (en) * | 1990-08-22 | 1999-12-14 | University Of Pittsburgh | Material for separating submicron particles |
US6013164A (en) * | 1997-06-25 | 2000-01-11 | Sandia Corporation | Electokinetic high pressure hydraulic system |
WO2000055502A1 (en) * | 1999-03-18 | 2000-09-21 | Sandia Corporation | Electrokinetic high pressure hydraulic system |
WO2001026714A1 (en) | 1999-10-12 | 2001-04-19 | Durect Corporation | Regulation of drug delivery through flow diversion |
US6406605B1 (en) | 1999-06-01 | 2002-06-18 | Ysi Incorporated | Electroosmotic flow controlled microfluidic devices |
US6409698B1 (en) * | 2000-11-27 | 2002-06-25 | John N. Robinson | Perforate electrodiffusion pump |
US20020189947A1 (en) * | 2001-06-13 | 2002-12-19 | Eksigent Technologies Llp | Electroosmotic flow controller |
US20030010638A1 (en) * | 2001-06-15 | 2003-01-16 | Hansford Derek J. | Nanopump devices and methods |
US20030052007A1 (en) * | 2001-06-13 | 2003-03-20 | Paul Phillip H. | Precision flow control system |
US6541021B1 (en) | 1999-03-18 | 2003-04-01 | Durect Corporation | Devices and methods for pain management |
US20030088236A1 (en) * | 1999-03-18 | 2003-05-08 | Johnson Randolph Mellus | Implantable devices and methods for treatment of pain by delivery of fentanyl and fentanyl congeners |
US6606251B1 (en) | 2002-02-07 | 2003-08-12 | Cooligy Inc. | Power conditioning module |
US20030164231A1 (en) * | 2001-09-28 | 2003-09-04 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
US6619925B2 (en) * | 2001-10-05 | 2003-09-16 | Toyo Technologies, Inc. | Fiber filled electro-osmotic pump |
US20030206806A1 (en) * | 2002-05-01 | 2003-11-06 | Paul Phillip H. | Bridges, elements and junctions for electroosmotic flow systems |
US20030205582A1 (en) * | 2002-05-01 | 2003-11-06 | Joshi Ashok V. | Fluid delivery device having an electrochemical pump with an anionic exchange membrane and associated method |
US20030212379A1 (en) * | 2002-02-26 | 2003-11-13 | Bylund Adam David | Systems and methods for remotely controlling medication infusion and analyte monitoring |
WO2004022069A1 (en) | 2002-09-06 | 2004-03-18 | Durect Corporation | Delivery of modulators of glutamate-mediated neurotransmission to the inner ear |
US6719535B2 (en) | 2002-01-31 | 2004-04-13 | Eksigent Technologies, Llc | Variable potential electrokinetic device |
US20040074784A1 (en) * | 2002-10-18 | 2004-04-22 | Anex Deon S. | Electrokinetic device having capacitive electrodes |
US20040096977A1 (en) * | 2002-11-15 | 2004-05-20 | Rakestraw David J. | Particulate processing system |
US20040101421A1 (en) * | 2002-09-23 | 2004-05-27 | Kenny Thomas W. | Micro-fabricated electrokinetic pump with on-frit electrode |
US20040102476A1 (en) * | 2002-11-25 | 2004-05-27 | Chan Tai Wah | High concentration formulations of opioids and opioid derivatives |
US20040104010A1 (en) * | 2002-11-01 | 2004-06-03 | Cooligy, Inc. | Interwoven manifolds for pressure drop reduction in microchannel heat exchangers |
US20040104022A1 (en) * | 2002-11-01 | 2004-06-03 | Cooligy, Inc. | Method and apparatus for flexible fluid delivery for cooling desired hot spots in a heat producing device |
US20040112585A1 (en) * | 2002-11-01 | 2004-06-17 | Cooligy Inc. | Method and apparatus for achieving temperature uniformity and hot spot cooling in a heat producing device |
US6770183B1 (en) * | 2001-07-26 | 2004-08-03 | Sandia National Laboratories | Electrokinetic pump |
US20040151962A1 (en) * | 2003-01-31 | 2004-08-05 | Paul Adams | Fuel cartridge for fuel cells |
US20040148959A1 (en) * | 2003-01-31 | 2004-08-05 | Cooligy, Inc. | Remedies to prevent cracking in a liquid system |
FR2850677A1 (en) * | 2003-01-30 | 2004-08-06 | Seb Sa | Ironing apparatus, has electro-osmotic pump that transfers water from water container to evaporation chamber, and includes porous body comprising alluvial sand grains or mixed grains comprising ion-exchange resin granules |
WO2004073822A2 (en) * | 2003-02-21 | 2004-09-02 | Sophion Bioscience A/S | Sieve electroosmotic pump |
WO2004076857A2 (en) * | 2003-01-31 | 2004-09-10 | Cooligy, Inc. | Method and apparatus for low-cost electrokinetic pump manufacturing |
US20040182560A1 (en) * | 2003-03-17 | 2004-09-23 | Cooligy Inc. | Apparatus and method of forming channels in a heat-exchanging device |
US6805841B2 (en) | 2001-05-09 | 2004-10-19 | The Provost Fellows And Scholars Of The College Of The Holy And Undivided Trinity Of Queen Elizabeth Near Dublin | Liquid pumping system |
US20040206477A1 (en) * | 2002-11-01 | 2004-10-21 | Cooligy, Inc. | Method and apparatus for efficient vertical fluid delivery for cooling a heat producing device |
WO2004101444A1 (en) * | 2003-05-12 | 2004-11-25 | Clean Water Gesellschaft Für Wasseraufbereitungs- Technik Mbh | Method and device for the purification, especially desalination, of water |
US20040235446A1 (en) * | 2000-12-21 | 2004-11-25 | Flaherty J. Christopher | Medical apparatus remote control and method |
US20040235181A1 (en) * | 2002-11-15 | 2004-11-25 | Arnold Don W. | Processing of particles |
US20040241004A1 (en) * | 2003-05-30 | 2004-12-02 | Goodson Kenneth E. | Electroosmotic micropump with planar features |
US20040241006A1 (en) * | 2001-10-02 | 2004-12-02 | Rafael Taboryski | Corbino disc electroosmotic flow pump |
US20040247450A1 (en) * | 2001-10-02 | 2004-12-09 | Jonatan Kutchinsky | Sieve electrooosmotic flow pump |
US20050016853A1 (en) * | 2003-07-21 | 2005-01-27 | Paul Phillip H. | Bridges for electroosmotic flow systems |
US20050034842A1 (en) * | 2003-08-11 | 2005-02-17 | David Huber | Electroosmotic micropumps with applications to fluid dispensing and field sampling |
US20050044352A1 (en) * | 2001-08-30 | 2005-02-24 | Riverhead Networks, Inc. | Protecting against spoofed DNS messages |
US20050070883A1 (en) * | 2000-11-29 | 2005-03-31 | Brown James E | Devices and methods for controlled delivery from a drug delivery device |
US20050084385A1 (en) * | 2002-09-23 | 2005-04-21 | David Corbin | Micro-fabricated electrokinetic pump |
US20050143789A1 (en) * | 2001-01-30 | 2005-06-30 | Whitehurst Todd K. | Methods and systems for stimulating a peripheral nerve to treat chronic pain |
US20050154419A1 (en) * | 2001-01-30 | 2005-07-14 | Whitehurst Todd K. | Methods and systems for stimulating a nerve originating in an upper cervical spine area to treat a medical condition |
US20050161334A1 (en) * | 1999-06-01 | 2005-07-28 | Paul Phillip H. | Electroosmotic flow systems |
US20050230080A1 (en) * | 2004-04-19 | 2005-10-20 | Paul Phillip H | Electrokinetic pump driven heat transfer system |
US20050233195A1 (en) * | 2004-04-19 | 2005-10-20 | Arnold Don W | Fuel cell system with electrokinetic pump |
US20050247558A1 (en) * | 2002-07-17 | 2005-11-10 | Anex Deon S | Electrokinetic delivery systems, devices and methods |
US20060036293A1 (en) * | 2004-08-16 | 2006-02-16 | Whitehurst Todd K | Methods for treating gastrointestinal disorders |
US20060052768A1 (en) * | 2002-05-01 | 2006-03-09 | Microlin, L.C. | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US20060064140A1 (en) * | 2001-01-30 | 2006-03-23 | Whitehurst Todd K | Methods and systems for stimulating a trigeminal nerve to treat a psychiatric disorder |
US7021369B2 (en) | 2003-07-23 | 2006-04-04 | Cooligy, Inc. | Hermetic closed loop fluid system |
US20060116663A1 (en) * | 2002-05-01 | 2006-06-01 | Joshi Ashok V | Electro-osmotic fluid delivery device and method |
US20060116641A1 (en) * | 2002-05-01 | 2006-06-01 | Microlin, L.C. | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US20060129201A1 (en) * | 2004-12-06 | 2006-06-15 | Lee Philip H J | Stimulation of the stomach in response to sensed parameters to treat obesity |
US20060131174A1 (en) * | 2004-12-20 | 2006-06-22 | Paul Phillip H | Electrokinetic device employing a non-Newtonian liquid |
US20060149340A1 (en) * | 2002-07-31 | 2006-07-06 | Karunasiri Rankiri T | Systems and methods for providing power to one or more implantable devices |
US20060161217A1 (en) * | 2004-12-21 | 2006-07-20 | Jaax Kristen N | Methods and systems for treating obesity |
US20060185665A1 (en) * | 2005-02-22 | 2006-08-24 | Bachinski Thomas J | Sauna fireplace |
US20060194724A1 (en) * | 2005-02-25 | 2006-08-31 | Whitehurst Todd K | Methods and systems for nerve regeneration |
US20060206165A1 (en) * | 2005-03-14 | 2006-09-14 | Jaax Kristen N | Occipital nerve stimulation to treat headaches and other conditions |
US20060207883A1 (en) * | 2004-10-19 | 2006-09-21 | Koval Carl A | Electrochemical high pressure pump |
US20060235484A1 (en) * | 2005-03-14 | 2006-10-19 | Jaax Kristen N | Stimulation of a stimulation site within the neck or head |
US20060247728A1 (en) * | 2004-12-21 | 2006-11-02 | Foster Allison M | Methods and systems for treating autism by decreasing neural activity within the brain |
US7134486B2 (en) | 2001-09-28 | 2006-11-14 | The Board Of Trustees Of The Leeland Stanford Junior University | Control of electrolysis gases in electroosmotic pump systems |
US20060264913A1 (en) * | 2002-09-06 | 2006-11-23 | Poutiatine Andrew I | Implantable flow regulator with failsafe mode and reserve drug supply |
US20060293723A1 (en) * | 2003-12-19 | 2006-12-28 | Whitehurst Todd K | Skull-mounted electrical stimulation system and method for treating patients |
US20070014820A1 (en) * | 2003-01-23 | 2007-01-18 | Dana Litmanovitz | Opioid formulations |
US20070021735A1 (en) * | 2005-07-15 | 2007-01-25 | Sai Bhavaraju | Dual membrane electro-osmotic fluid delivery device |
US20070025869A1 (en) * | 2005-07-15 | 2007-02-01 | Gordon John H | Fluid Delivery Device |
US20070049988A1 (en) * | 2005-03-14 | 2007-03-01 | Rafael Carbunaru | Optimal electrode contact polarity configurations for implantable stimulation systems |
US20070066997A1 (en) * | 2005-09-21 | 2007-03-22 | He Tom X | Methods and systems for placing an implanted stimulator for stimulating tissue |
WO2007034267A1 (en) * | 2005-07-07 | 2007-03-29 | Obshchestvo S Ogranichennoj Otvetstvennostyu 'institut Rentgenovskoj Optiki' | Electrokinetic micropump |
US20070068815A1 (en) * | 2005-09-26 | 2007-03-29 | Industrial Technology Research Institute | Micro electro-kinetic pump having a nano porous membrane |
US20070077547A1 (en) * | 2001-12-31 | 2007-04-05 | The Provost Fellows And Scholars Of The College Of The Holy And Undivided Trinity Of Queen Elizabeth | Assay assembly |
US20070083240A1 (en) * | 2003-05-08 | 2007-04-12 | Peterson David K L | Methods and systems for applying stimulation and sensing one or more indicators of cardiac activity with an implantable stimulator |
US20070100393A1 (en) * | 2002-05-24 | 2007-05-03 | Whitehurst Todd K | Treatment of movement disorders by brain stimulation |
WO2007052377A1 (en) * | 2005-11-02 | 2007-05-10 | Niigata Tlo Corporation | Micropump and micro fluid chip |
US20070117841A1 (en) * | 2003-10-24 | 2007-05-24 | Ozes Osman N | Use of pirfenidone in therapeutic regimens |
WO2007059010A2 (en) | 2005-11-14 | 2007-05-24 | Enterprise Partners Venture Capital | Stem cell factor therapy for tissue injury |
US20070156180A1 (en) * | 2005-12-30 | 2007-07-05 | Jaax Kristen N | Methods and systems for treating osteoarthritis |
US20070201204A1 (en) * | 2006-02-16 | 2007-08-30 | Girish Upadhya | Liquid cooling loops for server applications |
US20070219595A1 (en) * | 2006-03-14 | 2007-09-20 | Advanced Bionics Corporation | Stimulator system with electrode array and the method of making the same |
US7293423B2 (en) | 2004-06-04 | 2007-11-13 | Cooligy Inc. | Method and apparatus for controlling freezing nucleation and propagation |
WO2005113419A3 (en) * | 2004-04-21 | 2007-12-27 | Eksigent Technologies Llc | Electrokinetic delivery systems, devices and methods |
US20080027513A1 (en) * | 2004-07-09 | 2008-01-31 | Advanced Bionics Corporation | Systems And Methods For Using A Butterfly Coil To Communicate With Or Transfer Power To An Implantable Medical Device |
US7347746B1 (en) | 2006-10-27 | 2008-03-25 | Boston Scientific Neuromodulation Corporation | Receptacle connector assembly |
US20080131757A1 (en) * | 2006-12-04 | 2008-06-05 | Casio Computer Co., Ltd. | Gas-liquid separating device and electric power generating apparatus |
US20080209876A1 (en) * | 2007-02-07 | 2008-09-04 | Zettacore, Inc. | Liquid Composite Compositions Using Non-Volatile Liquids and Nanoparticles and Uses Thereof |
US20080260542A1 (en) * | 2004-06-07 | 2008-10-23 | Nano Fusion Technologies, Inc | Electroosmotic Pump System and Electroosmotic Pump |
US7445528B1 (en) | 2006-09-29 | 2008-11-04 | Boston Scientific Neuromodulation Corporation | Connector assemblies |
US20090005727A1 (en) * | 2006-03-09 | 2009-01-01 | Searete Llc | Acoustically controlled substance delivery device |
US20090126813A1 (en) * | 2005-03-30 | 2009-05-21 | Nano Fusion Technologies, Inc. | Liquid-Transport Device and System |
US20090136362A1 (en) * | 2005-03-30 | 2009-05-28 | Nano Fusion Technologies Inc. | Electroosmosis Pump and Liquid Feeding Device |
US20090162249A1 (en) * | 2006-03-09 | 2009-06-25 | Searete Llc | Acoustically controlled reaction device |
EP2098588A1 (en) * | 2006-11-22 | 2009-09-09 | Altair Corporation | Pipette core member, pipette, and pipette device |
US7591302B1 (en) | 2003-07-23 | 2009-09-22 | Cooligy Inc. | Pump and fan control concepts in a cooling system |
US20090270944A1 (en) * | 2004-12-22 | 2009-10-29 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating a psychotic disorder |
US20090281605A1 (en) * | 2004-05-28 | 2009-11-12 | Boston Scientific Neuromodulation Corporation | Engagement tool for implantable medical devices |
US20100030287A1 (en) * | 2004-12-21 | 2010-02-04 | Boston Scientific Neuromodulation Corporation | Methods for treating autism |
US20100030185A1 (en) * | 2006-01-18 | 2010-02-04 | Searete Llc | Remote controller for substance delivery system |
US20100076415A1 (en) * | 2005-11-09 | 2010-03-25 | Searete Llc | Remote control of substance delivery system |
US7713229B2 (en) | 2003-11-06 | 2010-05-11 | Lifescan, Inc. | Drug delivery pen with event notification means |
US7715194B2 (en) | 2006-04-11 | 2010-05-11 | Cooligy Inc. | Methodology of cooling multiple heat sources in a personal computer through the use of multiple fluid-based heat exchanging loops coupled via modular bus-type heat exchangers |
US20100124679A1 (en) * | 2008-11-20 | 2010-05-20 | Mti Microfuel Cells, Inc. | Method for increasing the durability of direct oxidation fuel cells |
US7729758B2 (en) | 2005-11-30 | 2010-06-01 | Boston Scientific Neuromodulation Corporation | Magnetically coupled microstimulators |
CN101153618B (en) * | 2006-09-27 | 2010-06-23 | 卡西欧计算机株式会社 | Connecting structure of a liquid sending apparatus, fuel-cell type electricity generating apparatus, and electronic device |
US20100222770A1 (en) * | 2005-07-01 | 2010-09-02 | John Howard Gordon | Fluid delivery device with a diffusion membrane for fast response time |
US7799037B1 (en) | 2000-02-24 | 2010-09-21 | Boston Scientific Neuromodulation Corporation | Surgical insertion tool |
WO2010107739A2 (en) | 2009-03-18 | 2010-09-23 | The Board Of Trustees Of The Leland Stanford Junior University | Methods and compositions of treating a flaviviridae family viral infection |
US7806168B2 (en) | 2002-11-01 | 2010-10-05 | Cooligy Inc | Optimal spreader system, device and method for fluid cooled micro-scaled heat exchange |
EP2236423A2 (en) | 2003-12-01 | 2010-10-06 | Société BIC | Method and apparatus for filling a fuel container |
US7835803B1 (en) | 2006-01-17 | 2010-11-16 | Boston Scientific Neuromodulation Corporation | Lead assemblies with one or more switching networks |
US7848803B1 (en) | 2005-03-14 | 2010-12-07 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US7867592B2 (en) | 2007-01-30 | 2011-01-11 | Eksigent Technologies, Inc. | Methods, compositions and devices, including electroosmotic pumps, comprising coated porous surfaces |
US7890176B2 (en) | 1998-07-06 | 2011-02-15 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating chronic pelvic pain |
US7896868B2 (en) | 2005-12-13 | 2011-03-01 | The Invention Science Fund I, Llc | Method and system for control of osmotic pump device |
US20110052431A1 (en) * | 2008-02-08 | 2011-03-03 | Osmotex Ag | Electro-osmotic pump |
US7913719B2 (en) * | 2006-01-30 | 2011-03-29 | Cooligy Inc. | Tape-wrapped multilayer tubing and methods for making the same |
US20110072914A1 (en) * | 2008-02-14 | 2011-03-31 | Illumina, Inc. | Flow Cells And Manifolds Having An Electroosmotic Pump |
WO2011057654A1 (en) * | 2009-11-13 | 2011-05-19 | Ab Skf | Bearing assembly with active oil lubrication |
US20110223233A1 (en) * | 2001-09-14 | 2011-09-15 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
EP2390262A1 (en) | 2003-05-16 | 2011-11-30 | Intermune, Inc. | Synthetic chemokine receptor ligands and methods of use thereof |
US8080380B2 (en) | 1999-05-21 | 2011-12-20 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US8152477B2 (en) | 2005-11-23 | 2012-04-10 | Eksigent Technologies, Llc | Electrokinetic pump designs and drug delivery systems |
US8157001B2 (en) | 2006-03-30 | 2012-04-17 | Cooligy Inc. | Integrated liquid to air conduction module |
US8251672B2 (en) | 2007-12-11 | 2012-08-28 | Eksigent Technologies, Llc | Electrokinetic pump with fixed stroke volume |
US8250877B2 (en) | 2008-03-10 | 2012-08-28 | Cooligy Inc. | Device and methodology for the removal of heat from an equipment rack by means of heat exchangers mounted to a door |
WO2012175698A1 (en) | 2011-06-23 | 2012-12-27 | Université Libre de Bruxelles | Therapeutic use of all-trans retinoic acid (atra) in patients suffering from alcoholic liver disease |
US20120325941A1 (en) * | 2010-03-04 | 2012-12-27 | Toppan Printing Co., Ltd. | Odor generator |
WO2013033636A2 (en) | 2011-09-01 | 2013-03-07 | University Of Southern California | Methods for preparing high throughput peptidomimetics, orally bioavailable drugs and compositions containing same |
US8401654B1 (en) | 2006-06-30 | 2013-03-19 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating one or more effects of deafferentation |
US8423155B1 (en) | 2005-03-14 | 2013-04-16 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US8481268B2 (en) | 1999-05-21 | 2013-07-09 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US8504163B1 (en) | 2006-06-30 | 2013-08-06 | Boston Scientific Neuromodulation Corporation | Cranially mounted stimulation systems and methods |
US8515541B1 (en) | 2004-12-22 | 2013-08-20 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating post-stroke disorders |
US8529551B2 (en) | 2005-11-09 | 2013-09-10 | The Invention Science Fund I, Llc | Acoustically controlled substance delivery device |
US8568388B2 (en) | 2005-11-09 | 2013-10-29 | The Invention Science Fund I, Llc | Remote controlled in situ reaction device |
WO2014019775A1 (en) * | 2012-07-31 | 2014-02-06 | General Electric Company | Devices and systems for isolating biomolecules and associated methods thereof |
US8906000B2 (en) | 2005-11-09 | 2014-12-09 | The Invention Science Fund I, Llc | Injectable controlled release fluid delivery system |
US8979511B2 (en) | 2011-05-05 | 2015-03-17 | Eksigent Technologies, Llc | Gel coupling diaphragm for electrokinetic delivery systems |
US8992475B2 (en) | 1998-08-18 | 2015-03-31 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US20150101930A1 (en) * | 2013-10-11 | 2015-04-16 | The Board Of Regents Of The University Of Oklahoma | Electroosmotic pump unit and assembly |
US20150126928A1 (en) * | 2012-07-06 | 2015-05-07 | Sanofi-Aventis Deutschland Gmbh | Drug delivery device |
US9067047B2 (en) | 2005-11-09 | 2015-06-30 | The Invention Science Fund I, Llc | Injectable controlled release fluid delivery system |
US9103331B2 (en) | 2011-12-15 | 2015-08-11 | General Electric Company | Electro-osmotic pump |
US9297571B1 (en) | 2008-03-10 | 2016-03-29 | Liebert Corporation | Device and methodology for the removal of heat from an equipment rack by means of heat exchangers mounted to a door |
US9327069B2 (en) | 2004-12-21 | 2016-05-03 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating a medical condition by promoting neural remodeling within the brain |
EP3025727A1 (en) | 2008-10-02 | 2016-06-01 | The J. David Gladstone Institutes | Methods of treating liver disease |
US9358393B1 (en) | 2004-11-09 | 2016-06-07 | Andres M. Lozano | Stimulation methods and systems for treating an auditory dysfunction |
US9364484B2 (en) | 2011-12-06 | 2016-06-14 | The Board Of Trustees Of The Leland Stanford Junior University | Methods and compositions for treating viral diseases |
WO2017023863A1 (en) | 2015-07-31 | 2017-02-09 | Research Institute At Nationwide Children's Hospital | Peptides and antibodies for the removal of biofilms |
WO2017066719A2 (en) | 2015-10-14 | 2017-04-20 | Research Institute At Nationwide Children's Hospital | Hu specific interfering agents |
EP3070331A4 (en) * | 2013-08-26 | 2017-05-31 | Sogang University Research Foundation | Electroosmotic pump and fluid pumping system having same |
WO2018129078A1 (en) | 2017-01-04 | 2018-07-12 | Research Institute At Nationwide Children's Hospital | Dnabii vaccines and antibodies with enhanced activity |
WO2018129092A1 (en) | 2017-01-04 | 2018-07-12 | Research Institute At Nationwide Children's Hospital | Antibody fragments for the treatment of biofilm-related disorders |
US10376841B2 (en) | 2013-08-26 | 2019-08-13 | Sogang University Research & Business Development Foundation | Electroosmotic pump and fluid pumping system including the same |
US10549030B2 (en) * | 2016-09-08 | 2020-02-04 | Eoflow Co., Ltd. | Liquid medicine injection device |
CN110755699A (en) * | 2019-09-18 | 2020-02-07 | 浙江省北大信息技术高等研究院 | Implantable electroosmotic micropump device |
WO2021007260A2 (en) | 2019-07-08 | 2021-01-14 | Research Institute At Nationwide Children's Hospital | Antibody compositions for disrupting biofilms |
US11090434B2 (en) | 2015-11-24 | 2021-08-17 | Insulet Corporation | Automated drug delivery system |
US11813429B1 (en) * | 2022-09-07 | 2023-11-14 | CraniUS LLC | Pump for implantable medical devices |
US12070463B2 (en) | 2015-03-09 | 2024-08-27 | Board Of Supervisors Of Louisiana State University And Agricultural And Mechanical College | Compositions and methods for the treatment of seizure caused by brain tumor |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2981671A (en) * | 1957-12-19 | 1961-04-25 | Permutit Co Ltd | Method of reducing scale formation in electrodialytic cells |
US3016840A (en) * | 1958-11-13 | 1962-01-16 | Union Carbide Corp | Fluid actuating device |
US3427978A (en) * | 1964-09-02 | 1969-02-18 | Electro Dynamics Inc | Electro-hydraulic transducer |
US3510418A (en) * | 1966-02-24 | 1970-05-05 | Tokuyama Soda Kk | Ion selective membrane |
US3544237A (en) * | 1968-12-19 | 1970-12-01 | Dornier System Gmbh | Hydraulic regulating device |
US3553092A (en) * | 1965-12-04 | 1971-01-05 | Konrad Mund | Electrodialysis process and cell |
US3568214A (en) * | 1968-07-24 | 1971-03-09 | Univ Utah | Artificial heart system and method of pumping blood by electromagnetically pulsed fluid |
US3829370A (en) * | 1971-03-30 | 1974-08-13 | Rhone Poulenc Sa | Method for forced flow electrophoresis |
-
1974
- 1974-08-15 US US497685A patent/US3923426A/en not_active Expired - Lifetime
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2981671A (en) * | 1957-12-19 | 1961-04-25 | Permutit Co Ltd | Method of reducing scale formation in electrodialytic cells |
US3016840A (en) * | 1958-11-13 | 1962-01-16 | Union Carbide Corp | Fluid actuating device |
US3427978A (en) * | 1964-09-02 | 1969-02-18 | Electro Dynamics Inc | Electro-hydraulic transducer |
US3553092A (en) * | 1965-12-04 | 1971-01-05 | Konrad Mund | Electrodialysis process and cell |
US3510418A (en) * | 1966-02-24 | 1970-05-05 | Tokuyama Soda Kk | Ion selective membrane |
US3568214A (en) * | 1968-07-24 | 1971-03-09 | Univ Utah | Artificial heart system and method of pumping blood by electromagnetically pulsed fluid |
US3544237A (en) * | 1968-12-19 | 1970-12-01 | Dornier System Gmbh | Hydraulic regulating device |
US3829370A (en) * | 1971-03-30 | 1974-08-13 | Rhone Poulenc Sa | Method for forced flow electrophoresis |
Cited By (369)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4381006A (en) * | 1980-11-10 | 1983-04-26 | Abbott Laboratories | Continuous low flow rate fluid dispenser |
US4484923A (en) * | 1982-03-25 | 1984-11-27 | Alza Corporation | Method for administering immunopotentiator |
US4715850A (en) * | 1984-12-06 | 1987-12-29 | Controlled Release Technologies, Inc. | Therapeutic agent delivery system and method |
US4822339A (en) * | 1984-12-06 | 1989-04-18 | Controlled Release Technologies, Inc. | Therapeutic agent delivery system and method |
US4593534A (en) * | 1985-02-21 | 1986-06-10 | Analytic Power Corporation | Electrochemically driven heat pump |
US4687423A (en) * | 1985-06-07 | 1987-08-18 | Ivac Corporation | Electrochemically-driven pulsatile drug dispenser |
WO1987002593A1 (en) * | 1985-10-28 | 1987-05-07 | California Institute Of Technology | Method and apparatus using a solid electrolyte in the form of a disk for the separation or pumping of oxygen |
US4978337A (en) * | 1988-09-08 | 1990-12-18 | Alza Corporation | Formulation chamber with exterior electrotransport delivery device |
US5041107A (en) * | 1989-10-06 | 1991-08-20 | Cardiac Pacemakers, Inc. | Electrically controllable, non-occluding, body implantable drug delivery system |
US5080559A (en) * | 1990-01-23 | 1992-01-14 | The United States Of America As Represented By The United States Department Of Energy | Liquid metal electric pump |
US6001251A (en) * | 1990-08-22 | 1999-12-14 | University Of Pittsburgh | Material for separating submicron particles |
US5533995A (en) * | 1991-11-13 | 1996-07-09 | Elan Corporation, Plc | Passive transdermal device with controlled drug delivery |
US5964997A (en) * | 1997-03-21 | 1999-10-12 | Sarnoff Corporation | Balanced asymmetric electronic pulse patterns for operating electrode-based pumps |
US6013164A (en) * | 1997-06-25 | 2000-01-11 | Sandia Corporation | Electokinetic high pressure hydraulic system |
WO1999016162A1 (en) * | 1997-09-25 | 1999-04-01 | Caliper Technologies Corporation | Micropump |
US6012902A (en) * | 1997-09-25 | 2000-01-11 | Caliper Technologies Corp. | Micropump |
US6171067B1 (en) | 1997-09-25 | 2001-01-09 | Caliper Technologies Corp. | Micropump |
US6568910B1 (en) | 1997-09-25 | 2003-05-27 | Caliper Technologies Corp. | Micropump |
US6394759B1 (en) | 1997-09-25 | 2002-05-28 | Caliper Technologies Corp. | Micropump |
US7890176B2 (en) | 1998-07-06 | 2011-02-15 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating chronic pelvic pain |
US9415157B2 (en) | 1998-08-18 | 2016-08-16 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US8992475B2 (en) | 1998-08-18 | 2015-03-31 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US10279110B2 (en) | 1998-08-18 | 2019-05-07 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US9744301B2 (en) | 1998-08-18 | 2017-08-29 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US20030088236A1 (en) * | 1999-03-18 | 2003-05-08 | Johnson Randolph Mellus | Implantable devices and methods for treatment of pain by delivery of fentanyl and fentanyl congeners |
WO2000055502A1 (en) * | 1999-03-18 | 2000-09-21 | Sandia Corporation | Electrokinetic high pressure hydraulic system |
US6541021B1 (en) | 1999-03-18 | 2003-04-01 | Durect Corporation | Devices and methods for pain management |
US20040157884A1 (en) * | 1999-03-18 | 2004-08-12 | Johnson Randolph Mellus | Devices and methods for pain management |
US6835194B2 (en) | 1999-03-18 | 2004-12-28 | Durect Corporation | Implantable devices and methods for treatment of pain by delivery of fentanyl and fentanyl congeners |
US6689373B2 (en) | 1999-03-18 | 2004-02-10 | Durect Corporation | Devices and methods for pain management |
US20050106205A1 (en) * | 1999-03-18 | 2005-05-19 | Gillis Edward M. | Implantable devices and methods for treatment of pain by delivery of fentanyl and fentanyl congeners |
US20050129737A1 (en) * | 1999-03-18 | 2005-06-16 | Johnson Randolph M. | Devices and methods for pain management |
US8883424B2 (en) | 1999-05-21 | 2014-11-11 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US8080380B2 (en) | 1999-05-21 | 2011-12-20 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US9289766B2 (en) | 1999-05-21 | 2016-03-22 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US8481268B2 (en) | 1999-05-21 | 2013-07-09 | Illumina, Inc. | Use of microfluidic systems in the detection of target analytes using microsphere arrays |
US20050161334A1 (en) * | 1999-06-01 | 2005-07-28 | Paul Phillip H. | Electroosmotic flow systems |
US6406605B1 (en) | 1999-06-01 | 2002-06-18 | Ysi Incorporated | Electroosmotic flow controlled microfluidic devices |
WO2001026714A1 (en) | 1999-10-12 | 2001-04-19 | Durect Corporation | Regulation of drug delivery through flow diversion |
US7799037B1 (en) | 2000-02-24 | 2010-09-21 | Boston Scientific Neuromodulation Corporation | Surgical insertion tool |
US6409698B1 (en) * | 2000-11-27 | 2002-06-25 | John N. Robinson | Perforate electrodiffusion pump |
US20050070883A1 (en) * | 2000-11-29 | 2005-03-31 | Brown James E | Devices and methods for controlled delivery from a drug delivery device |
US20040235446A1 (en) * | 2000-12-21 | 2004-11-25 | Flaherty J. Christopher | Medical apparatus remote control and method |
US20060064140A1 (en) * | 2001-01-30 | 2006-03-23 | Whitehurst Todd K | Methods and systems for stimulating a trigeminal nerve to treat a psychiatric disorder |
US20050143789A1 (en) * | 2001-01-30 | 2005-06-30 | Whitehurst Todd K. | Methods and systems for stimulating a peripheral nerve to treat chronic pain |
US20050154419A1 (en) * | 2001-01-30 | 2005-07-14 | Whitehurst Todd K. | Methods and systems for stimulating a nerve originating in an upper cervical spine area to treat a medical condition |
US7493172B2 (en) | 2001-01-30 | 2009-02-17 | Boston Scientific Neuromodulation Corp. | Methods and systems for stimulating a nerve originating in an upper cervical spine area to treat a medical condition |
US6805841B2 (en) | 2001-05-09 | 2004-10-19 | The Provost Fellows And Scholars Of The College Of The Holy And Undivided Trinity Of Queen Elizabeth Near Dublin | Liquid pumping system |
US20030052007A1 (en) * | 2001-06-13 | 2003-03-20 | Paul Phillip H. | Precision flow control system |
US8685218B2 (en) | 2001-06-13 | 2014-04-01 | Ab Sciex Llc | Precision flow control system |
US7465382B2 (en) | 2001-06-13 | 2008-12-16 | Eksigent Technologies Llc | Precision flow control system |
US20020189947A1 (en) * | 2001-06-13 | 2002-12-19 | Eksigent Technologies Llp | Electroosmotic flow controller |
US20090090174A1 (en) * | 2001-06-13 | 2009-04-09 | Paul Phillip H | Precision Flow Control System |
US20040163957A1 (en) * | 2001-06-13 | 2004-08-26 | Neyer David W. | Flow control systems |
US20020195344A1 (en) * | 2001-06-13 | 2002-12-26 | Neyer David W. | Combined electroosmotic and pressure driven flow system |
US7927477B2 (en) | 2001-06-13 | 2011-04-19 | Ab Sciex Llc | Precision flow control system |
US7695603B2 (en) | 2001-06-13 | 2010-04-13 | Eksigent Technologies, Llc | Electroosmotic flow controller |
US7597790B2 (en) | 2001-06-13 | 2009-10-06 | Eksigent Technologies, Llc | Flow control systems |
US20110186157A1 (en) * | 2001-06-13 | 2011-08-04 | Paul Phillip H | Precision Flow Control System |
US20030010638A1 (en) * | 2001-06-15 | 2003-01-16 | Hansford Derek J. | Nanopump devices and methods |
US7799197B2 (en) * | 2001-06-15 | 2010-09-21 | The Ohio State University Research Foundation | Nanopump devices and methods |
US20060191831A1 (en) * | 2001-06-15 | 2006-08-31 | The Ohio State University Research Foundation | Nanopump devices and methods |
US6770183B1 (en) * | 2001-07-26 | 2004-08-03 | Sandia National Laboratories | Electrokinetic pump |
US20050044352A1 (en) * | 2001-08-30 | 2005-02-24 | Riverhead Networks, Inc. | Protecting against spoofed DNS messages |
US9066875B2 (en) | 2001-09-14 | 2015-06-30 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US9066876B2 (en) | 2001-09-14 | 2015-06-30 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US9005650B2 (en) | 2001-09-14 | 2015-04-14 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US9433573B2 (en) | 2001-09-14 | 2016-09-06 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US9433574B2 (en) | 2001-09-14 | 2016-09-06 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US20110223233A1 (en) * | 2001-09-14 | 2011-09-15 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US8986727B2 (en) | 2001-09-14 | 2015-03-24 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US9271926B2 (en) | 2001-09-14 | 2016-03-01 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US8603076B2 (en) | 2001-09-14 | 2013-12-10 | Delpor, Inc. | Microfabricated nanopore device for sustained release of therapeutic agent |
US20030164231A1 (en) * | 2001-09-28 | 2003-09-04 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
US7185697B2 (en) | 2001-09-28 | 2007-03-06 | Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
EP1811257A1 (en) * | 2001-09-28 | 2007-07-25 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic pump apparatus |
US20050098299A1 (en) * | 2001-09-28 | 2005-05-12 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
EP1576320A2 (en) * | 2001-09-28 | 2005-09-21 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
US6991024B2 (en) | 2001-09-28 | 2006-01-31 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
US6942018B2 (en) | 2001-09-28 | 2005-09-13 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic microchannel cooling system |
US7334630B2 (en) | 2001-09-28 | 2008-02-26 | The Board Of Trustees Of The Leland Stanford Junior University | Closed-loop microchannel cooling system |
EP1576320A4 (en) * | 2001-09-28 | 2005-10-05 | Univ Leland Stanford Junior | Electroosmotic microchannel cooling system |
US7134486B2 (en) | 2001-09-28 | 2006-11-14 | The Board Of Trustees Of The Leeland Stanford Junior University | Control of electrolysis gases in electroosmotic pump systems |
US7131486B2 (en) * | 2001-09-28 | 2006-11-07 | The Board Of Trustees Of The Leland Stanford Junior Universty | Electroosmotic microchannel cooling system |
US7037082B2 (en) * | 2001-10-02 | 2006-05-02 | Sophion Bioscience A/S | Corbino disc electroosmotic flow pump |
US20040247450A1 (en) * | 2001-10-02 | 2004-12-09 | Jonatan Kutchinsky | Sieve electrooosmotic flow pump |
US20040241006A1 (en) * | 2001-10-02 | 2004-12-02 | Rafael Taboryski | Corbino disc electroosmotic flow pump |
US6619925B2 (en) * | 2001-10-05 | 2003-09-16 | Toyo Technologies, Inc. | Fiber filled electro-osmotic pump |
US20070077547A1 (en) * | 2001-12-31 | 2007-04-05 | The Provost Fellows And Scholars Of The College Of The Holy And Undivided Trinity Of Queen Elizabeth | Assay assembly |
US6719535B2 (en) | 2002-01-31 | 2004-04-13 | Eksigent Technologies, Llc | Variable potential electrokinetic device |
US20040163959A1 (en) * | 2002-01-31 | 2004-08-26 | Rakestraw David J. | Variable potential electrokinetic devices |
US7399398B2 (en) | 2002-01-31 | 2008-07-15 | Eksigent Technologies, Llc | Variable potential electrokinetic devices |
US6606251B1 (en) | 2002-02-07 | 2003-08-12 | Cooligy Inc. | Power conditioning module |
US6678168B2 (en) | 2002-02-07 | 2004-01-13 | Cooligy, Inc. | System including power conditioning modules |
US20030173942A1 (en) * | 2002-02-07 | 2003-09-18 | Cooligy, Inc. | Apparatus for conditioning power and managing thermal energy in an electronic device |
US20040240245A1 (en) * | 2002-02-07 | 2004-12-02 | Cooligy, Inc. | Power conditioning module |
US7061104B2 (en) | 2002-02-07 | 2006-06-13 | Cooligy, Inc. | Apparatus for conditioning power and managing thermal energy in an electronic device |
US7050308B2 (en) | 2002-02-07 | 2006-05-23 | Cooligy, Inc. | Power conditioning module |
US20030212379A1 (en) * | 2002-02-26 | 2003-11-13 | Bylund Adam David | Systems and methods for remotely controlling medication infusion and analyte monitoring |
US20060116663A1 (en) * | 2002-05-01 | 2006-06-01 | Joshi Ashok V | Electro-osmotic fluid delivery device and method |
US7470267B2 (en) | 2002-05-01 | 2008-12-30 | Microlin, Llc | Fluid delivery device having an electrochemical pump with an anionic exchange membrane and associated method |
US7896867B2 (en) | 2002-05-01 | 2011-03-01 | Microlin, Llc | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US20030206806A1 (en) * | 2002-05-01 | 2003-11-06 | Paul Phillip H. | Bridges, elements and junctions for electroosmotic flow systems |
US20030205582A1 (en) * | 2002-05-01 | 2003-11-06 | Joshi Ashok V. | Fluid delivery device having an electrochemical pump with an anionic exchange membrane and associated method |
US20060052768A1 (en) * | 2002-05-01 | 2006-03-09 | Microlin, L.C. | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US7060170B2 (en) | 2002-05-01 | 2006-06-13 | Eksigent Technologies Llc | Bridges, elements and junctions for electroosmotic flow systems |
US7458965B2 (en) | 2002-05-01 | 2008-12-02 | Microlin, Llc | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US20060116641A1 (en) * | 2002-05-01 | 2006-06-01 | Microlin, L.C. | Fluid delivery device having an electrochemical pump with an ion-exchange membrane and associated method |
US20100331807A1 (en) * | 2002-05-24 | 2010-12-30 | Boston Scientific Neuromodulation Corporation | Treatment of movement disorders by brain stimulation |
US20070100393A1 (en) * | 2002-05-24 | 2007-05-03 | Whitehurst Todd K | Treatment of movement disorders by brain stimulation |
US8401634B2 (en) | 2002-05-24 | 2013-03-19 | Boston Scientific Neuromodulation Corporation | Treatment of movement disorders by brain stimulation |
US7517440B2 (en) | 2002-07-17 | 2009-04-14 | Eksigent Technologies Llc | Electrokinetic delivery systems, devices and methods |
US20050247558A1 (en) * | 2002-07-17 | 2005-11-10 | Anex Deon S | Electrokinetic delivery systems, devices and methods |
US7254449B2 (en) | 2002-07-31 | 2007-08-07 | Advanced Bionics Corp | Systems and methods for providing power to one or more implantable devices |
US20060149340A1 (en) * | 2002-07-31 | 2006-07-06 | Karunasiri Rankiri T | Systems and methods for providing power to one or more implantable devices |
WO2004022069A1 (en) | 2002-09-06 | 2004-03-18 | Durect Corporation | Delivery of modulators of glutamate-mediated neurotransmission to the inner ear |
US20060264913A1 (en) * | 2002-09-06 | 2006-11-23 | Poutiatine Andrew I | Implantable flow regulator with failsafe mode and reserve drug supply |
US7449122B2 (en) | 2002-09-23 | 2008-11-11 | Cooligy Inc. | Micro-fabricated electrokinetic pump |
US7086839B2 (en) | 2002-09-23 | 2006-08-08 | Cooligy, Inc. | Micro-fabricated electrokinetic pump with on-frit electrode |
US20050084385A1 (en) * | 2002-09-23 | 2005-04-21 | David Corbin | Micro-fabricated electrokinetic pump |
US20040101421A1 (en) * | 2002-09-23 | 2004-05-27 | Kenny Thomas W. | Micro-fabricated electrokinetic pump with on-frit electrode |
US8715480B2 (en) | 2002-10-18 | 2014-05-06 | Eksigent Technologies, Llc | Electrokinetic pump having capacitive electrodes |
US20040074784A1 (en) * | 2002-10-18 | 2004-04-22 | Anex Deon S. | Electrokinetic device having capacitive electrodes |
US7875159B2 (en) | 2002-10-18 | 2011-01-25 | Eksigent Technologies, Llc | Electrokinetic pump having capacitive electrodes |
US7235164B2 (en) * | 2002-10-18 | 2007-06-26 | Eksigent Technologies, Llc | Electrokinetic pump having capacitive electrodes |
US8192604B2 (en) | 2002-10-18 | 2012-06-05 | Eksigent Technologies, Llc | Electrokinetic pump having capacitive electrodes |
US20040074768A1 (en) * | 2002-10-18 | 2004-04-22 | Anex Deon S. | Electrokinetic pump having capacitive electrodes |
US7267753B2 (en) | 2002-10-18 | 2007-09-11 | Eksigent Technologies Llc | Electrokinetic device having capacitive electrodes |
US20040112585A1 (en) * | 2002-11-01 | 2004-06-17 | Cooligy Inc. | Method and apparatus for achieving temperature uniformity and hot spot cooling in a heat producing device |
US20040104022A1 (en) * | 2002-11-01 | 2004-06-03 | Cooligy, Inc. | Method and apparatus for flexible fluid delivery for cooling desired hot spots in a heat producing device |
US7104312B2 (en) | 2002-11-01 | 2006-09-12 | Cooligy, Inc. | Method and apparatus for achieving temperature uniformity and hot spot cooling in a heat producing device |
US20040206477A1 (en) * | 2002-11-01 | 2004-10-21 | Cooligy, Inc. | Method and apparatus for efficient vertical fluid delivery for cooling a heat producing device |
US20040104010A1 (en) * | 2002-11-01 | 2004-06-03 | Cooligy, Inc. | Interwoven manifolds for pressure drop reduction in microchannel heat exchangers |
US6986382B2 (en) | 2002-11-01 | 2006-01-17 | Cooligy Inc. | Interwoven manifolds for pressure drop reduction in microchannel heat exchangers |
US7806168B2 (en) | 2002-11-01 | 2010-10-05 | Cooligy Inc | Optimal spreader system, device and method for fluid cooled micro-scaled heat exchange |
US6988534B2 (en) | 2002-11-01 | 2006-01-24 | Cooligy, Inc. | Method and apparatus for flexible fluid delivery for cooling desired hot spots in a heat producing device |
US7000684B2 (en) | 2002-11-01 | 2006-02-21 | Cooligy, Inc. | Method and apparatus for efficient vertical fluid delivery for cooling a heat producing device |
US7175810B2 (en) | 2002-11-15 | 2007-02-13 | Eksigent Technologies | Processing of particles |
US20040235181A1 (en) * | 2002-11-15 | 2004-11-25 | Arnold Don W. | Processing of particles |
US7220592B2 (en) | 2002-11-15 | 2007-05-22 | Eksigent Technologies, Llc | Particulate processing system |
US20040096977A1 (en) * | 2002-11-15 | 2004-05-20 | Rakestraw David J. | Particulate processing system |
US20040102476A1 (en) * | 2002-11-25 | 2004-05-27 | Chan Tai Wah | High concentration formulations of opioids and opioid derivatives |
US20110136847A1 (en) * | 2002-11-25 | 2011-06-09 | Tai Wah Chan | High Concentration Formulations of Opioids and Opioid Derivatives |
US20070014820A1 (en) * | 2003-01-23 | 2007-01-18 | Dana Litmanovitz | Opioid formulations |
FR2850677A1 (en) * | 2003-01-30 | 2004-08-06 | Seb Sa | Ironing apparatus, has electro-osmotic pump that transfers water from water container to evaporation chamber, and includes porous body comprising alluvial sand grains or mixed grains comprising ion-exchange resin granules |
EP1479814A1 (en) * | 2003-01-30 | 2004-11-24 | Seb S.A. | Iron with an electro-osmotic pump |
US20040181979A1 (en) * | 2003-01-30 | 2004-09-23 | Seb S.A. | Pressing iron having an electro-osmotic pump |
US20040151962A1 (en) * | 2003-01-31 | 2004-08-05 | Paul Adams | Fuel cartridge for fuel cells |
WO2004076857A3 (en) * | 2003-01-31 | 2006-01-05 | Cooligy Inc | Method and apparatus for low-cost electrokinetic pump manufacturing |
US7147955B2 (en) | 2003-01-31 | 2006-12-12 | Societe Bic | Fuel cartridge for fuel cells |
US20050183443A1 (en) * | 2003-01-31 | 2005-08-25 | Mark Munch | Remedies to prevent cracking in a liquid system |
US20070095860A1 (en) * | 2003-01-31 | 2007-05-03 | Societe Bic | Fuel Cartridge for Fuel Cells |
US7402029B2 (en) | 2003-01-31 | 2008-07-22 | Cooligy Inc. | Remedies to prevent cracking in a liquid system |
EP2259372A2 (en) | 2003-01-31 | 2010-12-08 | Société BIC | Fuel cartridge for fuel cells |
US20050183445A1 (en) * | 2003-01-31 | 2005-08-25 | Mark Munch | Remedies to prevent cracking in a liquid system |
US7201214B2 (en) | 2003-01-31 | 2007-04-10 | Cooligy, Inc. | Remedies to prevent cracking in a liquid system |
US20050183444A1 (en) * | 2003-01-31 | 2005-08-25 | Mark Munch | Remedies to prevent cracking in a liquid system |
US20040148959A1 (en) * | 2003-01-31 | 2004-08-05 | Cooligy, Inc. | Remedies to prevent cracking in a liquid system |
US7201012B2 (en) | 2003-01-31 | 2007-04-10 | Cooligy, Inc. | Remedies to prevent cracking in a liquid system |
US20050210913A1 (en) * | 2003-01-31 | 2005-09-29 | Mark Munch | Remedies to prevent cracking in a liquid system |
US7278549B2 (en) | 2003-01-31 | 2007-10-09 | Cooligy Inc. | Remedies to prevent cracking in a liquid system |
JP2006522434A (en) * | 2003-01-31 | 2006-09-28 | ソシエテ ビック | Fuel cartridge for fuel cell |
US7344363B2 (en) | 2003-01-31 | 2008-03-18 | Cooligy Inc. | Remedies to prevent cracking in a liquid system |
US20050183845A1 (en) * | 2003-01-31 | 2005-08-25 | Mark Munch | Remedies to prevent cracking in a liquid system |
WO2004076857A2 (en) * | 2003-01-31 | 2004-09-10 | Cooligy, Inc. | Method and apparatus for low-cost electrokinetic pump manufacturing |
US20080073213A1 (en) * | 2003-02-21 | 2008-03-27 | Sophion Bioscience A/S | Sieve Eop Pump |
CN100360217C (en) * | 2003-02-21 | 2008-01-09 | 索菲昂生物科学有限公司 | Sieve of electroosmotic pump |
WO2004073822A2 (en) * | 2003-02-21 | 2004-09-02 | Sophion Bioscience A/S | Sieve electroosmotic pump |
WO2004073822A3 (en) * | 2003-02-21 | 2004-10-07 | Sophion Bioscience As | Sieve electroosmotic pump |
US20040182560A1 (en) * | 2003-03-17 | 2004-09-23 | Cooligy Inc. | Apparatus and method of forming channels in a heat-exchanging device |
US7017654B2 (en) | 2003-03-17 | 2006-03-28 | Cooligy, Inc. | Apparatus and method of forming channels in a heat-exchanging device |
US20070083240A1 (en) * | 2003-05-08 | 2007-04-12 | Peterson David K L | Methods and systems for applying stimulation and sensing one or more indicators of cardiac activity with an implantable stimulator |
WO2004101444A1 (en) * | 2003-05-12 | 2004-11-25 | Clean Water Gesellschaft Für Wasseraufbereitungs- Technik Mbh | Method and device for the purification, especially desalination, of water |
US20060108286A1 (en) * | 2003-05-12 | 2006-05-25 | Guenther Hambitzer | Method and device for the purification, especially desalination, of water |
US7488421B2 (en) | 2003-05-12 | 2009-02-10 | Clean Water Gesellschaft Fuer Wasseraufbereitungstechnik Mbh | Method and device for the purification, especially desalination, of water |
CN100445215C (en) * | 2003-05-12 | 2008-12-24 | 清洁水净化技术有限责任公司 | Method and device for the purification, especially desalination, of water |
EP2390262A1 (en) | 2003-05-16 | 2011-11-30 | Intermune, Inc. | Synthetic chemokine receptor ligands and methods of use thereof |
US7316543B2 (en) | 2003-05-30 | 2008-01-08 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic micropump with planar features |
US20040241004A1 (en) * | 2003-05-30 | 2004-12-02 | Goodson Kenneth E. | Electroosmotic micropump with planar features |
US20050016853A1 (en) * | 2003-07-21 | 2005-01-27 | Paul Phillip H. | Bridges for electroosmotic flow systems |
US7258777B2 (en) | 2003-07-21 | 2007-08-21 | Eksigent Technologies Llc | Bridges for electroosmotic flow systems |
US7591302B1 (en) | 2003-07-23 | 2009-09-22 | Cooligy Inc. | Pump and fan control concepts in a cooling system |
US7021369B2 (en) | 2003-07-23 | 2006-04-04 | Cooligy, Inc. | Hermetic closed loop fluid system |
US8602092B2 (en) | 2003-07-23 | 2013-12-10 | Cooligy, Inc. | Pump and fan control concepts in a cooling system |
US20050034842A1 (en) * | 2003-08-11 | 2005-02-17 | David Huber | Electroosmotic micropumps with applications to fluid dispensing and field sampling |
US7231839B2 (en) | 2003-08-11 | 2007-06-19 | The Board Of Trustees Of The Leland Stanford Junior University | Electroosmotic micropumps with applications to fluid dispensing and field sampling |
US20070117841A1 (en) * | 2003-10-24 | 2007-05-24 | Ozes Osman N | Use of pirfenidone in therapeutic regimens |
US7407973B2 (en) | 2003-10-24 | 2008-08-05 | Intermune, Inc. | Use of pirfenidone in therapeutic regimens |
US20100168661A1 (en) * | 2003-11-06 | 2010-07-01 | Lifescan, Inc. | Drug delivery with event notification |
US8551039B2 (en) | 2003-11-06 | 2013-10-08 | Lifescan, Inc. | Drug delivery with event notification |
US7713229B2 (en) | 2003-11-06 | 2010-05-11 | Lifescan, Inc. | Drug delivery pen with event notification means |
US8333752B2 (en) | 2003-11-06 | 2012-12-18 | Lifescan, Inc. | Drug delivery with event notification |
EP2236423A2 (en) | 2003-12-01 | 2010-10-06 | Société BIC | Method and apparatus for filling a fuel container |
US20110009920A1 (en) * | 2003-12-19 | 2011-01-13 | Boston Scientific Neuromodulation Corporation | Skull-mounted electrical stimulation system and method for treating patients |
US20060293723A1 (en) * | 2003-12-19 | 2006-12-28 | Whitehurst Todd K | Skull-mounted electrical stimulation system and method for treating patients |
US7769461B2 (en) | 2003-12-19 | 2010-08-03 | Boston Scientific Neuromodulation Corporation | Skull-mounted electrical stimulation system and method for treating patients |
US7559356B2 (en) * | 2004-04-19 | 2009-07-14 | Eksident Technologies, Inc. | Electrokinetic pump driven heat transfer system |
US7521140B2 (en) | 2004-04-19 | 2009-04-21 | Eksigent Technologies, Llc | Fuel cell system with electrokinetic pump |
WO2005114061A3 (en) * | 2004-04-19 | 2007-06-28 | Eksigent Technologies Llc | Electrokinetic pump driven heat transfer system |
US20050230080A1 (en) * | 2004-04-19 | 2005-10-20 | Paul Phillip H | Electrokinetic pump driven heat transfer system |
US20050233195A1 (en) * | 2004-04-19 | 2005-10-20 | Arnold Don W | Fuel cell system with electrokinetic pump |
WO2005114061A2 (en) * | 2004-04-19 | 2005-12-01 | Eksigent Technologies, Llc | Electrokinetic pump driven heat transfer system |
WO2005113419A3 (en) * | 2004-04-21 | 2007-12-27 | Eksigent Technologies Llc | Electrokinetic delivery systems, devices and methods |
CN101365885B (en) * | 2004-04-21 | 2011-08-03 | 艾克西根特技术有限公司 | Electrokinetic delivery systems, devices and methods |
EP1740497A4 (en) * | 2004-04-21 | 2015-11-11 | Eksigent Technologies Llc | Electrokinetic delivery systems, devices and methods |
US20090281605A1 (en) * | 2004-05-28 | 2009-11-12 | Boston Scientific Neuromodulation Corporation | Engagement tool for implantable medical devices |
US8364280B2 (en) | 2004-05-28 | 2013-01-29 | Boston Scientific Neuromodulation Corporation | Engagement tool for implantable medical devices |
US7293423B2 (en) | 2004-06-04 | 2007-11-13 | Cooligy Inc. | Method and apparatus for controlling freezing nucleation and propagation |
US20080260542A1 (en) * | 2004-06-07 | 2008-10-23 | Nano Fusion Technologies, Inc | Electroosmotic Pump System and Electroosmotic Pump |
US20080027513A1 (en) * | 2004-07-09 | 2008-01-31 | Advanced Bionics Corporation | Systems And Methods For Using A Butterfly Coil To Communicate With Or Transfer Power To An Implantable Medical Device |
US8452407B2 (en) | 2004-08-16 | 2013-05-28 | Boston Scientific Neuromodulation Corporation | Methods for treating gastrointestinal disorders |
US20060036293A1 (en) * | 2004-08-16 | 2006-02-16 | Whitehurst Todd K | Methods for treating gastrointestinal disorders |
US7718047B2 (en) | 2004-10-19 | 2010-05-18 | The Regents Of The University Of Colorado | Electrochemical high pressure pump |
US20060207883A1 (en) * | 2004-10-19 | 2006-09-21 | Koval Carl A | Electrochemical high pressure pump |
US9358393B1 (en) | 2004-11-09 | 2016-06-07 | Andres M. Lozano | Stimulation methods and systems for treating an auditory dysfunction |
US7483746B2 (en) | 2004-12-06 | 2009-01-27 | Boston Scientific Neuromodulation Corp. | Stimulation of the stomach in response to sensed parameters to treat obesity |
US8095219B2 (en) | 2004-12-06 | 2012-01-10 | Boston Scientific Neuromodulation Corporation | Stimulation of the stomach in response to sensed parameters to treat obesity |
US20060129201A1 (en) * | 2004-12-06 | 2006-06-15 | Lee Philip H J | Stimulation of the stomach in response to sensed parameters to treat obesity |
US20090192565A1 (en) * | 2004-12-06 | 2009-07-30 | Boston Scientific Neuromodulation Corporation | Stimulation of the stomach in response to sensed parameters to treat obesity |
US20060131174A1 (en) * | 2004-12-20 | 2006-06-22 | Paul Phillip H | Electrokinetic device employing a non-Newtonian liquid |
US7429317B2 (en) | 2004-12-20 | 2008-09-30 | Eksigent Technologies Llc | Electrokinetic device employing a non-newtonian liquid |
US20100030287A1 (en) * | 2004-12-21 | 2010-02-04 | Boston Scientific Neuromodulation Corporation | Methods for treating autism |
US20060247728A1 (en) * | 2004-12-21 | 2006-11-02 | Foster Allison M | Methods and systems for treating autism by decreasing neural activity within the brain |
US20060161217A1 (en) * | 2004-12-21 | 2006-07-20 | Jaax Kristen N | Methods and systems for treating obesity |
US9327069B2 (en) | 2004-12-21 | 2016-05-03 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating a medical condition by promoting neural remodeling within the brain |
US9095713B2 (en) | 2004-12-21 | 2015-08-04 | Allison M. Foster | Methods and systems for treating autism by decreasing neural activity within the brain |
US9352145B2 (en) | 2004-12-22 | 2016-05-31 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating a psychotic disorder |
US8515541B1 (en) | 2004-12-22 | 2013-08-20 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating post-stroke disorders |
US20090270944A1 (en) * | 2004-12-22 | 2009-10-29 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating a psychotic disorder |
US20060185665A1 (en) * | 2005-02-22 | 2006-08-24 | Bachinski Thomas J | Sauna fireplace |
US20060194724A1 (en) * | 2005-02-25 | 2006-08-31 | Whitehurst Todd K | Methods and systems for nerve regeneration |
US20060235484A1 (en) * | 2005-03-14 | 2006-10-19 | Jaax Kristen N | Stimulation of a stimulation site within the neck or head |
US8644954B2 (en) | 2005-03-14 | 2014-02-04 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US8315704B2 (en) | 2005-03-14 | 2012-11-20 | Boston Scientific Neuromodulation Corporation | Stimulation of a stimulation site within the neck or head |
US7853321B2 (en) | 2005-03-14 | 2010-12-14 | Boston Scientific Neuromodulation Corporation | Stimulation of a stimulation site within the neck or head |
US7848803B1 (en) | 2005-03-14 | 2010-12-07 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US20070049988A1 (en) * | 2005-03-14 | 2007-03-01 | Rafael Carbunaru | Optimal electrode contact polarity configurations for implantable stimulation systems |
US20060206165A1 (en) * | 2005-03-14 | 2006-09-14 | Jaax Kristen N | Occipital nerve stimulation to treat headaches and other conditions |
US8423155B1 (en) | 2005-03-14 | 2013-04-16 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US20110060382A1 (en) * | 2005-03-14 | 2011-03-10 | Boston Scientific Neuromodulation Corporation | Stimulation of a stimulation site within the neck or head |
US8224451B2 (en) | 2005-03-14 | 2012-07-17 | Boston Scientific Neuromodulation Corporation | Methods and systems for facilitating stimulation of one or more stimulation sites |
US20090126813A1 (en) * | 2005-03-30 | 2009-05-21 | Nano Fusion Technologies, Inc. | Liquid-Transport Device and System |
US20090136362A1 (en) * | 2005-03-30 | 2009-05-28 | Nano Fusion Technologies Inc. | Electroosmosis Pump and Liquid Feeding Device |
US20100222770A1 (en) * | 2005-07-01 | 2010-09-02 | John Howard Gordon | Fluid delivery device with a diffusion membrane for fast response time |
US8348930B2 (en) | 2005-07-01 | 2013-01-08 | Microlin, Llc | Fluid delivery device with a diffusion membrane and electrochemical pump |
WO2007034267A1 (en) * | 2005-07-07 | 2007-03-29 | Obshchestvo S Ogranichennoj Otvetstvennostyu 'institut Rentgenovskoj Optiki' | Electrokinetic micropump |
US20070021735A1 (en) * | 2005-07-15 | 2007-01-25 | Sai Bhavaraju | Dual membrane electro-osmotic fluid delivery device |
US20070025869A1 (en) * | 2005-07-15 | 2007-02-01 | Gordon John H | Fluid Delivery Device |
US20070066997A1 (en) * | 2005-09-21 | 2007-03-22 | He Tom X | Methods and systems for placing an implanted stimulator for stimulating tissue |
US7684858B2 (en) | 2005-09-21 | 2010-03-23 | Boston Scientific Neuromodulation Corporation | Methods and systems for placing an implanted stimulator for stimulating tissue |
US20070068815A1 (en) * | 2005-09-26 | 2007-03-29 | Industrial Technology Research Institute | Micro electro-kinetic pump having a nano porous membrane |
JPWO2007052377A1 (en) * | 2005-11-02 | 2009-04-30 | 株式会社新潟Tlo | Micropump and microfluidic chip |
JP4528330B2 (en) * | 2005-11-02 | 2010-08-18 | 株式会社新潟Tlo | Micropump and microfluidic chip |
WO2007052377A1 (en) * | 2005-11-02 | 2007-05-10 | Niigata Tlo Corporation | Micropump and micro fluid chip |
US8906000B2 (en) | 2005-11-09 | 2014-12-09 | The Invention Science Fund I, Llc | Injectable controlled release fluid delivery system |
US9254256B2 (en) | 2005-11-09 | 2016-02-09 | The Invention Science Fund I, Llc | Remote controlled in vivo reaction method |
US8529551B2 (en) | 2005-11-09 | 2013-09-10 | The Invention Science Fund I, Llc | Acoustically controlled substance delivery device |
US8585684B2 (en) | 2005-11-09 | 2013-11-19 | The Invention Science Fund I, Llc | Reaction device controlled by magnetic control signal |
US9028467B2 (en) | 2005-11-09 | 2015-05-12 | The Invention Science Fund I, Llc | Osmotic pump with remotely controlled osmotic pressure generation |
US8882747B2 (en) | 2005-11-09 | 2014-11-11 | The Invention Science Fund I, Llc | Substance delivery system |
US8992511B2 (en) | 2005-11-09 | 2015-03-31 | The Invention Science Fund I, Llc | Acoustically controlled substance delivery device |
US8172833B2 (en) | 2005-11-09 | 2012-05-08 | The Invention Science Fund I, Llc | Remote control of substance delivery system |
US8617141B2 (en) | 2005-11-09 | 2013-12-31 | The Invention Science Fund I, Llc | Remote controlled in situ reaction device |
US8998884B2 (en) | 2005-11-09 | 2015-04-07 | The Invention Science Fund I, Llc | Remote controlled in situ reaction method |
US9067047B2 (en) | 2005-11-09 | 2015-06-30 | The Invention Science Fund I, Llc | Injectable controlled release fluid delivery system |
US8968274B2 (en) | 2005-11-09 | 2015-03-03 | The Invention Science Fund I, Llc | Acoustically controlled substance delivery device |
US7942867B2 (en) | 2005-11-09 | 2011-05-17 | The Invention Science Fund I, Llc | Remotely controlled substance delivery device |
US9474712B2 (en) | 2005-11-09 | 2016-10-25 | Gearbox, Llc | In situ reaction device |
US20100076415A1 (en) * | 2005-11-09 | 2010-03-25 | Searete Llc | Remote control of substance delivery system |
US8936590B2 (en) | 2005-11-09 | 2015-01-20 | The Invention Science Fund I, Llc | Acoustically controlled reaction device |
US8568388B2 (en) | 2005-11-09 | 2013-10-29 | The Invention Science Fund I, Llc | Remote controlled in situ reaction device |
US8114065B2 (en) | 2005-11-09 | 2012-02-14 | The Invention Science Fund I, Llc | Remote control of substance delivery system |
WO2007059010A2 (en) | 2005-11-14 | 2007-05-24 | Enterprise Partners Venture Capital | Stem cell factor therapy for tissue injury |
US20090304636A1 (en) * | 2005-11-14 | 2009-12-10 | Enterprise Partners Venture Capital | Stem Cell Factor Therapy for Tissue Injury |
US8404653B2 (en) | 2005-11-14 | 2013-03-26 | Enterprise Partners Venture Capital | Membrane bound stem cell factor therapy for ischemic heart |
US8630705B2 (en) | 2005-11-16 | 2014-01-14 | Boston Scientific Neuromodulation Corporation | Implantable stimulator |
US7920915B2 (en) | 2005-11-16 | 2011-04-05 | Boston Scientific Neuromodulation Corporation | Implantable stimulator |
US20070112404A1 (en) * | 2005-11-16 | 2007-05-17 | Mann Alfred E | Implantable stimulator |
US20110172739A1 (en) * | 2005-11-16 | 2011-07-14 | Boston Scientific Neuromodulation Corporation | Implantable stimulator |
US8152477B2 (en) | 2005-11-23 | 2012-04-10 | Eksigent Technologies, Llc | Electrokinetic pump designs and drug delivery systems |
US8794929B2 (en) | 2005-11-23 | 2014-08-05 | Eksigent Technologies Llc | Electrokinetic pump designs and drug delivery systems |
US7729758B2 (en) | 2005-11-30 | 2010-06-01 | Boston Scientific Neuromodulation Corporation | Magnetically coupled microstimulators |
US8192390B2 (en) | 2005-12-13 | 2012-06-05 | The Invention Science Fund I, Llc | Method and system for control of osmotic pump device |
US8998886B2 (en) * | 2005-12-13 | 2015-04-07 | The Invention Science Fund I, Llc | Remote control of osmotic pump device |
US7896868B2 (en) | 2005-12-13 | 2011-03-01 | The Invention Science Fund I, Llc | Method and system for control of osmotic pump device |
US8273075B2 (en) | 2005-12-13 | 2012-09-25 | The Invention Science Fund I, Llc | Osmotic pump with remotely controlled osmotic flow rate |
US8109923B2 (en) | 2005-12-13 | 2012-02-07 | The Invention Science Fund I, Llc | Osmotic pump with remotely controlled osmotic pressure generation |
US7610100B2 (en) | 2005-12-30 | 2009-10-27 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating osteoarthritis |
US20070156180A1 (en) * | 2005-12-30 | 2007-07-05 | Jaax Kristen N | Methods and systems for treating osteoarthritis |
US8423154B2 (en) | 2006-01-17 | 2013-04-16 | Boston Scientific Neuromodulation Corporation | Lead assemblies with one or more switching networks |
US20110029042A1 (en) * | 2006-01-17 | 2011-02-03 | Boston Scientific Neuromodulation Corporation | Lead assemblies with one or more switching networks |
US8214058B2 (en) | 2006-01-17 | 2012-07-03 | Boston Scientific Neuromodulation Corporation | Lead assemblies with one or more switching networks |
US7835803B1 (en) | 2006-01-17 | 2010-11-16 | Boston Scientific Neuromodulation Corporation | Lead assemblies with one or more switching networks |
US20100030185A1 (en) * | 2006-01-18 | 2010-02-04 | Searete Llc | Remote controller for substance delivery system |
US8273071B2 (en) | 2006-01-18 | 2012-09-25 | The Invention Science Fund I, Llc | Remote controller for substance delivery system |
US7913719B2 (en) * | 2006-01-30 | 2011-03-29 | Cooligy Inc. | Tape-wrapped multilayer tubing and methods for making the same |
US20070201204A1 (en) * | 2006-02-16 | 2007-08-30 | Girish Upadhya | Liquid cooling loops for server applications |
US7599184B2 (en) | 2006-02-16 | 2009-10-06 | Cooligy Inc. | Liquid cooling loops for server applications |
US8367003B2 (en) | 2006-03-09 | 2013-02-05 | The Invention Science Fund I, Llc | Acoustically controlled reaction device |
US20090162249A1 (en) * | 2006-03-09 | 2009-06-25 | Searete Llc | Acoustically controlled reaction device |
US8083710B2 (en) | 2006-03-09 | 2011-12-27 | The Invention Science Fund I, Llc | Acoustically controlled substance delivery device |
US8349261B2 (en) | 2006-03-09 | 2013-01-08 | The Invention Science Fund, I, LLC | Acoustically controlled reaction device |
US20090005727A1 (en) * | 2006-03-09 | 2009-01-01 | Searete Llc | Acoustically controlled substance delivery device |
US8175710B2 (en) | 2006-03-14 | 2012-05-08 | Boston Scientific Neuromodulation Corporation | Stimulator system with electrode array and the method of making the same |
US20070219595A1 (en) * | 2006-03-14 | 2007-09-20 | Advanced Bionics Corporation | Stimulator system with electrode array and the method of making the same |
US8157001B2 (en) | 2006-03-30 | 2012-04-17 | Cooligy Inc. | Integrated liquid to air conduction module |
US7715194B2 (en) | 2006-04-11 | 2010-05-11 | Cooligy Inc. | Methodology of cooling multiple heat sources in a personal computer through the use of multiple fluid-based heat exchanging loops coupled via modular bus-type heat exchangers |
US8401654B1 (en) | 2006-06-30 | 2013-03-19 | Boston Scientific Neuromodulation Corporation | Methods and systems for treating one or more effects of deafferentation |
US8504163B1 (en) | 2006-06-30 | 2013-08-06 | Boston Scientific Neuromodulation Corporation | Cranially mounted stimulation systems and methods |
CN101153618B (en) * | 2006-09-27 | 2010-06-23 | 卡西欧计算机株式会社 | Connecting structure of a liquid sending apparatus, fuel-cell type electricity generating apparatus, and electronic device |
US7445528B1 (en) | 2006-09-29 | 2008-11-04 | Boston Scientific Neuromodulation Corporation | Connector assemblies |
US7347746B1 (en) | 2006-10-27 | 2008-03-25 | Boston Scientific Neuromodulation Corporation | Receptacle connector assembly |
EP2098588A1 (en) * | 2006-11-22 | 2009-09-09 | Altair Corporation | Pipette core member, pipette, and pipette device |
US8268261B2 (en) * | 2006-11-22 | 2012-09-18 | Altair Corporation | Pipette core member, pipette, and pipette device |
US20090317304A1 (en) * | 2006-11-22 | 2009-12-24 | Altair Corporation | Pipette Core Member, Pipette, and Pipette Device |
EP2098588A4 (en) * | 2006-11-22 | 2011-11-02 | Altair Corp | Pipette core member, pipette, and pipette device |
US7709129B2 (en) * | 2006-12-04 | 2010-05-04 | Casio Computer Co., Ltd. | Gas-liquid separating device and electric power generating apparatus |
US20080131757A1 (en) * | 2006-12-04 | 2008-06-05 | Casio Computer Co., Ltd. | Gas-liquid separating device and electric power generating apparatus |
US7867592B2 (en) | 2007-01-30 | 2011-01-11 | Eksigent Technologies, Inc. | Methods, compositions and devices, including electroosmotic pumps, comprising coated porous surfaces |
US20080209876A1 (en) * | 2007-02-07 | 2008-09-04 | Zettacore, Inc. | Liquid Composite Compositions Using Non-Volatile Liquids and Nanoparticles and Uses Thereof |
US9403190B2 (en) | 2007-02-07 | 2016-08-02 | Esionic Corp. | Liquid composite compositions using non-volatile liquids and nanoparticles and uses thereof |
US8709531B2 (en) * | 2007-02-07 | 2014-04-29 | Esionic Es, Inc. | Liquid composite compositions using non-volatile liquids and nanoparticles and uses thereof |
US9120121B2 (en) | 2007-02-07 | 2015-09-01 | Esionic Corp. | Liquid composite compositions using non-volatile liquids and nanoparticles and uses thereof |
US8540899B2 (en) | 2007-02-07 | 2013-09-24 | Esionic Es, Inc. | Liquid composite compositions using non-volatile liquids and nanoparticles and uses thereof |
US8251672B2 (en) | 2007-12-11 | 2012-08-28 | Eksigent Technologies, Llc | Electrokinetic pump with fixed stroke volume |
US20110052431A1 (en) * | 2008-02-08 | 2011-03-03 | Osmotex Ag | Electro-osmotic pump |
US20110072914A1 (en) * | 2008-02-14 | 2011-03-31 | Illumina, Inc. | Flow Cells And Manifolds Having An Electroosmotic Pump |
US8173080B2 (en) * | 2008-02-14 | 2012-05-08 | Illumina, Inc. | Flow cells and manifolds having an electroosmotic pump |
US9347440B2 (en) | 2008-02-14 | 2016-05-24 | Illumina, Inc. | Flow cells and manifolds having an electroosmotic pump |
US8250877B2 (en) | 2008-03-10 | 2012-08-28 | Cooligy Inc. | Device and methodology for the removal of heat from an equipment rack by means of heat exchangers mounted to a door |
US9297571B1 (en) | 2008-03-10 | 2016-03-29 | Liebert Corporation | Device and methodology for the removal of heat from an equipment rack by means of heat exchangers mounted to a door |
EP3025727A1 (en) | 2008-10-02 | 2016-06-01 | The J. David Gladstone Institutes | Methods of treating liver disease |
US20100124679A1 (en) * | 2008-11-20 | 2010-05-20 | Mti Microfuel Cells, Inc. | Method for increasing the durability of direct oxidation fuel cells |
WO2010107739A2 (en) | 2009-03-18 | 2010-09-23 | The Board Of Trustees Of The Leland Stanford Junior University | Methods and compositions of treating a flaviviridae family viral infection |
WO2011057654A1 (en) * | 2009-11-13 | 2011-05-19 | Ab Skf | Bearing assembly with active oil lubrication |
US20120325941A1 (en) * | 2010-03-04 | 2012-12-27 | Toppan Printing Co., Ltd. | Odor generator |
US9377786B2 (en) * | 2010-03-04 | 2016-06-28 | Tokyo Institute Of Technology | Odor generator |
US8979511B2 (en) | 2011-05-05 | 2015-03-17 | Eksigent Technologies, Llc | Gel coupling diaphragm for electrokinetic delivery systems |
WO2012175698A1 (en) | 2011-06-23 | 2012-12-27 | Université Libre de Bruxelles | Therapeutic use of all-trans retinoic acid (atra) in patients suffering from alcoholic liver disease |
WO2013033636A2 (en) | 2011-09-01 | 2013-03-07 | University Of Southern California | Methods for preparing high throughput peptidomimetics, orally bioavailable drugs and compositions containing same |
EP3222720A1 (en) | 2011-09-01 | 2017-09-27 | University of Southern California | Methods for preparing high throughput peptidomimetics, orally bioavailable drugs and compositions containing same |
US9364484B2 (en) | 2011-12-06 | 2016-06-14 | The Board Of Trustees Of The Leland Stanford Junior University | Methods and compositions for treating viral diseases |
US10869873B2 (en) | 2011-12-06 | 2020-12-22 | The Board Of Trustees Of The Leland Stanford Junior University | Methods and compositions for treating viral diseases |
US9103331B2 (en) | 2011-12-15 | 2015-08-11 | General Electric Company | Electro-osmotic pump |
JP2015521870A (en) * | 2012-07-06 | 2015-08-03 | サノフィ−アベンティス・ドイチュラント・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング | Drug delivery device |
US20150126928A1 (en) * | 2012-07-06 | 2015-05-07 | Sanofi-Aventis Deutschland Gmbh | Drug delivery device |
US9956338B2 (en) * | 2012-07-06 | 2018-05-01 | Sanofi-Aventis Deutschland Gmbh | Drug delivery device |
US9399986B2 (en) * | 2012-07-31 | 2016-07-26 | General Electric Company | Devices and systems for isolating biomolecules and associated methods thereof |
WO2014019775A1 (en) * | 2012-07-31 | 2014-02-06 | General Electric Company | Devices and systems for isolating biomolecules and associated methods thereof |
US20140039172A1 (en) * | 2012-07-31 | 2014-02-06 | General Electric Company | Devices and systems for isolating biomolecules and associated methods thereof |
EP3070331A4 (en) * | 2013-08-26 | 2017-05-31 | Sogang University Research Foundation | Electroosmotic pump and fluid pumping system having same |
US10376841B2 (en) | 2013-08-26 | 2019-08-13 | Sogang University Research & Business Development Foundation | Electroosmotic pump and fluid pumping system including the same |
US9982663B2 (en) * | 2013-10-11 | 2018-05-29 | The Board Of Regents Of The University Of Oklahoma | Electroosmotic pump unit and assembly |
US20150101930A1 (en) * | 2013-10-11 | 2015-04-16 | The Board Of Regents Of The University Of Oklahoma | Electroosmotic pump unit and assembly |
US12070463B2 (en) | 2015-03-09 | 2024-08-27 | Board Of Supervisors Of Louisiana State University And Agricultural And Mechanical College | Compositions and methods for the treatment of seizure caused by brain tumor |
WO2017023863A1 (en) | 2015-07-31 | 2017-02-09 | Research Institute At Nationwide Children's Hospital | Peptides and antibodies for the removal of biofilms |
WO2017066719A2 (en) | 2015-10-14 | 2017-04-20 | Research Institute At Nationwide Children's Hospital | Hu specific interfering agents |
US11744944B2 (en) | 2015-11-24 | 2023-09-05 | Insulet Corporation | Wearable automated medication delivery system |
US11090434B2 (en) | 2015-11-24 | 2021-08-17 | Insulet Corporation | Automated drug delivery system |
US20200129692A1 (en) * | 2016-09-08 | 2020-04-30 | Eoflow Co., Ltd. | Liquid medicine injection device |
US10549030B2 (en) * | 2016-09-08 | 2020-02-04 | Eoflow Co., Ltd. | Liquid medicine injection device |
US11738137B2 (en) * | 2016-09-08 | 2023-08-29 | Eoflow Co., Ltd. | Liquid medicine injection device |
WO2018129092A1 (en) | 2017-01-04 | 2018-07-12 | Research Institute At Nationwide Children's Hospital | Antibody fragments for the treatment of biofilm-related disorders |
WO2018129078A1 (en) | 2017-01-04 | 2018-07-12 | Research Institute At Nationwide Children's Hospital | Dnabii vaccines and antibodies with enhanced activity |
WO2021007260A2 (en) | 2019-07-08 | 2021-01-14 | Research Institute At Nationwide Children's Hospital | Antibody compositions for disrupting biofilms |
EP4361171A2 (en) | 2019-07-08 | 2024-05-01 | Research Institute at Nationwide Children's Hospital | Antibody compositions for disrupting biofilms |
CN110755699A (en) * | 2019-09-18 | 2020-02-07 | 浙江省北大信息技术高等研究院 | Implantable electroosmotic micropump device |
US11813429B1 (en) * | 2022-09-07 | 2023-11-14 | CraniUS LLC | Pump for implantable medical devices |
WO2024054721A1 (en) * | 2022-09-07 | 2024-03-14 | CraniUS LLC | Pump for implantable medical devices |
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