CA1316063C - Portable infusion device assembly - Google Patents
Portable infusion device assemblyInfo
- Publication number
- CA1316063C CA1316063C CA000607723A CA607723A CA1316063C CA 1316063 C CA1316063 C CA 1316063C CA 000607723 A CA000607723 A CA 000607723A CA 607723 A CA607723 A CA 607723A CA 1316063 C CA1316063 C CA 1316063C
- Authority
- CA
- Canada
- Prior art keywords
- pump
- disposed
- compartment
- housing
- wick
- 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 - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M2005/14513—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons with secondary fluid driving or regulating the infusion
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M5/14248—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/12—Pressure infusion
Abstract
PORTABLE INFUSION DEVICE ASSEMBLY
ABSTRACT
A portable infusion device assembly, having two side-by-side compartments, the first containing the drug or agent to be infused and an osmotic pump, and the second containing the driving liquid for the pump. The two chambers are separated during storage by a barrier. When the barrier is ruptured, the driving fluid is carried by means of a wick to the osmotic pump. The drag is then forced out of the device by the pressure developed by the osmotic pump. The assembly is characterized by a very flat profile, and is light, comfortable, and inconspicuous in use.
ABSTRACT
A portable infusion device assembly, having two side-by-side compartments, the first containing the drug or agent to be infused and an osmotic pump, and the second containing the driving liquid for the pump. The two chambers are separated during storage by a barrier. When the barrier is ruptured, the driving fluid is carried by means of a wick to the osmotic pump. The drag is then forced out of the device by the pressure developed by the osmotic pump. The assembly is characterized by a very flat profile, and is light, comfortable, and inconspicuous in use.
Description
~ 3~63 PORTABLE INFUSION DEVICE ASS~M~LY
FIELD OF THE INVENTION
Thls invention relates to contro:Lled release lnfuslon devices, and particularly to small body-mounted devices capable of delivering drugs or other pharmaceutlcal agents for prolonged periods.
BACKGROUND OF THE INV~NTION
Many klnds of parenteral drug therapy require contlnuous delivery in pre~erence to slngle or multlple ln~ections. Beneflts that accrue from continuous therapy may include, for instance, reduction of toxic or other side effects associated with sharp pulses of drug, siynlficant improvement ln the effectiveness of the therapy, and Increased comfort of the patient. The tradi-tional manner of admlnistering sustained parenteral treatments ls an intravenous drlp. While this may he perfectly acceptable ln a hospital environment, it obvlously lmposes severe restrlctions on the activity of the reciplent. As a result, considerable research over the last few years has been ~evoted to the development of small portable infu~ion pumps. A range of devices has appeared, includlng those with electric or clockwork motors that drive syringe or peristaltic pumps, and others powered by the elastic tension of an lnflated balloon, or the vapor pressure of a vola-tile propellant. Literature describing ~uch pumps includes Controlled Release Micropump for Insulin Admlnstratlon, (M.V.
Sefton et al., Ann. Biomed. Eng., Vol. 7, pp. 329-343, 1979~, Continuous Intravenous Arabinosyl Cytoslne Infusions Dellvered by a New Portable Infusion System, (J. Bottlno et al., Cancer, Vol.
43, pp. 2197-2201, 1979), or product brochures from Auto-Syrin~e, Inc., Hooksett, New Hampshire and Cormet, Inc., Medlna, New York.
These devices are typlcally strapped to the wearer, or carrlad on '~:
' X
~.
~1051-2315 a belt or in a harness. Also, most are designed to deliver relatively large quantities of fluid and do not dispense small volumes oE the order of a few milliliteræ or less effectively.
An alternative approach that has been exploited to a llmlted extent is to drive the lnfusor osmotlcally, using a Rose-Nelson pump activated by lmbibltion of water or other driving llquid. In comparison wlth rnechanlcally drlven devices, Rose-Nelson pumps are small, reliahle, and simple and cheap to manufacture. U.S. Patent 3,604,417 discloses a modificatlon of lC the Rose-Nelson pump ln whlch a moveable plston replace~ the elastic diaphragm separating the drug and salt chamber, and both the drug and salt are loaded lnto the pump as solutlons. U.S.
Patent 4,474,048 discloses another modlflcation employing an lmpermeable elastlc wall, and a moveable end wall whlch can be screwed in to dellver a pulse dose of the contalned drug at any tlme durlng the operatlon of the pump. U.S. patent 4,474,575 ls a varlant of 4,474,048 where the flow rate of the dispensed agent can be varled by altering the area of semipermeable membrane exposed to the water chamber. U.S. Patent 4,552,561 dlscloses a pump assembly for use with a small osmotlc pump, which can be filled in advance of use with the actlve agent to be dispensed.
The action of the pump ls initiated by fllling the lower chamber of the houslng with a hydrogel. Once the pump ls in action, an optional mechanism for dellvering pulse doses can be employed.
All the~e osmotic pumps are self driven and begin to operate as soon as they are prlmed with the contents of the several chambers.
Canadian Patent l~?7g~543 issued January 2Y, l991 and commonly owned with the present appllcation describes a portable osmotic lnfuslon pump that can be filled with the agent to be dlspensed, the osmotic salt and the drivlng fluld, and then stored until required.
~ ~ .
~ 3 ~ 3 In developi~g ~ portable inrw;o~l device, thero ar~ p~ion~ compliance as well ~s technical proble~ ~o bo ~ddressed. For IOD8 tOrnL infusioll ther~py to be ~ucce3sful, the infu~ion dovico must ~ accoptable to the weuor, Dev;ccs that are bulky, hesvy, uncomîor~ble or ob~rusive, or that cau~e ~mbarn~ment, or otherwis~ linJit th~ user'~ li~style, or th~t r~quire complicated proceduros to 3et up or monitor, are poorly acccpted. M~ny of the devicos doscri~d ~bove, wh;ch ~pic~lly woigh up to I Ib, aDd h~Yo a bs~o ~rea of 19-20 3quuo inches, suff~r from these inheront problems, Evon ~he smaller units have rigid housings, and are norlIaally carried in a belt, cuff or vest. Tllus there still exists Q longstanding need for comfortable, compac~, discreet devices tbat do not obtrude on the user's lifestyle or appearance.
SUMI~ARY OF THE IN~'ENTION
The present invention provides a portsble controlled releaso infus;on pump assembly. Tha sssembly i~cludes a housing wlth two side-by-sido comp~rtments.
Tho dimensioos of the housing will vary according to the nmounts of drug, driving uid, etc. that ar~ contained, but in genersl the assembly is eharacterized by ~
very flat profile when compared with other infusion devices, This makes ;t easy to co~ce~l under normal clothin~, and reprosents a major ~dvantage in ~erms of patient comfort ~nd acceptability, Vne compartment of the housing coatains aa 2û osmotic pump, co~sisting of 8 umiporQIoable membrsDo ~nd an e~spandable diaphr~gm ~oparsted by an osmotic salt. The other computm~nt contai~3 the :~ drivi~ liqoid ~r the pump, Tbo two compsr~nent~ ars coDDected by a wick.
During ms~ufactur~ a~d 3tor~8e of the dovico the wic~ is separ~ted from the driving liquid by Ul imperm~abb seal. The a~mbly ~Iso includes Im 3Gtiva~Or that n~ptures the seal, thereby ~llowing th~ drivi~g 1iquid to be absorbed into Ihe wick. Thc olher orld of tho wick i~ i~ eo~t~t with ~ho ~omipormoablo Dlo~br~rle,Wh~n the iDfu~o~ il in us~s, liquid tr~lY215 through tho wick ~md cQntac~ the semipermeabJo membrane. The Uquid di~fu!~es Ithrou~h the membrane under a concerltration gradieDt, cresting a saturated~,alt ~olutio~ d e~erting a pressure on the escpandable di~phragm, which i~ tUrD f~r~ ~h~ a~o~t to be dilpensed oot of the as3embly ~hrough a deli~0ry tu~O lrbo os~notic pre~llro dPvolo~d by this type of pump i~ much higher than th~ equi~od ~o pump ~he drug îrom ~he deYice; henco tho drug deli~2ry ~ ~emai~s cons~rlt as 10~8 a3 so~e excess undis~olved sall remain3. The pump ~ ~semely ~i~plo, and once activated, is self sur.t~ ing, thus problems ~ocia~ed with with mechanial failuse, adjustment or monitoring are elimi~ated.
Because they ~re simple and small, o~motic pump~ ue inherently suitable for delivering small drug volumes. The pump assemb1y oî this invention, while it canbe ~ailored for a ran8e of drug volumes and dosage r~tes, is particularly usefulwhere the total drug ~lolume to bo di~pensed u oî the ordler of a îew milliliters, and the delivery time for that volume i~ ~ day or more. Thus tl2e invention enables ther~py in~o!ving highly ~otsnt subs~nces. such 8S powerful anal~es;cs, antidotes to chemical or biolo~ical poisons, ~nd peptide drugs of ~sriou~ kinds, to be carried out without ~ubjecting the victim ta ~peatod injections or sequiring him to be hooked up to sn l~r drip.
The pump has no moving part~, ~nd doe~ Dot Fequire 8 riyid assembly.
Therefore, the pump housing m~y b~ for~ed ~rom B flo~ible material that conform~ ~o body contour~ and body mo~me~t, ~mother n~ajor sdvanfsge a3 f5r u comf~rt and ~inimal iatorrupdon w;th ~regular actiYities is roncor~ed. When fil1ed, the pump as~em'oly typical~y ~w a~out J0 ~o 20 8rRms. The assembly ca~ be aetached to the body of Ihe woarer by ~D adhesi~e co~tin~ oll the b~so ofthe assembly, vr by adhesivl3 ~trip~ or overiy~, Imd do~ ~ot requ;re the use of straps, belts or other carry;ng garmo~es.
Tho sstembly ~ut bo f~llod with l~ ~l h~rod~an~, storod ror prolongod ~ 3 ~ 3 periods of months or years without deterioration, and activated on demand by the user.
It is an object of the present invention then to provide a portable in~usion device that is readily acceptable to users.
It is another object of the invention to provide a portable infusion device that is comfortable ko wear.
It is ano~her object of the invention to provide a portable infusion device that is small and light.
It is another object of the invention to prov:ide a portable infusion device that is inconspicuous in use.
It is another object of the invention to prov:Lde a portable infusion device that is simple to operate.
It is another object of the invention to provide a portable infusion device that is not susceptible to mechanical ; ~ailure.
It is another object of the invention to provide a portable infusion device that can dispense small volumes of active agent over a pro1onged period.
It i~ another object of the invention to provide a portable infusion device that can be prefilled with all components, and activated on demand.
According to a broad aspect of the invention there is provided a portable infusion device assembly, comprising:
a) a housing, defining first and second compartments disposed in side-by-side r~lationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said ~ 5 :
~ 3 ~ 3 second compartment, d) wick means, disposed within said housin~, in liquid transferring relationship between sald first and seccnd compartmen~s, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing sald barrier.
According to another broad aspect of the invention there is provided a housing for a portable osmotic infusion device, comprising:
a) b se 1 te a a p a b) a raised portion defining ~irst and second compartments ; disposed in side-by-side relationship to one another, said raised portion being sealed to said baseplate around its perimeter, c) support means within said first compartment for holdlng an osmotic pump,and d~ sealing means for isolating said first compartment from said second compartment.
Other objects and advantages of the invention will be apparent to those of ordinary skill in ~he art from the description that follows.
BRIEF DESCRIPTIO~ OF TH~ DRAWI~GS
Figure 1 is a perspective view of a basic embodiment of the invention.
Figure 2 is a schematic cross-section along the line 1 1.
5a .
, ~ 3 ~
Figure 3 is a schematic of the compartment containing the driving fluid, showing an alternakive barrier and actlvator means.
Figure 4 is a schematic of the compartment containlng the driving fluid, showing , ' ~ 5b a third type of barrier aod aetiYa~or means.
l:~ElAILEI:) DESCRIPTION QiF THE INVENTION
~l:)rug ' ~ wcd horein broadly lncludes any phyYiolo~ical1y or pharmacologically Be~iva ~u~stance for produci~g a lo~li~ed effect at the administration site or ~ sy~temic ~ffect a~ a ~ito romote from the administration sit~.
Th~ objects de~cribed abovo ~re ~chiev~d by an osmotic pUlDp usembly showD ia perspecti~o ~i~w il~ Figure 1, ~d in cross sectio~ in Fi~ure 2.
Re~erring now to the3e fi~ures, th~ pump a~sembty 1, hu an outer housing 2, defining a first compartment 3, and a second compartment 4. Tlle housing may be made from ~ ri~id or non-rigid material. By non-rigid is meant sufîicien~ly fle~ible to ~ive~ to conform to body contours or movement, yet having enough structurnl integrity to retain the housing shape in normal use. Whereever possi~le, fle~ible materials are preferred, because they allow thc device lo urve to accomodate body contours. However, in some flaxible embodiments, it may be ~: ~ desirable to provide ~ mor~ rigid outer shell Dver eith~r the dru8 or drivin2 fluid ~- chambers, or both9 to avoid accident~l comprcssion of these computments. In preferred embodiments, the second compartme~t 4, i~ msde from a 8rade of material sufficiently soft to yield under atmospheric pressure a~ the driving liquid supply become~ e%hsustod, !10 that the pump is ~ot working ~gQin5t ~ bsck pressure. The housillg m~teri81 should be chemicslly inert and imperrneable to the salt~, ~olutions and s~enls coDtsined, no~-irritsSin~ to tho ~kin, accoptable for ~terll~l medical u~e, and capablo of 8t~riliz~tion. Material~ th~t ~ight bo uscdfor forming tho ho~sin8 inctude, for 01ulmpb, ne~tible or ri&id 8rado~ of polyvinyl 2~ chloride, polymethylmethscrylato, or polyethylone, or polycarbol~nt~, poly~ulîono or the like. The hou~ing may be manuf~cturod by injoctiv~ or comproi~ion moldin~, vacuum forming or any ~tandard techniql~e for handliag ~hermoplastic ~ 3 ~ 3 polymers. Alternatively, rigid embodins~ntj may bo formoâ from ~h;n sheets of stainless s~eel, a2uminum or like metal. It i~ ~noral~y çonYenîent to form the housing jD ~WO parls, n fla~ baseplate S, and ~ nu~ed portion 6, and ~o join thetwo parts around the perimeter by heat ~ealin~, ~eldin or by means of ~
~ppropri4to sdh~ive. Tho buopla~o aqd ~he ni30d portio~ m~y, bllt Deed no2, be m~de of ~he samo material or the ~e 8rade of that mater;all. IRi~id em~odiments misht ~Iso be machined from lightweiRht, inert ~ot~l part~. In msny instances itwill be desirable that ~t Ic~st the raised porti~ns of tho hou3in~ defining the t-Yo compartments be 6ransparent to ~sist tl~e user i~ monitoring the status of dru~
or driving fluid.
The drug 7, to be dispensed, is contained witbin tho first compsrtmen~ 3.
The drug may gonerally be 811y ngent or combination of a8ents capable of administration by the parenteral route. A preferr~d embodimont employs a drug dissolved in an appropriate solve~, generally water. ~Iternatively, if Iho drug to be used is u~stable io solution, the device can be ~embled with Iy~philized drug, or withou~ drug. Water or drug solutio~ may the~ be add~d immcdia~ely prisr to use. Drugs that could bo used i~ th$ Wlly include, for e~can~ple, pro~in or peptide drugs such as insulin, growth hormones or illterfero~. Tho pump is filled with drug~ and solver~ts ~hrough the îill pon 8 which may be placed at ~ny convenient point on the îirs~ compartment 3. A secoDd port 9, allows for displacemeDt of air by tho dru8 ~olution. Wbon th~ pump has bee~ rillcd the port~ 8r~e heat ~ealodl or otherwise closod. Duri~g u~e, drug leave~ the device through a tbird por/ 10, ~d t~bc I I. The tube may be in~erted during Dlanufacture of ~ho device, may be formed int0grally ~ith tho housing, or ~nay be i~erted immediately before use. The e~d o the tubc r~mote from the device may be adapted for wo with a ~kin-piercia~ needle OT ~ t~uldard commercial : 7 ~ 3 ~ 3 61051-~315 suhcutaneous drug delivery set, for example, the Sub-Q-Set~
obtainable ~rom Travenol Laboratories, Deerfield, Illinois.
Alternatively the tube may be lnserted lnto one of the normal body orifices. Optionally one of the ports used during filling may be reopened and used as the delivery port.
The Eirst compartment 3, a7so contains the osmotic pump 12, conslsting of an elastic diaphragm 13, and a semipermeable membrane 14, separated by an osmotic salt 15. The delivery rate of the pump depends on the area, thlckness and permeabllity of the lU semipermeable membrane. Hence the choice of a suitable membrane materlal ls essential to good performance of khe pump. A prefer-red choice ls a membrane made from one of the cellulose esters or ethers, such as cellulose acetate or cellulose butyrate. Cellulose acetate has a long record of use in membrane appllcations and can easily be formed into thin fllms of reproducible thickness with standard solution castlncJ techniques, maklng it a particularly preferred cholce.
A wlde range of approprlate solutes for use in osmotic pumps is disclosed in U.S. Patent number 4,034,756. Preferred salts are sodium chloride, potasslum chlorlde, magneslum sulfate and sodium sulfate. These give a good range of osmotic pressure dlfferences across the membrane and provide a means whereby the flow rate of the pump can be varied to suit the desired applica-tion.
The infusion device of the present inventlon can be fllled, stored for extended perlods of time and then actlvated on demand. It is, therefore, important that the elastic diaphr~gm be lmpermeable to the chosen drug, lest slow migration of drug into the salt chamber cau~e the device to deteriorate during storage.
A wide range of standard impermeable materials with good elasto-~ meric properties is known in the art, such as latex rubber, poly-`~ isoprene, butyl rubber, nitrile rubber, copolymers of ~ styrene/butadiene and the like. When prolonged , stora~e periods of months or ye~ uo env^~a~, it i~ preferrsd to use a s~andard elE~tomer fncod with a thin layer of aluminum foi1~ which will rupture as soon as the elastic diaphr~gm be2ins to oj~pand. A ~scond preîerred alternative is to use 8 metallized elastic material, formed by Y8cuum depc~ition of sluminum orother metals o~ an otastic rubber-b~ed material.
Manufac~ure i~ ~impliîiod if the osmotic pump i~ pre~i~smbled. Thi~ c~n be done by preparing a lamioate by ~irst ~ttsehin~ ~he membra~ls ~o the support member 16, typically by m~ans of an epoxy or ~imilar ~dhosive. The salt dislc isthern placed on top of the membtane and covered with the cliaphsa~m, v~hich i5 in turn attached to tl~e support member by epoxy glue or otherwise. The support member may conYeniently, al~hough not necessatily, be formed ftom the same ma~erial as the hou~ing ~nd sandwiched ~çtween ~he upper and 10wer portions of the hou~ing during manufacture.
The sscond compartment 4, contains tho osmotie drivin~ liquid 17. Tho :15 liquid i3 introduced throu3h fill port IC, which i3 thell sealed. Tlie driving liquid is normally water, slthough any liquid c~pablc of ~enersting an o~motic pres~urein eonjunction with ~he solute could bo used. Before the pump is actiY~ted, the driving liqu;d is separated from the wick by an impermeable barrier. The barrier~ay take ~ number of forms. In the embodiment shown in Figur~s î and 2 the barrier comprises a se~l 19, made from metsl îoil, motalliæd plastic film or thelike, ooverin$ a hols 20, in the ~upport momber 16. Thi~ ~mbodi~ent is acti~ated by deprcssing the top of th8 ~eco~d compartment ~o that start button 21, en~en the hole 20, thereby perfor~ti~ the 3081 aDd ~llowin~ lho driving liquid to co~twt the wick 22. Other possible alter~ative moth~ of ~opara~iD~s 2~ tho driving liquid and wick9 and of activatirl~ the ~ump, ue show~ ia Fi~ure~ 3 s~d 4. Ref'errin~ ww to Figuro 3, tho impormeQblo b~rrior 23, h~3 a pro~ilo as aho~n, and includ~ ~ ri~g 24, ~vhero th~ b~rricr mat~ri~l it comp~r~ltiYely thin , and weak. l'he pump is aeti~rated by depre~ ho 3tar~ butto~ 25, c~using the barrier to break around the ri~g 23. In tho ombodi~nt of Figure 4, the impormQable b~rrier 26, h~s a radiAI ~core 27, def;nin~ a woak zone. The barrieris broken by fle~ing ~hc device sloag the ~coro. It sho~ld bg apparent that a variety of oiechanic~l solution~ to Iho barrier/activation ~obl0m are passible and that the methods describod ~r~ not ~c1u3iw. Th~ iOV3~ iDcJudes lhe concep~
of a barrier a~d an activatin~ do~vico ~nd the sc~pe of the in~O~tiOD i~ intended to encompas~ any mechar~i~m that wouid pert'orm theso fuD~ions.
The wick mat~ria1 may be filter paper, or aDy porow or ~pongy msierial capable of absorbing and transporting the dri~ing liquid.
In use, the assembly of the present inven~ion may be sttached to the body of the user by means of a biocompatible adhesive spplied to the baseplate, or byadhesive strips or ovorlays. The de~ice may be attached anywhere on the body that i~ conYeniont, sither immediately adjacent to the deliv~ry site, or dt a point distant from that site.
Tbe followin~ e~t~mples ~re give~ by way oî illus~ration to further e~pl~in the principles of the in~ention. These e;tamples a~e meroly illustr~tive and are not to be understood as 1imiting thc scopo and unde~ying priwiples of the inven~ion in ~ny way.
:
EXAMPLE 1.
The basic emb~diment Or ~ho irlYentio~ ~own in ~i~ure5 1 snd 2 was prcpared. Th8 howin~ of th~ devico ~nd tho intern~l ~upport momber wore f~bricat~d ~rom 16-mil-thick doublo polished po1yvinyl cllloridt ~heet. The 25 ~ membrano ~a~ a collulo~e acetatB fil3n 25 micron3 tl~ick (Clarifoil 912AA, Courtaulds CPD, I~c., Newark, N.J.). The 61a~ti~: diaphr~gm WQS ~ ~r~toD~ 1652 ~ f,~ o i ~6~3 (Shell Chemical t:~o., Houston, Te~a33 film 40-60 micro~ thick, prep~red by solvent ca~tin~. Tho 03motic #IJt wU 1~ k of ~odium chlor;de 0.03 in thick, and containod 2~ Ac-Di-SOP SD-711 ~b1et di~integr~J~t (~;MC Corp., Philadelphia, PA).
Tho pump 3a~dwich, coD3i3tin~ of tho 3upport, di~phragm aold membrane with the ~alt disk betw~ol3, was pro-~se~ ~ witb epoxy.
The devico ~e~b1y ~as ~ab~ tod in ~hrec layer~. Tho bottom layer wa3 R
PVC ~hoet Ol~ whiell ~ placed 1I fi~ter paper wick ~ppro~ima~ely I i~ by l.S im A~o~hcr sheet oî PVC, cont~ mombra~ t/diaphragm s~b~ssembly, and having rour 0.2S-in-diame2er uniformly ~paced holss cover~d by a disk of aluminum ~oil, was placed on top. ~ho top layer v~as vacu-formed to create a dru~ chamber and a water chan~ avin3 a general shap~ a3 shown in Figure 2, and tubular connections for rilling the chambers and delivering the dru~. Four 0.12S-in draw-downs wero formed in the top Or thc water chamber, at positions correspoDding to tho hole~ in th~ internal support chamber. The three PVC
~heets were aligned, then joined by RF ~velding.
The fi~ished pump had overall dimension~ of 1.7S in by 3.4 in by 0.4 in, weighed about 7 grams emp~y, ~d had a ~vater capacity of ~ppro;cimately 4 rnL
a~d 8 drug c~pac;ty ot appro~im~tdy Rcltai~
EXAMPLE 2.
~D iDlrUsiOII devico usoDbl~ ~ pr~pared u in Example 1. The driving liquid wed ~v~ water. Tlle dsvico w~ fillod ~rith a siDlulated dru~, solution coraptisin~ 2wtS6 ~,JYGUOI in wster. 'Tho doYic~ was l~tartod sndl ~llowo~ to pump i~to ~ colloction veg~el co~ irlg 1~0 mI, o~ wator. Tho colleo~io~ v~ssel wa~
~tirred conti~luo~ly to o~uro proper ani~ting. ~mplo~ wors withdrawn periodically, ~nd the conc~n~ration of ~Iycerol meuured by HPLC. The pumpin~
$ 3 r~te ws~ ealculsted from ~ho ~e of chan8e oî ~Iycerol collc~ntr~tion in the collectio~ ves~e1, and wu fou~d to b9 0.~0 mL/day.
The expcriment~ wero ropo~ted ~ith otlher basches of pumps prepared in the ~ame way. Pu~npiD~ rate~ of 0.~2 mL/d~y aDd 0.94 mL/day ~were measurod.
FIELD OF THE INVENTION
Thls invention relates to contro:Lled release lnfuslon devices, and particularly to small body-mounted devices capable of delivering drugs or other pharmaceutlcal agents for prolonged periods.
BACKGROUND OF THE INV~NTION
Many klnds of parenteral drug therapy require contlnuous delivery in pre~erence to slngle or multlple ln~ections. Beneflts that accrue from continuous therapy may include, for instance, reduction of toxic or other side effects associated with sharp pulses of drug, siynlficant improvement ln the effectiveness of the therapy, and Increased comfort of the patient. The tradi-tional manner of admlnistering sustained parenteral treatments ls an intravenous drlp. While this may he perfectly acceptable ln a hospital environment, it obvlously lmposes severe restrlctions on the activity of the reciplent. As a result, considerable research over the last few years has been ~evoted to the development of small portable infu~ion pumps. A range of devices has appeared, includlng those with electric or clockwork motors that drive syringe or peristaltic pumps, and others powered by the elastic tension of an lnflated balloon, or the vapor pressure of a vola-tile propellant. Literature describing ~uch pumps includes Controlled Release Micropump for Insulin Admlnstratlon, (M.V.
Sefton et al., Ann. Biomed. Eng., Vol. 7, pp. 329-343, 1979~, Continuous Intravenous Arabinosyl Cytoslne Infusions Dellvered by a New Portable Infusion System, (J. Bottlno et al., Cancer, Vol.
43, pp. 2197-2201, 1979), or product brochures from Auto-Syrin~e, Inc., Hooksett, New Hampshire and Cormet, Inc., Medlna, New York.
These devices are typlcally strapped to the wearer, or carrlad on '~:
' X
~.
~1051-2315 a belt or in a harness. Also, most are designed to deliver relatively large quantities of fluid and do not dispense small volumes oE the order of a few milliliteræ or less effectively.
An alternative approach that has been exploited to a llmlted extent is to drive the lnfusor osmotlcally, using a Rose-Nelson pump activated by lmbibltion of water or other driving llquid. In comparison wlth rnechanlcally drlven devices, Rose-Nelson pumps are small, reliahle, and simple and cheap to manufacture. U.S. Patent 3,604,417 discloses a modificatlon of lC the Rose-Nelson pump ln whlch a moveable plston replace~ the elastic diaphragm separating the drug and salt chamber, and both the drug and salt are loaded lnto the pump as solutlons. U.S.
Patent 4,474,048 discloses another modlflcation employing an lmpermeable elastlc wall, and a moveable end wall whlch can be screwed in to dellver a pulse dose of the contalned drug at any tlme durlng the operatlon of the pump. U.S. patent 4,474,575 ls a varlant of 4,474,048 where the flow rate of the dispensed agent can be varled by altering the area of semipermeable membrane exposed to the water chamber. U.S. Patent 4,552,561 dlscloses a pump assembly for use with a small osmotlc pump, which can be filled in advance of use with the actlve agent to be dispensed.
The action of the pump ls initiated by fllling the lower chamber of the houslng with a hydrogel. Once the pump ls in action, an optional mechanism for dellvering pulse doses can be employed.
All the~e osmotic pumps are self driven and begin to operate as soon as they are prlmed with the contents of the several chambers.
Canadian Patent l~?7g~543 issued January 2Y, l991 and commonly owned with the present appllcation describes a portable osmotic lnfuslon pump that can be filled with the agent to be dlspensed, the osmotic salt and the drivlng fluld, and then stored until required.
~ ~ .
~ 3 ~ 3 In developi~g ~ portable inrw;o~l device, thero ar~ p~ion~ compliance as well ~s technical proble~ ~o bo ~ddressed. For IOD8 tOrnL infusioll ther~py to be ~ucce3sful, the infu~ion dovico must ~ accoptable to the weuor, Dev;ccs that are bulky, hesvy, uncomîor~ble or ob~rusive, or that cau~e ~mbarn~ment, or otherwis~ linJit th~ user'~ li~style, or th~t r~quire complicated proceduros to 3et up or monitor, are poorly acccpted. M~ny of the devicos doscri~d ~bove, wh;ch ~pic~lly woigh up to I Ib, aDd h~Yo a bs~o ~rea of 19-20 3quuo inches, suff~r from these inheront problems, Evon ~he smaller units have rigid housings, and are norlIaally carried in a belt, cuff or vest. Tllus there still exists Q longstanding need for comfortable, compac~, discreet devices tbat do not obtrude on the user's lifestyle or appearance.
SUMI~ARY OF THE IN~'ENTION
The present invention provides a portsble controlled releaso infus;on pump assembly. Tha sssembly i~cludes a housing wlth two side-by-sido comp~rtments.
Tho dimensioos of the housing will vary according to the nmounts of drug, driving uid, etc. that ar~ contained, but in genersl the assembly is eharacterized by ~
very flat profile when compared with other infusion devices, This makes ;t easy to co~ce~l under normal clothin~, and reprosents a major ~dvantage in ~erms of patient comfort ~nd acceptability, Vne compartment of the housing coatains aa 2û osmotic pump, co~sisting of 8 umiporQIoable membrsDo ~nd an e~spandable diaphr~gm ~oparsted by an osmotic salt. The other computm~nt contai~3 the :~ drivi~ liqoid ~r the pump, Tbo two compsr~nent~ ars coDDected by a wick.
During ms~ufactur~ a~d 3tor~8e of the dovico the wic~ is separ~ted from the driving liquid by Ul imperm~abb seal. The a~mbly ~Iso includes Im 3Gtiva~Or that n~ptures the seal, thereby ~llowing th~ drivi~g 1iquid to be absorbed into Ihe wick. Thc olher orld of tho wick i~ i~ eo~t~t with ~ho ~omipormoablo Dlo~br~rle,Wh~n the iDfu~o~ il in us~s, liquid tr~lY215 through tho wick ~md cQntac~ the semipermeabJo membrane. The Uquid di~fu!~es Ithrou~h the membrane under a concerltration gradieDt, cresting a saturated~,alt ~olutio~ d e~erting a pressure on the escpandable di~phragm, which i~ tUrD f~r~ ~h~ a~o~t to be dilpensed oot of the as3embly ~hrough a deli~0ry tu~O lrbo os~notic pre~llro dPvolo~d by this type of pump i~ much higher than th~ equi~od ~o pump ~he drug îrom ~he deYice; henco tho drug deli~2ry ~ ~emai~s cons~rlt as 10~8 a3 so~e excess undis~olved sall remain3. The pump ~ ~semely ~i~plo, and once activated, is self sur.t~ ing, thus problems ~ocia~ed with with mechanial failuse, adjustment or monitoring are elimi~ated.
Because they ~re simple and small, o~motic pump~ ue inherently suitable for delivering small drug volumes. The pump assemb1y oî this invention, while it canbe ~ailored for a ran8e of drug volumes and dosage r~tes, is particularly usefulwhere the total drug ~lolume to bo di~pensed u oî the ordler of a îew milliliters, and the delivery time for that volume i~ ~ day or more. Thus tl2e invention enables ther~py in~o!ving highly ~otsnt subs~nces. such 8S powerful anal~es;cs, antidotes to chemical or biolo~ical poisons, ~nd peptide drugs of ~sriou~ kinds, to be carried out without ~ubjecting the victim ta ~peatod injections or sequiring him to be hooked up to sn l~r drip.
The pump has no moving part~, ~nd doe~ Dot Fequire 8 riyid assembly.
Therefore, the pump housing m~y b~ for~ed ~rom B flo~ible material that conform~ ~o body contour~ and body mo~me~t, ~mother n~ajor sdvanfsge a3 f5r u comf~rt and ~inimal iatorrupdon w;th ~regular actiYities is roncor~ed. When fil1ed, the pump as~em'oly typical~y ~w a~out J0 ~o 20 8rRms. The assembly ca~ be aetached to the body of Ihe woarer by ~D adhesi~e co~tin~ oll the b~so ofthe assembly, vr by adhesivl3 ~trip~ or overiy~, Imd do~ ~ot requ;re the use of straps, belts or other carry;ng garmo~es.
Tho sstembly ~ut bo f~llod with l~ ~l h~rod~an~, storod ror prolongod ~ 3 ~ 3 periods of months or years without deterioration, and activated on demand by the user.
It is an object of the present invention then to provide a portable in~usion device that is readily acceptable to users.
It is another object of the invention to provide a portable infusion device that is comfortable ko wear.
It is ano~her object of the invention to provide a portable infusion device that is small and light.
It is another object of the invention to prov:ide a portable infusion device that is inconspicuous in use.
It is another object of the invention to prov:Lde a portable infusion device that is simple to operate.
It is another object of the invention to provide a portable infusion device that is not susceptible to mechanical ; ~ailure.
It is another object of the invention to provide a portable infusion device that can dispense small volumes of active agent over a pro1onged period.
It i~ another object of the invention to provide a portable infusion device that can be prefilled with all components, and activated on demand.
According to a broad aspect of the invention there is provided a portable infusion device assembly, comprising:
a) a housing, defining first and second compartments disposed in side-by-side r~lationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said ~ 5 :
~ 3 ~ 3 second compartment, d) wick means, disposed within said housin~, in liquid transferring relationship between sald first and seccnd compartmen~s, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing sald barrier.
According to another broad aspect of the invention there is provided a housing for a portable osmotic infusion device, comprising:
a) b se 1 te a a p a b) a raised portion defining ~irst and second compartments ; disposed in side-by-side relationship to one another, said raised portion being sealed to said baseplate around its perimeter, c) support means within said first compartment for holdlng an osmotic pump,and d~ sealing means for isolating said first compartment from said second compartment.
Other objects and advantages of the invention will be apparent to those of ordinary skill in ~he art from the description that follows.
BRIEF DESCRIPTIO~ OF TH~ DRAWI~GS
Figure 1 is a perspective view of a basic embodiment of the invention.
Figure 2 is a schematic cross-section along the line 1 1.
5a .
, ~ 3 ~
Figure 3 is a schematic of the compartment containing the driving fluid, showing an alternakive barrier and actlvator means.
Figure 4 is a schematic of the compartment containlng the driving fluid, showing , ' ~ 5b a third type of barrier aod aetiYa~or means.
l:~ElAILEI:) DESCRIPTION QiF THE INVENTION
~l:)rug ' ~ wcd horein broadly lncludes any phyYiolo~ical1y or pharmacologically Be~iva ~u~stance for produci~g a lo~li~ed effect at the administration site or ~ sy~temic ~ffect a~ a ~ito romote from the administration sit~.
Th~ objects de~cribed abovo ~re ~chiev~d by an osmotic pUlDp usembly showD ia perspecti~o ~i~w il~ Figure 1, ~d in cross sectio~ in Fi~ure 2.
Re~erring now to the3e fi~ures, th~ pump a~sembty 1, hu an outer housing 2, defining a first compartment 3, and a second compartment 4. Tlle housing may be made from ~ ri~id or non-rigid material. By non-rigid is meant sufîicien~ly fle~ible to ~ive~ to conform to body contours or movement, yet having enough structurnl integrity to retain the housing shape in normal use. Whereever possi~le, fle~ible materials are preferred, because they allow thc device lo urve to accomodate body contours. However, in some flaxible embodiments, it may be ~: ~ desirable to provide ~ mor~ rigid outer shell Dver eith~r the dru8 or drivin2 fluid ~- chambers, or both9 to avoid accident~l comprcssion of these computments. In preferred embodiments, the second compartme~t 4, i~ msde from a 8rade of material sufficiently soft to yield under atmospheric pressure a~ the driving liquid supply become~ e%hsustod, !10 that the pump is ~ot working ~gQin5t ~ bsck pressure. The housillg m~teri81 should be chemicslly inert and imperrneable to the salt~, ~olutions and s~enls coDtsined, no~-irritsSin~ to tho ~kin, accoptable for ~terll~l medical u~e, and capablo of 8t~riliz~tion. Material~ th~t ~ight bo uscdfor forming tho ho~sin8 inctude, for 01ulmpb, ne~tible or ri&id 8rado~ of polyvinyl 2~ chloride, polymethylmethscrylato, or polyethylone, or polycarbol~nt~, poly~ulîono or the like. The hou~ing may be manuf~cturod by injoctiv~ or comproi~ion moldin~, vacuum forming or any ~tandard techniql~e for handliag ~hermoplastic ~ 3 ~ 3 polymers. Alternatively, rigid embodins~ntj may bo formoâ from ~h;n sheets of stainless s~eel, a2uminum or like metal. It i~ ~noral~y çonYenîent to form the housing jD ~WO parls, n fla~ baseplate S, and ~ nu~ed portion 6, and ~o join thetwo parts around the perimeter by heat ~ealin~, ~eldin or by means of ~
~ppropri4to sdh~ive. Tho buopla~o aqd ~he ni30d portio~ m~y, bllt Deed no2, be m~de of ~he samo material or the ~e 8rade of that mater;all. IRi~id em~odiments misht ~Iso be machined from lightweiRht, inert ~ot~l part~. In msny instances itwill be desirable that ~t Ic~st the raised porti~ns of tho hou3in~ defining the t-Yo compartments be 6ransparent to ~sist tl~e user i~ monitoring the status of dru~
or driving fluid.
The drug 7, to be dispensed, is contained witbin tho first compsrtmen~ 3.
The drug may gonerally be 811y ngent or combination of a8ents capable of administration by the parenteral route. A preferr~d embodimont employs a drug dissolved in an appropriate solve~, generally water. ~Iternatively, if Iho drug to be used is u~stable io solution, the device can be ~embled with Iy~philized drug, or withou~ drug. Water or drug solutio~ may the~ be add~d immcdia~ely prisr to use. Drugs that could bo used i~ th$ Wlly include, for e~can~ple, pro~in or peptide drugs such as insulin, growth hormones or illterfero~. Tho pump is filled with drug~ and solver~ts ~hrough the îill pon 8 which may be placed at ~ny convenient point on the îirs~ compartment 3. A secoDd port 9, allows for displacemeDt of air by tho dru8 ~olution. Wbon th~ pump has bee~ rillcd the port~ 8r~e heat ~ealodl or otherwise closod. Duri~g u~e, drug leave~ the device through a tbird por/ 10, ~d t~bc I I. The tube may be in~erted during Dlanufacture of ~ho device, may be formed int0grally ~ith tho housing, or ~nay be i~erted immediately before use. The e~d o the tubc r~mote from the device may be adapted for wo with a ~kin-piercia~ needle OT ~ t~uldard commercial : 7 ~ 3 ~ 3 61051-~315 suhcutaneous drug delivery set, for example, the Sub-Q-Set~
obtainable ~rom Travenol Laboratories, Deerfield, Illinois.
Alternatively the tube may be lnserted lnto one of the normal body orifices. Optionally one of the ports used during filling may be reopened and used as the delivery port.
The Eirst compartment 3, a7so contains the osmotic pump 12, conslsting of an elastic diaphragm 13, and a semipermeable membrane 14, separated by an osmotic salt 15. The delivery rate of the pump depends on the area, thlckness and permeabllity of the lU semipermeable membrane. Hence the choice of a suitable membrane materlal ls essential to good performance of khe pump. A prefer-red choice ls a membrane made from one of the cellulose esters or ethers, such as cellulose acetate or cellulose butyrate. Cellulose acetate has a long record of use in membrane appllcations and can easily be formed into thin fllms of reproducible thickness with standard solution castlncJ techniques, maklng it a particularly preferred cholce.
A wlde range of approprlate solutes for use in osmotic pumps is disclosed in U.S. Patent number 4,034,756. Preferred salts are sodium chloride, potasslum chlorlde, magneslum sulfate and sodium sulfate. These give a good range of osmotic pressure dlfferences across the membrane and provide a means whereby the flow rate of the pump can be varied to suit the desired applica-tion.
The infusion device of the present inventlon can be fllled, stored for extended perlods of time and then actlvated on demand. It is, therefore, important that the elastic diaphr~gm be lmpermeable to the chosen drug, lest slow migration of drug into the salt chamber cau~e the device to deteriorate during storage.
A wide range of standard impermeable materials with good elasto-~ meric properties is known in the art, such as latex rubber, poly-`~ isoprene, butyl rubber, nitrile rubber, copolymers of ~ styrene/butadiene and the like. When prolonged , stora~e periods of months or ye~ uo env^~a~, it i~ preferrsd to use a s~andard elE~tomer fncod with a thin layer of aluminum foi1~ which will rupture as soon as the elastic diaphr~gm be2ins to oj~pand. A ~scond preîerred alternative is to use 8 metallized elastic material, formed by Y8cuum depc~ition of sluminum orother metals o~ an otastic rubber-b~ed material.
Manufac~ure i~ ~impliîiod if the osmotic pump i~ pre~i~smbled. Thi~ c~n be done by preparing a lamioate by ~irst ~ttsehin~ ~he membra~ls ~o the support member 16, typically by m~ans of an epoxy or ~imilar ~dhosive. The salt dislc isthern placed on top of the membtane and covered with the cliaphsa~m, v~hich i5 in turn attached to tl~e support member by epoxy glue or otherwise. The support member may conYeniently, al~hough not necessatily, be formed ftom the same ma~erial as the hou~ing ~nd sandwiched ~çtween ~he upper and 10wer portions of the hou~ing during manufacture.
The sscond compartment 4, contains tho osmotie drivin~ liquid 17. Tho :15 liquid i3 introduced throu3h fill port IC, which i3 thell sealed. Tlie driving liquid is normally water, slthough any liquid c~pablc of ~enersting an o~motic pres~urein eonjunction with ~he solute could bo used. Before the pump is actiY~ted, the driving liqu;d is separated from the wick by an impermeable barrier. The barrier~ay take ~ number of forms. In the embodiment shown in Figur~s î and 2 the barrier comprises a se~l 19, made from metsl îoil, motalliæd plastic film or thelike, ooverin$ a hols 20, in the ~upport momber 16. Thi~ ~mbodi~ent is acti~ated by deprcssing the top of th8 ~eco~d compartment ~o that start button 21, en~en the hole 20, thereby perfor~ti~ the 3081 aDd ~llowin~ lho driving liquid to co~twt the wick 22. Other possible alter~ative moth~ of ~opara~iD~s 2~ tho driving liquid and wick9 and of activatirl~ the ~ump, ue show~ ia Fi~ure~ 3 s~d 4. Ref'errin~ ww to Figuro 3, tho impormeQblo b~rrior 23, h~3 a pro~ilo as aho~n, and includ~ ~ ri~g 24, ~vhero th~ b~rricr mat~ri~l it comp~r~ltiYely thin , and weak. l'he pump is aeti~rated by depre~ ho 3tar~ butto~ 25, c~using the barrier to break around the ri~g 23. In tho ombodi~nt of Figure 4, the impormQable b~rrier 26, h~s a radiAI ~core 27, def;nin~ a woak zone. The barrieris broken by fle~ing ~hc device sloag the ~coro. It sho~ld bg apparent that a variety of oiechanic~l solution~ to Iho barrier/activation ~obl0m are passible and that the methods describod ~r~ not ~c1u3iw. Th~ iOV3~ iDcJudes lhe concep~
of a barrier a~d an activatin~ do~vico ~nd the sc~pe of the in~O~tiOD i~ intended to encompas~ any mechar~i~m that wouid pert'orm theso fuD~ions.
The wick mat~ria1 may be filter paper, or aDy porow or ~pongy msierial capable of absorbing and transporting the dri~ing liquid.
In use, the assembly of the present inven~ion may be sttached to the body of the user by means of a biocompatible adhesive spplied to the baseplate, or byadhesive strips or ovorlays. The de~ice may be attached anywhere on the body that i~ conYeniont, sither immediately adjacent to the deliv~ry site, or dt a point distant from that site.
Tbe followin~ e~t~mples ~re give~ by way oî illus~ration to further e~pl~in the principles of the in~ention. These e;tamples a~e meroly illustr~tive and are not to be understood as 1imiting thc scopo and unde~ying priwiples of the inven~ion in ~ny way.
:
EXAMPLE 1.
The basic emb~diment Or ~ho irlYentio~ ~own in ~i~ure5 1 snd 2 was prcpared. Th8 howin~ of th~ devico ~nd tho intern~l ~upport momber wore f~bricat~d ~rom 16-mil-thick doublo polished po1yvinyl cllloridt ~heet. The 25 ~ membrano ~a~ a collulo~e acetatB fil3n 25 micron3 tl~ick (Clarifoil 912AA, Courtaulds CPD, I~c., Newark, N.J.). The 61a~ti~: diaphr~gm WQS ~ ~r~toD~ 1652 ~ f,~ o i ~6~3 (Shell Chemical t:~o., Houston, Te~a33 film 40-60 micro~ thick, prep~red by solvent ca~tin~. Tho 03motic #IJt wU 1~ k of ~odium chlor;de 0.03 in thick, and containod 2~ Ac-Di-SOP SD-711 ~b1et di~integr~J~t (~;MC Corp., Philadelphia, PA).
Tho pump 3a~dwich, coD3i3tin~ of tho 3upport, di~phragm aold membrane with the ~alt disk betw~ol3, was pro-~se~ ~ witb epoxy.
The devico ~e~b1y ~as ~ab~ tod in ~hrec layer~. Tho bottom layer wa3 R
PVC ~hoet Ol~ whiell ~ placed 1I fi~ter paper wick ~ppro~ima~ely I i~ by l.S im A~o~hcr sheet oî PVC, cont~ mombra~ t/diaphragm s~b~ssembly, and having rour 0.2S-in-diame2er uniformly ~paced holss cover~d by a disk of aluminum ~oil, was placed on top. ~ho top layer v~as vacu-formed to create a dru~ chamber and a water chan~ avin3 a general shap~ a3 shown in Figure 2, and tubular connections for rilling the chambers and delivering the dru~. Four 0.12S-in draw-downs wero formed in the top Or thc water chamber, at positions correspoDding to tho hole~ in th~ internal support chamber. The three PVC
~heets were aligned, then joined by RF ~velding.
The fi~ished pump had overall dimension~ of 1.7S in by 3.4 in by 0.4 in, weighed about 7 grams emp~y, ~d had a ~vater capacity of ~ppro;cimately 4 rnL
a~d 8 drug c~pac;ty ot appro~im~tdy Rcltai~
EXAMPLE 2.
~D iDlrUsiOII devico usoDbl~ ~ pr~pared u in Example 1. The driving liquid wed ~v~ water. Tlle dsvico w~ fillod ~rith a siDlulated dru~, solution coraptisin~ 2wtS6 ~,JYGUOI in wster. 'Tho doYic~ was l~tartod sndl ~llowo~ to pump i~to ~ colloction veg~el co~ irlg 1~0 mI, o~ wator. Tho colleo~io~ v~ssel wa~
~tirred conti~luo~ly to o~uro proper ani~ting. ~mplo~ wors withdrawn periodically, ~nd the conc~n~ration of ~Iycerol meuured by HPLC. The pumpin~
$ 3 r~te ws~ ealculsted from ~ho ~e of chan8e oî ~Iycerol collc~ntr~tion in the collectio~ ves~e1, and wu fou~d to b9 0.~0 mL/day.
The expcriment~ wero ropo~ted ~ith otlher basches of pumps prepared in the ~ame way. Pu~npiD~ rate~ of 0.~2 mL/d~y aDd 0.94 mL/day ~were measurod.
Claims (7)
1. A portable infusion device assembly, comprising:
a) a housing, defining first and second compartments disposed in side-by-side relationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said second compartment, d) wick means, disposed within said housing, in liquid transferring relationship between said first and second compartments, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing said barrier.
a) a housing, defining first and second compartments disposed in side-by-side relationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said second compartment, d) wick means, disposed within said housing, in liquid transferring relationship between said first and second compartments, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing said barrier.
2. A portable infusion device assembly, comprising:
a) a flexible housing, defining first and second compartments disposed in side-by-side relationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said second compartment, d) wick means, disposed within said housing, in liquid transferring relationship between said first and second compartments, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing said barrier.
a) a flexible housing, defining first and second compartments disposed in side-by-side relationship to one another, b) an osmotic pump, disposed within said first compartment, c) a driving liquid for said pump disposed within said second compartment, d) wick means, disposed within said housing, in liquid transferring relationship between said first and second compartments, e) a barrier disposed between said wick means and said driving liquid, and separating said driving liquid from said wick, and f) means for rupturing said barrier.
3. A housing for a portable osmotic infusion device, comprising:
a) a baseplate, b) a raised portion defining first and second compartments disposed in side-by-side relationship to one another, said raised portion being sealed to said baseplate around its perimeter, c) support means within said first compartment for holding an osmotic pump, and d) sealing means for isolating said first compartment from said second compartment.
a) a baseplate, b) a raised portion defining first and second compartments disposed in side-by-side relationship to one another, said raised portion being sealed to said baseplate around its perimeter, c) support means within said first compartment for holding an osmotic pump, and d) sealing means for isolating said first compartment from said second compartment.
4. The housing of claim 3, wherein said baseplate is flexible.
5. The housing of claim 3, wherein said raised portion is flexible.
6. The housing of claim 3, wherein said second compartment is flexible.
7. The housing of claim 3, wherein said support means and said sealing means comprise a single internal support member disposed generally parallel to said baseplate, said single internal support being sealed to said raised portion around its perimeter and between said first and second compartments.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/230,620 US4898582A (en) | 1988-08-09 | 1988-08-09 | Portable infusion device assembly |
| US230,620 | 1988-08-09 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1316063C true CA1316063C (en) | 1993-04-13 |
Family
ID=22865929
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000607723A Expired - Fee Related CA1316063C (en) | 1988-08-09 | 1989-08-08 | Portable infusion device assembly |
Country Status (11)
| Country | Link |
|---|---|
| US (1) | US4898582A (en) |
| EP (1) | EP0354742B1 (en) |
| JP (1) | JPH02119871A (en) |
| AT (1) | ATE102839T1 (en) |
| AU (1) | AU634481B2 (en) |
| CA (1) | CA1316063C (en) |
| DE (1) | DE68913854T2 (en) |
| ES (1) | ES2050243T3 (en) |
| MX (1) | MX166422B (en) |
| NO (1) | NO172326C (en) |
| NZ (1) | NZ230182A (en) |
Families Citing this family (110)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE3915251A1 (en) * | 1989-05-10 | 1990-11-22 | Annemarie Schloegl Ges M B H | IMPLANTABLE DEVICE FOR DISPENSING DISPOSAL OF MEDICINES IN HUMAN BODIES |
| US5336188A (en) * | 1989-06-16 | 1994-08-09 | Science Incorporated | Fluid delivery apparatus having a stored energy source |
| US5135498A (en) * | 1990-04-02 | 1992-08-04 | Kam Robert J | Controlled release infusion device |
| US5085644A (en) * | 1990-04-02 | 1992-02-04 | Pudenz-Schulte Medical Research Corporation | Sterilizable medication infusion device with dose recharge restriction |
| US5152753A (en) * | 1990-04-02 | 1992-10-06 | Pudenz-Schulte Medical Research Corporation | Medication infusion device with dose recharge restriction |
| US5672167A (en) * | 1990-05-21 | 1997-09-30 | Recordati Corporation | Controlled release osmotic pump |
| US5169390A (en) * | 1990-05-21 | 1992-12-08 | Athayde Amulya L | Osmotic infusion device |
| US5257987A (en) * | 1990-05-21 | 1993-11-02 | Pharmetrix Corporation | Controlled release osmotic infusion system |
| GB9027422D0 (en) * | 1990-12-18 | 1991-02-06 | Scras | Osmotically driven infusion device |
| GB2250920B (en) * | 1990-12-18 | 1995-03-08 | Scras | Osmotic pumps |
| US6358239B1 (en) * | 1992-01-24 | 2002-03-19 | I-Flow Corporation | Platen pump |
| US6251098B1 (en) | 1992-01-24 | 2001-06-26 | I-Flow, Corp. | Fluid container for use with platen pump |
| US5306257A (en) * | 1992-05-04 | 1994-04-26 | Prime Medical Products, Inc. | Drug infuser |
| DE19509634C1 (en) * | 1995-03-17 | 1996-03-28 | Fresenius Ag | Implantable infusion pump with constant delivery rate |
| US5785688A (en) * | 1996-05-07 | 1998-07-28 | Ceramatec, Inc. | Fluid delivery apparatus and method |
| US6977074B2 (en) * | 1997-07-10 | 2005-12-20 | Mannkind Corporation | Method of inducing a CTL response |
| US6994851B1 (en) | 1997-07-10 | 2006-02-07 | Mannkind Corporation | Method of inducing a CTL response |
| US6264634B1 (en) * | 1997-07-25 | 2001-07-24 | Seiko Instruments Inc. | Implant type chemical supply device |
| US6833242B2 (en) * | 1997-09-23 | 2004-12-21 | California Institute Of Technology | Methods for detecting and sorting polynucleotides based on size |
| US7214298B2 (en) * | 1997-09-23 | 2007-05-08 | California Institute Of Technology | Microfabricated cell sorter |
| US7244396B2 (en) | 1999-04-06 | 2007-07-17 | Uab Research Foundation | Method for preparation of microarrays for screening of crystal growth conditions |
| US20030022383A1 (en) * | 1999-04-06 | 2003-01-30 | Uab Research Foundation | Method for screening crystallization conditions in solution crystal growth |
| US7247490B2 (en) * | 1999-04-06 | 2007-07-24 | Uab Research Foundation | Method for screening crystallization conditions in solution crystal growth |
| ATE357656T1 (en) * | 1999-04-06 | 2007-04-15 | Univ Alabama Res Found | DEVICE FOR SCREENING CRYSTALIZATION CONDITIONS IN CRYSTAL GROWING SOLUTIONS |
| US7214540B2 (en) | 1999-04-06 | 2007-05-08 | Uab Research Foundation | Method for screening crystallization conditions in solution crystal growth |
| US7250305B2 (en) * | 2001-07-30 | 2007-07-31 | Uab Research Foundation | Use of dye to distinguish salt and protein crystals under microcrystallization conditions |
| US6193704B1 (en) * | 1999-06-10 | 2001-02-27 | Thomas F. Winters | Site-specific postoperative pain relief system, fit and method |
| US8550119B2 (en) * | 1999-06-28 | 2013-10-08 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US7217321B2 (en) * | 2001-04-06 | 2007-05-15 | California Institute Of Technology | Microfluidic protein crystallography techniques |
| US8709153B2 (en) | 1999-06-28 | 2014-04-29 | California Institute Of Technology | Microfludic protein crystallography techniques |
| US7052545B2 (en) * | 2001-04-06 | 2006-05-30 | California Institute Of Technology | High throughput screening of crystallization of materials |
| US20080277007A1 (en) * | 1999-06-28 | 2008-11-13 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US7144616B1 (en) * | 1999-06-28 | 2006-12-05 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US7306672B2 (en) * | 2001-04-06 | 2007-12-11 | California Institute Of Technology | Microfluidic free interface diffusion techniques |
| CA2721172C (en) * | 1999-06-28 | 2012-04-10 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US7244402B2 (en) * | 2001-04-06 | 2007-07-17 | California Institute Of Technology | Microfluidic protein crystallography |
| US6899137B2 (en) * | 1999-06-28 | 2005-05-31 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US7195670B2 (en) * | 2000-06-27 | 2007-03-27 | California Institute Of Technology | High throughput screening of crystallization of materials |
| US7459022B2 (en) * | 2001-04-06 | 2008-12-02 | California Institute Of Technology | Microfluidic protein crystallography |
| US8052792B2 (en) * | 2001-04-06 | 2011-11-08 | California Institute Of Technology | Microfluidic protein crystallography techniques |
| US6929030B2 (en) * | 1999-06-28 | 2005-08-16 | California Institute Of Technology | Microfabricated elastomeric valve and pump systems |
| US6464688B1 (en) | 2000-02-15 | 2002-10-15 | Microsolutions, Inc. | Osmotic pump delivery system with flexible drug compartment |
| AU2001240040A1 (en) * | 2000-03-03 | 2001-09-17 | California Institute Of Technology | Combinatorial array for nucleic acid analysis |
| AU2001249214A1 (en) | 2000-03-15 | 2001-09-24 | The Brigham And Women's Hospital, Inc. | Suppression of vascular disorders by mucosal administration of heat shock protein peptides |
| US20050118073A1 (en) * | 2003-11-26 | 2005-06-02 | Fluidigm Corporation | Devices and methods for holding microfluidic devices |
| US7867763B2 (en) | 2004-01-25 | 2011-01-11 | Fluidigm Corporation | Integrated chip carriers with thermocycler interfaces and methods of using the same |
| US7351376B1 (en) * | 2000-06-05 | 2008-04-01 | California Institute Of Technology | Integrated active flux microfluidic devices and methods |
| US6829753B2 (en) * | 2000-06-27 | 2004-12-07 | Fluidigm Corporation | Microfluidic design automation method and system |
| EP1334347A1 (en) | 2000-09-15 | 2003-08-13 | California Institute Of Technology | Microfabricated crossflow devices and methods |
| US7678547B2 (en) * | 2000-10-03 | 2010-03-16 | California Institute Of Technology | Velocity independent analyte characterization |
| US7097809B2 (en) * | 2000-10-03 | 2006-08-29 | California Institute Of Technology | Combinatorial synthesis system |
| US7258774B2 (en) * | 2000-10-03 | 2007-08-21 | California Institute Of Technology | Microfluidic devices and methods of use |
| AU1189702A (en) * | 2000-10-13 | 2002-04-22 | Fluidigm Corp | Microfluidic device based sample injection system for analytical devices |
| WO2002065005A1 (en) * | 2000-11-06 | 2002-08-22 | California Institute Of Technology | Electrostatic valves for microfluidic devices |
| EP1343973B2 (en) | 2000-11-16 | 2020-09-16 | California Institute Of Technology | Apparatus and methods for conducting assays and high throughput screening |
| AU2002248149A1 (en) * | 2000-11-16 | 2002-08-12 | Fluidigm Corporation | Microfluidic devices for introducing and dispensing fluids from microfluidic systems |
| US20050196785A1 (en) * | 2001-03-05 | 2005-09-08 | California Institute Of Technology | Combinational array for nucleic acid analysis |
| US7670429B2 (en) * | 2001-04-05 | 2010-03-02 | The California Institute Of Technology | High throughput screening of crystallization of materials |
| DE60239328D1 (en) * | 2001-04-06 | 2011-04-14 | Fluidigm Corp | POLYMER SURFACE MODIFICATION |
| US20020164816A1 (en) * | 2001-04-06 | 2002-11-07 | California Institute Of Technology | Microfluidic sample separation device |
| US6752922B2 (en) * | 2001-04-06 | 2004-06-22 | Fluidigm Corporation | Microfluidic chromatography |
| AU2002307152A1 (en) * | 2001-04-06 | 2002-10-21 | California Institute Of Technology | Nucleic acid amplification utilizing microfluidic devices |
| US6632217B2 (en) * | 2001-04-19 | 2003-10-14 | Microsolutions, Inc. | Implantable osmotic pump |
| US20050149304A1 (en) * | 2001-06-27 | 2005-07-07 | Fluidigm Corporation | Object oriented microfluidic design method and system |
| US7075162B2 (en) * | 2001-08-30 | 2006-07-11 | Fluidigm Corporation | Electrostatic/electrostrictive actuation of elastomer structures using compliant electrodes |
| US7192629B2 (en) | 2001-10-11 | 2007-03-20 | California Institute Of Technology | Devices utilizing self-assembled gel and method of manufacture |
| US8440093B1 (en) | 2001-10-26 | 2013-05-14 | Fuidigm Corporation | Methods and devices for electronic and magnetic sensing of the contents of microfluidic flow channels |
| EP1314910A1 (en) * | 2001-11-21 | 2003-05-28 | Honeywell International, Inc. | Arrangement for producing a rotary movement |
| EP1463796B1 (en) * | 2001-11-30 | 2013-01-09 | Fluidigm Corporation | Microfluidic device and methods of using same |
| US7691333B2 (en) * | 2001-11-30 | 2010-04-06 | Fluidigm Corporation | Microfluidic device and methods of using same |
| US20040073175A1 (en) * | 2002-01-07 | 2004-04-15 | Jacobson James D. | Infusion system |
| FR2836520B1 (en) * | 2002-02-28 | 2004-07-16 | Univ Joseph Fourier | OSMOTIC ACTUATOR AND MOTOR |
| EP1499706A4 (en) | 2002-04-01 | 2010-11-03 | Fluidigm Corp | Microfluidic particle-analysis systems |
| US7312085B2 (en) * | 2002-04-01 | 2007-12-25 | Fluidigm Corporation | Microfluidic particle-analysis systems |
| US20070026528A1 (en) * | 2002-05-30 | 2007-02-01 | Delucas Lawrence J | Method for screening crystallization conditions in solution crystal growth |
| US20060086309A1 (en) * | 2002-06-24 | 2006-04-27 | Fluiding Corporation | Recirculating fluidic network and methods for using the same |
| US20040007672A1 (en) * | 2002-07-10 | 2004-01-15 | Delucas Lawrence J. | Method for distinguishing between biomolecule and non-biomolecule crystals |
| EP1551753A2 (en) * | 2002-09-25 | 2005-07-13 | California Institute Of Technology | Microfluidic large scale integration |
| US8220494B2 (en) * | 2002-09-25 | 2012-07-17 | California Institute Of Technology | Microfluidic large scale integration |
| JP5695287B2 (en) | 2002-10-02 | 2015-04-01 | カリフォルニア インスティテュート オブ テクノロジー | Nucleic acid analysis of microfluids |
| US7476363B2 (en) * | 2003-04-03 | 2009-01-13 | Fluidigm Corporation | Microfluidic devices and methods of using same |
| US8828663B2 (en) * | 2005-03-18 | 2014-09-09 | Fluidigm Corporation | Thermal reaction device and method for using the same |
| US7604965B2 (en) * | 2003-04-03 | 2009-10-20 | Fluidigm Corporation | Thermal reaction device and method for using the same |
| US20050145496A1 (en) | 2003-04-03 | 2005-07-07 | Federico Goodsaid | Thermal reaction device and method for using the same |
| US7666361B2 (en) * | 2003-04-03 | 2010-02-23 | Fluidigm Corporation | Microfluidic devices and methods of using same |
| WO2004094020A2 (en) * | 2003-04-17 | 2004-11-04 | Fluidigm Corporation | Crystal growth devices and systems, and methods for using same |
| CA2526368A1 (en) * | 2003-05-20 | 2004-12-02 | Fluidigm Corporation | Method and system for microfluidic device and imaging thereof |
| US8025053B1 (en) * | 2003-06-26 | 2011-09-27 | Mine Safety Appliances Company | Pressure regulator assembly |
| SG145697A1 (en) * | 2003-07-28 | 2008-09-29 | Fluidigm Corp | Image processing method and system for microfluidic devices |
| US7413712B2 (en) * | 2003-08-11 | 2008-08-19 | California Institute Of Technology | Microfluidic rotary flow reactor matrix |
| KR20060099520A (en) | 2003-10-21 | 2006-09-19 | 노보 노르디스크 에이/에스 | Medical skin mountable device |
| EP1527792A1 (en) * | 2003-10-27 | 2005-05-04 | Novo Nordisk A/S | Medical injection device mountable to the skin |
| DE602004025025D1 (en) * | 2003-10-27 | 2010-02-25 | Novo Nordisk As | ON THE SKIN FIXABLE MEDICAL INJECTION DEVICE |
| US7407799B2 (en) * | 2004-01-16 | 2008-08-05 | California Institute Of Technology | Microfluidic chemostat |
| WO2005072353A2 (en) * | 2004-01-25 | 2005-08-11 | Fluidigm Corporation | Crystal forming devices and systems and methods for making and using the same |
| US20060024751A1 (en) * | 2004-06-03 | 2006-02-02 | Fluidigm Corporation | Scale-up methods and systems for performing the same |
| CA2592922A1 (en) * | 2004-12-29 | 2006-07-06 | Mannkind Corporation | Methods to trigger, maintain and manipulate immune responses by targeted administration of biological response modifiers into lymphoid organs |
| US8691772B2 (en) | 2005-01-04 | 2014-04-08 | Yeda Research And Development Co. Ltd. | HSP60, HSP60 peptides and T cell vaccines for immunomodulation |
| EP1877116A1 (en) * | 2005-04-13 | 2008-01-16 | Novo Nordisk A/S | Medical skin mountable device and system |
| CN101262897A (en) * | 2005-09-13 | 2008-09-10 | 诺沃-诺迪斯克有限公司 | Reservoir device with inspection aid for detection of drug condition |
| WO2007045644A1 (en) * | 2005-10-17 | 2007-04-26 | Novo Nordisk A/S | Vented drug reservoir unit |
| US7815868B1 (en) | 2006-02-28 | 2010-10-19 | Fluidigm Corporation | Microfluidic reaction apparatus for high throughput screening |
| US8211053B2 (en) * | 2008-05-13 | 2012-07-03 | Equilibrate, Llc | Interosmolar fluid removal |
| EP2331240A2 (en) | 2008-08-28 | 2011-06-15 | Microlin, LLC | Apparatus and method for delivering beneficial liquids at steady rate |
| DK2453953T3 (en) * | 2009-07-14 | 2018-08-06 | Sanofi Aventis Deutschland | Medication container with a flexible inner layer and a rigid outer layer |
| JP5963265B2 (en) * | 2013-03-19 | 2016-08-03 | 株式会社アクアテック | Micro pump |
| US20160058940A1 (en) * | 2014-08-28 | 2016-03-03 | Zyno Medical, LLC. | Low-cost ambulatory medical pump |
| WO2019071129A1 (en) * | 2017-10-05 | 2019-04-11 | Pirouette Medical LLC | Protective case for an auto-injector |
| WO2019242821A1 (en) * | 2018-06-18 | 2019-12-26 | Subcuject Aps | An osmotic actuator for an injecting device and an injection device comprising such an osmotic actuator |
| JPWO2021210126A1 (en) | 2020-04-16 | 2021-10-21 |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3604417A (en) * | 1970-03-31 | 1971-09-14 | Wayne Henry Linkenheimer | Osmotic fluid reservoir for osmotically activated long-term continuous injector device |
| US4193398A (en) * | 1978-05-25 | 1980-03-18 | Watson-Marlow Limited | Fluid displacement |
| US4340048A (en) * | 1981-03-28 | 1982-07-20 | Alza Corporation | Self-driven hypodermic injector |
| DE3138320A1 (en) * | 1981-09-25 | 1983-04-14 | Siemens AG, 1000 Berlin und 8000 München | INFUSION DEVICE PROVIDED FOR IMPLANTATION IN A LIVING BODY |
| US4552561A (en) * | 1982-12-23 | 1985-11-12 | Alza Corporation | Body mounted pump housing and pump assembly employing the same |
| US4689044A (en) * | 1984-10-23 | 1987-08-25 | Aso Pharmaceutical Co., Ltd. | First-aid adhesive bandage |
| US4655766A (en) * | 1985-08-01 | 1987-04-07 | Alza Corporation | Fluid imbibing pump with self-regulating skin patch |
| US4838862A (en) * | 1986-08-04 | 1989-06-13 | Pharmetrix Corp. | Portable controlled release osmotic infusion device |
-
1988
- 1988-08-09 US US07/230,620 patent/US4898582A/en not_active Expired - Fee Related
-
1989
- 1989-07-27 AU AU39021/89A patent/AU634481B2/en not_active Ceased
- 1989-08-02 NZ NZ23018289A patent/NZ230182A/en unknown
- 1989-08-04 ES ES89307970T patent/ES2050243T3/en not_active Expired - Lifetime
- 1989-08-04 EP EP89307970A patent/EP0354742B1/en not_active Expired - Lifetime
- 1989-08-04 AT AT89307970T patent/ATE102839T1/en not_active IP Right Cessation
- 1989-08-04 DE DE68913854T patent/DE68913854T2/en not_active Expired - Fee Related
- 1989-08-08 MX MX017120A patent/MX166422B/en unknown
- 1989-08-08 CA CA000607723A patent/CA1316063C/en not_active Expired - Fee Related
- 1989-08-08 NO NO893199A patent/NO172326C/en unknown
- 1989-08-09 JP JP1206578A patent/JPH02119871A/en active Pending
Also Published As
| Publication number | Publication date |
|---|---|
| ATE102839T1 (en) | 1994-04-15 |
| EP0354742A3 (en) | 1990-07-25 |
| JPH02119871A (en) | 1990-05-07 |
| NZ230182A (en) | 1994-07-26 |
| NO172326B (en) | 1993-03-29 |
| MX166422B (en) | 1993-01-07 |
| NO172326C (en) | 1993-07-07 |
| EP0354742B1 (en) | 1994-03-16 |
| DE68913854T2 (en) | 1994-08-11 |
| AU634481B2 (en) | 1993-02-25 |
| NO893199L (en) | 1990-02-12 |
| ES2050243T3 (en) | 1994-05-16 |
| US4898582A (en) | 1990-02-06 |
| AU3902189A (en) | 1990-02-15 |
| DE68913854D1 (en) | 1994-04-21 |
| NO893199D0 (en) | 1989-08-08 |
| EP0354742A2 (en) | 1990-02-14 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKLA | Lapsed |