the invention relates to miniature long - term delivery devices and pen - like injection devices specifically designed for use with new anhydrous , solid drug compositions . the long - term delivery devices , which are preferably implantable , dispense the solid drug compositions according to a predetermined delivery profile . the solid drug compositions include one or more drugs and one or more carriers , and are preferably in the form of a cylindrical filament or flat tape that is pliable enough to be handled and inserted into and dispensed from a delivery device , yet strong enough to withstand such manipulation . the cross - sectional shape and dimensions of these filaments or tapes must be consistent along their length , and small enough to allow for high precision in the delivery of the drug based on a given length of the filament or tape . these filaments have a diameter of , e . g ., 0 . 1 to 0 . 5 mm , and preferably 0 . 2 to 0 . 3 mm , and can be one half to several meters in length . the tapes can be up to 0 . 1 mm thick and 2 . 0 to 5 . 0 mm wide . the ratio of the surface area to the weight of the drug in the solid drug compositions , e . g ., filaments or tapes , is also important to achieve a rapid dispersion of the drug from the composition once introduced into the bodily fluids of a patient . for a substantially non - porous solid composition this ratio should be at least 10 mm 2 of surface area per milligram of the drug in the solid composition , and can range up to 30 mm 2 to 60 mm 2 or more per milligram of drug . for a porous solid composition , the surface area can be much higher , because the pores add to the total surface area . in this case , the ratio can be in the range of 100 mm 2 per milligram . these ratios can be achieved by preparing the solid drug filaments as described below . for example , a cylindrical filament with a diameter of 0 . 25 mm and a length of 10 mm has a total surface area of about 8 . 25 mm 2 ( including the ends of the filament ). if this filament contains , e . g ., 0 . 165 mg of insulin , e . g ., 40 % insulin in a composition with a total weight of 0 . 4125 mg , the surface area to drug weight ratio is about 50 mm 2 per milligram . the drug or drugs can be homogeneously distributed throughout the solid filament , or can be distributed only in discrete segments of the filament . similarly , combinations of drugs can be homogeneously mixed throughout the composition , or distributed into separate discrete portions in a desired sequence to provide sequential delivery of different drugs . sections of the composition without any drug can be interspersed between sections including a drug or drugs to provide intermittent or pulsatile delivery of the drug or drugs . certain drugs can themselves be formulated into a solid filament or tape without any carrier . for example , so - called &# 34 ; pro - drugs &# 34 ; are polymerized from hybrid molecules of a cross - linkable drug , e . g ., a drug and a cross - linkable moiety , e . g ., sugar or polyamino acid , e . g ., polyarginine , derivatives . however , a typical drug composition will include at least 30 % and up to 90 % of the drug or drugs depending on the physical characteristics of the carrier and the resulting filament or tape . preferably the composition contains at least 50 % of the drug . even when a carrier is used , an advantage of the solid drug compositions is that they minimize the total amount of carrier introduced into the patient . in particular , the drug compositions preferably include less than 50 % by weight of a carrier . many liquid drug formulations include organic solvents or other additives , e . g ., to change the ph to force the drug to dissolve in the solution . such solvents and additives are usually toxic to the patient , even in small amounts , and thus , it is advantageous to minimize their use . the invention also avoids formulation and solubility problems of liquid drug solutions . therefore , the drug compositions can include any one or more of a wide variety of drugs , even those which are insoluble or otherwise incompatible with standard liquid formulations , because the drug , e . g ., in particulate form , can be merely dispersed in the carrier to form a suspension without dissolving the drug . the resulting homogenous mixture is then solidified . as a result , drugs that are insoluble , or that are otherwise incompatible when in solution , can be easily incorporated into a solid drug composition . another advantage of the invention is the increased stability of the drug in the solid composition . drug solutions are often difficult to keep stable for prolonged periods of time . the anhydrous , solid drug compositions largely avoid this problem . moreover , solid compositions are not subject to the same sheer forces and turbulence that break down proteins and peptides in solution . thus , the drug or drugs in the solid drug compositions are stable for long periods of time compared to the same drugs in a liquid formulation . drugs that can be used in the solid drug compositions include polypeptides such as growth hormone ( gh ), growth hormone releasing peptide ( ghrp ), growth hormone releasing factor ( grf ), epidermal growth factor , interferon , insulin , somatostatin , bombesin , calcitonin , calcitonin gene related peptide ( cgrp ), amylin , parathyroid hormone ( pth ), parathyroid hormone related peptide ( pthrp ), gastrin , gastrin releasing peptide ( grp ), melanocyte stimulating hormone ( msh ), adrenocorticotrophic hormone ( acth ), luteinizing hormone ( lh ), luteinizing hormone - releasing hormone ( lh - rh ), cytokinases , sorbine , cholecystokinin ( cck ), glucagon , glucagon - like peptide ( glp ), gastrin , enkephalin , neuromedin , endothelin , substance p , neuropeptide y ( npy ), peptide yy ( pyy ), vasoactive intestinal peptide ( vip ), pituitary adenylate cyclase activating polypeptide ( pacap ), bradykinin , thyrotropin releasing hormone ( trh ), or derivatives , fragments , analogs , agonists , or antagonists of any of the foregoing . preferably , the drug is used for diabetes , inflammation , oncology , cardiology , hormone therapy , gynecology , immunology , metabolism , or maturation , or as a vaccine . examples of such drugs include insulin , adrenalin , xylocaine , morphine , corticoid compounds , atropine , cytostatic compounds , estrogen , anti - paf ( platelet activating factor ) agents such as ginkolides ( e . g ., bn 52021 or bn50730 , beaufour ipsen , france ), androgen , interleukin , digitoxin , biotin , testosterone , heparin , cyclosporin , penicillin , vitamins , somatriptan ™, or diazepam . the nature of the drug composition depends upon the type of delivery device to be used . the drug composition can contain any of a large number of carriers , with only minor , if any , limitations in terms of delivery properties or toxicity , because of the small carrier volume . when the drug composition is intended to be dispensed into the body from the delivery device , the carrier should be water - soluble . suitable water - soluble carriers include such polymers as hyaluronic acid , cellulose , e . g ., hydroxy propyl methylcellulose ( hpmc ), carboxyl methylcellulose ( cmc ), and hydroxy ethylcellulose ( hec ), polyalcohols such as mannitol , sugars , e . g ., dextrose , mannose , or glucose , and starches . when the drug composition is intended to be merely exposed to bodily fluids , but not dispensed directly into the body from the delivery device , the carrier should be substantially water - insoluble , but preferably biodegradable to allow the drug to easily be released from the carrier . examples of suitable water - insoluble polymers include l - lactic acid , d - lactic acid , dl - lactic acid , glycolide , glycolic acid , and any optically active isomers , racemates , or copolymers thereof . non - biodegradable , water - insoluble carriers are also useful , and include silicon , nylon , polypropylene , polyethylene , silk , or cotton . other suitable water - insoluble carriers include fatty acids , collagens , lipids , and waxes . a carrier , e . g ., hec , hpmc , or hyaluronic acid , and water are added to a container , e . g ., a 10 ml syringe which was previously covered at the bottom with a stopper . the two ingredients are mixed , e . g ., using a spatula , to homogeneity . once a gel is formed and allowed to reach structural equilibrium , e . g ., after about 24 hours , the gel is mixed with the desired drug or drugs in another container , e . g ., a 2 ml plastic syringe . if no carrier is used , the drug itself is mixed with water . the resulting gel / drug mixture , or drug / water paste , is kneaded to homogeneity , e . g ., with a spatula . the mixture is then transferred to an extrusion device , e . g ., a stainless steel syringe , with an extrusion nozzle , e . g ., a hollow cylindrical needle attached to the syringe if a cylindrical filament is desired . other nozzle shapes can be used to create flat tapes of the gel / drug mixture or the drug / water paste . the amount of drug per amount of gel can be varied in separate batches of gel and then added to the extrusion device in sequence to create a filament that will dispense different drugs in the desired sequence . similarly , batches of gel without any drug can be interspersed between batches of drug containing gel to create a filament that provides intermittent drug delivery . the gel / drug mixture is extruded into a drying chamber as a continuous cylindrical filament or flattened tape , depending on the cross - sectional shape of the extrusion nozzle . for drying , the barrel of an extrusion syringe can be connected to the drying chamber of a mini - spray dryer ( buchi 190 , buchi laboratoriums technik ag , switzerland ), and the extruded filament or tape is collected , e . g ., onto a sieve placed at 10 cm under the exit of the needle , so as to avoid stretching of the filament after extrusion . the drying system is heated , e . g ., to 40 ° c ., and connected to an air blower . the filament is therefore partially dried immediately upon exiting the needle , which also tends to avoid undesired stretching . the filament is further dried under vacuum until all water is removed , e . g ., for 24 hours . the filament can also be dried under continuous vacuum from the moment of extrusion into a glass vessel . the filament can also be collected into a coagulation bath and then dried to avoid stretching . other standard techniques , such as fusion extrusion or wet or dry spinning , also can be used to create the solid drug filaments . all of these techniques involve moving a non - solid mass of material through an orifice with a particular shape that produces an elongated filament with a desired cross - section . this filament can be directly dried or otherwise solidified , or can be stretched and then solidified . the material is made non - solid by heating or adding a solvent , and is returned to a solid state by cooling or removing the solvent by , e . g ., evaporation , freeze drying , or vacuum drying , respectively . to determine the mass percentage of drug in the filament , samples of a specific length are taken , the total amount of drug is removed from the filament , e . g ., by acetic acid 0 . 1 % in water or any other appropriate drug solvent , and is measured using standard hplc methodology . for example , when the drug is insulin , a chromatograph column of kromasil - c8 5 μm 25 × 0 . 46 cm can be used . the mobile phase is an isocratic mixture of acetonitrile and 0 . 1 % triethylamine in 0 . 2m na 2 so 4 , ph of 2 . 3 . the various drug components are detected under uv at 220 nm . the solvent for the sample is 0 . 05n hcl and 0 . 2 mm cetyl - tri - methyl - ammonium bromide ( sigma ). after drying is complete , the tensile strength of the drug - containing filaments or tapes , is measured to determine its propensity to break . this method involves incrementally stretching a filament until it breaks and recording this requisite minimum force . breakage strength , elasticity , and other mechanical parameters of the filaments or tapes can all be measured , e . g ., with a universal testing instrument ( lloyd 1000r , lloyd instruments , england ). to proceed with this analysis , ten equal lengths of the same filament are tested . each filament length is individually tested on the device to determine a strength / extension ratio . elasticity module , strength at breaking , maximum energy required for breaking , and other mechanical properties can be calculated from a graph ( fig1 ). the weight / length ratio is also calculated for each of ten equal lengths of ten different filaments . a specific filament is utilized only if the relative standard deviation ( rsd ) of this ratio is less than 1 %. this rsd equals the ( standard deviation of the weight / length ratio ÷ mean )× 100 , so it is a measure of the uniformity of the weight / length ratio . to ensure uniformity of a given filament , which may be one or more meters in length , samples are taken at the beginning and the end of the filament and compared . these same samples are also used for the hplc drug content analysis . the precise dosage of the filament can then be calculated for a given length of the filament . for example , a cylindrical filament of 0 . 2 mm diameter , loaded with 45 % somatuline ™ and 55 % hec , will provide a dosage of 0 . 125 mg for each 1 cm of length dispensed into the bodily fluids . in another example , pure insulin , e . g ., recombinant human insulin , provides about 26 to 28 insulin units ( iu ) per mg depending on purity . therefore , a filament having a diameter of 0 . 3 mm , loaded with 50 % insulin and 50 % hyaluronic acid will provide a dosage of 0 . 27 mg or about 7 . 3 iu per cm . such solid insulin filaments can then be used to administer the required dosage , e . g ., 20 to 50 , and even up to 200 iu per day , merely by administering the proper length of filament to the patient . furthermore , at body temperature , such an insulin filament should remain stable for several months to over a year . once the above tests are satisfied and the precise dosage per unit length is calculated , each filament is loaded into a delivery device as described below . the present solid drug compositions and devices are well - suited for insulin therapy . the devices are small enough to be implanted subcutaneously or intraperitoneally and are designed to dispense precise amounts of a drug over prolonged periods of time . the solid drug filaments are stable and provide a high dosage per unit volume . solid filaments of insulin and hec as a carrier were manufactured according to the method described above . human recombinant insulin ( hri ) was mixed with a hec gel to provide a solid filament containing 40 % insulin by weight . the above protocol was performed by mixing 1 . 0 g of hec and 9 . 0 g of water . 0 . 26417 g of the resulting gel was added to 0 . 02648 g of hri . the mixture was extruded through a 2 . 3 mm syringe ( 0 . 3 mm internal diameter needle ) with a harvard syringe pump . the filaments were extruded and dried under vacuum for 24 hours , and were examined for homogeneity , stability , and solidity . these filaments provided a good precision of insulin delivery at a dosage of 0 . 184 mg insulin ( 4 . 96 iu )/ cm . the filaments were then tested in terms of biopharmaceutical activity by implanting given lengths of filaments into beagle dogs subcutaneously . the hypoglycemic effect of the filaments were measured and compared to the same dosage administered as a liquid insulin solution . as shown in the graphs of fig2 and 3 the solid filaments (◯) were found to have essentially the same effect on insulin level ( fig2 ), and to be as efficient in lowering the blood glucose level ( fig3 ) as the standard liquid insulin formulation (). fig2 and 3 show the mean results of six different dog tests . similarly , bovine pancreas insulin ( bpi ) was mixed with hec to form a solid drug composition containing 50 % insulin . the above protocol was performed by mixing 1 . 5 g of hec and 8 . 5 g of water . 0 . 37733 g of the resulting gel was added to 0 . 05643 g of bpi . the mixture was extruded through a 2 . 3 mm syringe ( 0 . 3 mm internal diameter needle ) with a harvard syringe pump . the filaments were obtained by extrusion and drying under vacuum for 24 hours , and provided a good precision of insulin delivery at a dosage of 0 . 206 mg insulin ( 5 . 56 iu )/ cm . filaments were also made with a somatostatin analog , somatuline ™ ( bim 23014c , biomeasure , milford mass .) and hec or hyaluronic acid as the carrier to produce a solid composition containing 50 % somatuline ™. the above protocol was performed by mixing 1 . 500 g of hec and 8 . 500 g of water . 0 . 42250 g of the resulting gel was added to 0 . 06395 g of bim 23014 . the mixture was extruded through a 2 . 3 mm syringe ( 0 . 3 mm internal diameter needle ), collected , and dried under vacuum for 24 hours . the dried filament contained 0 . 107 mg of bim 23014 / cm ( weight percentage 50 % hec and 50 % bim 23014 ). the filaments were tested for pharmacokinetics and compared to liquid infusions of the same dosage of somatuline ™ in dogs . the results are shown in the graphs in fig4 a , 4b , and 5 . as shown in fig4 a and 4b , the solution formulation provided an initial blood concentration of somatuline ™ of about 0 . 5 ng / ml . however , the blood concentration decreased to less than 0 . 1 ng / ml within about 2 hours , to less than 0 . 001 within about 8 hours , and to about 0 . 0005 ng / ml in less than 12 hours . on the other hand , the blood concentration of somatuline ™ provided by the solid drug filament was at an almost constant level over 0 . 1 ng / ml for the first 10 hours , declined to about 0 . 002 ng / ml within 24 hours , and declined further to 0 . 0005 ng / ml by 72 hours . similarly , fig5 shows the results of administrations of somatuline ™ filaments to five different dogs . the different symbols in the graph , i . e ., square , circle , triangle , represent different dogs . dog number 267 was injected intravenously , whereas the other dogs were injected subcutaneously . filaments were also made with a synthetic peptide agonist analog of lh - rh , triptorelin acetate ( shally et al ., u . s . pat . no . 4 , 010 , 125 ), and hec as the carrier , to produce a solid composition containing 50 % triptorelin . the above protocol was performed by mixing 1 . 500 g of hec and 8 . 500 g of water . 0 . 19778 g of the resulting gel was added to 0 . 02968 g of triptorelin acetate . the mixture was extruded through a 2 . 3 mm syringe ( 0 . 3 mm internal diameter needle ), collected , and dried under vacuum for 24 hours . the resulting filament contained 0 . 216 mg triptorelin / cm ( weight percentage 50 % hec and 50 % triptorelin ). an important advantage of this invention is the miniaturization of the drug reservoir compared to standard liquid drug dispensing devices . solid drug compositions occupy a very small volume in comparison with liquid drug formulations . with many drugs , this reduces the total volume by hundreds or thousands of times , and thus allows the present devices to be much smaller than prior implantable liquid drug pumps . the miniaturization of the drug reservoir is highly compatible with miniature motors , electronics , and batteries , and results in a very small total size and volume of the device . the device motor and movement are lighter and more energy efficient than comparable motors for liquid pumps because of the greatly reduced drug volume . whatever the drug , one can make a device with a duration and delivery profile adapted to a specific disease . the delivery device will always contain the following elements : 1 ) a solid drug composition with or without a carrier as required for the specific delivery system which is protected from the surrounding environment , e . g ., the bodily fluids ; 2 ) an actuator capable of delivering this drug composition to the patient ; 3 ) a power source ; 4 ) a transit or contact area where the drug is released from the composition to the environment outside of the device ; and 5 ) a housing to enclose all , or at least the liquid - sensitive , of these parts and the drug composition , fitted together in a specific manner for a specific remedy and / or therapy . with reference to fig6 to 9 , device 10 includes a housing 12 , which encloses all of the other parts of the device and the solid drug composition , which is in the form of a filament 14 , and prevents contact of these parts with the environment outside the device , e . g ., bodily fluids . housing 12 may be machined or molded from a suitable heat resistant , chemically inert , sterilizable , rigid material , e . g ., polyvinylchloride , polycarbonate , teflon ®, polysulfone ® ( amoco ), stainless steel , or titanium . the housing may be transparent to facilitate the determination of whether filament 14 , is properly feeding through the device . the external dimensions of the housing may be about 4 cm by 2 cm , and 1 cm high , or 3 cm in diameter by 1 cm in height when in cylindrical form . housing 12 is sealed watertight by means of a cover ring 16 , and screws 18 . the cover ring secures a cover 20 , which is preferably a flexible membrane molded from , e . g ., silicone , rubber , or a biocompatible elastic . this cover or membrane is in the general shape of opening 22 in the housing . the cover 20 is placed over the opening between the housing 12 and cover ring 16 , which is also in the shape of the opening . the ring 16 is attached to the housing with screws 18 to create a watertight seal around the opening in the housing . if the cover is a membrane , it can flex in or out of the housing as a result of changes in the ambient pressure or pressure within device 10 once it is implanted into a patient . pressure fluctuation within the device may result , e . g ., from the decrease in pressure within the device when the drug composition is released from the device . housing 12 encloses a reservoir for the solid drug composition filament , which in this embodiment is a removable bobbin 24 . filament 14 is wrapped around the bobbin before the bobbin is inserted into the housing . the bobbin is secured in the housing by a bobbin pin 26 . the filament is initially fed from the bobbin , into actuator 30 which includes feeder cylinders 31 , 32 , and gear wheels 34 , 35 . the feeder cylinders direct the filament between two wheels 34 , 35 which contact and pull the filament forwards between them and feed the filament out of the device through a transit assembly ( 36 , 37 , 38 , 40 ). this transit assembly fits into an opening in the housing like a cork in a bottle . the feeder mechanism includes two cylindrical members . the first member 31 is hollowed in a conical fashion at the proximal end , e . g ., the end that filament 14 first enters , to facilitate entry of the filament into the actuator . the distal end of member 31 is hollowed such that the internal diameter is the same as the outer diameter of the second member 32 . other feeder mechanisms can be easily adapted for this device . actuator 30 houses the feeder mechanism and also supports gear wheels 34 , 35 preferably manufactured from stainless steel or plastic . these wheels can also be smooth - surfaced wheels or rollers , e . g ., of rubber or plastic , without gear teeth , as long as they can contact and move the solid drug composition filament from the reservoir through the actuator , and out of the device . the actuator has two openings 42 , 44 . the first opening 42 provides the entrance to the actuator through the proximal end of the first cylindrical member 31 . the second opening 44 is fitted with the transit assembly ( 36 , 37 , 38 , 40 ). the two gear wheels 34 , 35 are positioned between the two openings 42 , 44 , and are arranged to contact filament 14 between them . the wheels rotate in opposite directions such that the filament is moved between them and fed out of the device through the transit assembly . the pressure that the wheels place on the filament is regulated by spring 46 ( shown in dashed lines in fig7 ) which forces the two wheels towards each other . the power supply for the device in this embodiment is an electrical motor 48 powered by a battery 49 , e . g ., a lithium battery that is designed to provide electricity for several years . the motor rotates an axle which engages a small gear 50 which in turn engages one of the two gear wheels 34 , 35 . gear 50 causes wheel 34 to rotate , which in turn causes the second wheel 35 to rotate in the opposite direction . the motor can be an inexpensive one - step watch movement , which includes a motor and a gearbox , and which is usually less than 2 . 5 cm by 5 mm . for example , a circular movement can be 2 . 5 by 0 . 3 cm , and a rectangular motor can be 1 . 8 by 1 . 5 by 0 . 3 cm . in the case of a watch motor , the power can be transmitted to the gear wheels by either the hour or minute hand axles . suitable watch movements include f . e . 6220 and 6230 ( france - ebauches , s . a .) ( size 63 / 4 , 8 ), ronda harvey ( 101 / 2 ), ronda 313 ( 111 / 2 ), and isa 1198 ( 111 / 2 ). other possible motors include continuous current motors , e . g ., maxon dc motor ( 2 . 8 to 12 mm diameter ) or arsape am 15 - 24 or am 10 - 20 motor , or stepper motors , e . g ., arsape single phase stepper motors p130 - s130 or p141 , or mmt two phase stepper motors . preferably , the motor interacts with the actuator through a gear box or a transmission which reduces the rotation speed and / or increases power . other types of motors may be used , e . g ., a spring - powered or shape memory alloy - powered mechanical motor , or an osmotically or electrochemically driven motor , as long as the power can be converted into a force that moves the filament from the bobbin to the transit assembly . the transit assembly includes four members : a guide tube 36 , a support 37 , a screw 38 to connect the guide tube to housing 12 , and a cap 40 which protects the device and must be removed prior to use . the inner diameter of the transit guide tube 36 is only slightly larger then the outer diameter of filament 14 . the inside of guide tube 36 , and preferably the entire housing , is filled with a biocompatible oil to insure that the housing remains watertight . suitable oils include silicon oil , dow corning 344 medical fluid , miglyol 812 dynamit oil , castor oil , isopropyl myristate , ethyl oleate , or injectable olive oil . the oil prevents aqueous liquids , e . g ., bodily fluids , from entering the housing through the transit assembly . in other embodiments , the oil is contained only within a small reservoir in the transit assembly . the delivery profile of the drug , i . e ., the dosage of the drug or drugs delivered by the device over a set period of time , is controlled by a combination of the solid drug composition itself , and a control mechanism 52 arranged within the device . a varied or changing delivery profile is desirable in the treatment of diseases in which the requirement for one or more drugs varies throughout the day . a good example is diabetes , in which a basal dose of insulin must be supplemented by bolus doses , e . g ., at meal times . the delivery profile can be varied in three ways . first , the drug composition filament is precisely manufactured , e . g ., extruded , to contain a specific known amount of drug per unit length of the filament . the amount of drug can be varied along the length of the filament , and various drugs can be mixed within the same segment of filament or included separately in sequential segments of the filament as described above . thus , a precise delivery of drug or drugs can be achieved by dispensing the filament into the body of the patient at a fixed rate , with any desired variation in delivery profile being based solely on the nature of the filament . in such a device , the electrical control mechanism 52 can be very simple , and needs only to turn the motor on and off , and maintain it at a constant speed . in addition , all such mechanisms should include safety features , such as a default &# 34 ; off &# 34 ; position , to avoid accidental dispensing of the drug . second , the delivery profile can be varied by changing the rate at which the filament is dispensed from the device . this can be accomplished by changing the speed at which motor 48 causes wheels 34 , 35 to rotate . for example , the device may be controlled to dispense the filament only during certain hours of the day , or at one rate for certain hours , and at another rate during other hours . in such an embodiment , the electrical control mechanism 52 is more complex , but such controllers and related circuitry are known in the art as described below . third , the delivery profile can also be varied by a combination of variable drug loading in the filament , and variable delivery rate . for example , the rate of delivery can be changed by altering the speed at which the wheels rotate , and the type of drug being dispensed can be altered by the type of filament loaded into the device . the control mechanism 52 preferably includes an integrated circuit or microprocessor and related circuitry which controls the motor and is pre - programmed to the desired delivery profile , or is arranged with a receiver to receive , e . g ., radio , control signals from a programmer device located outside of the patient to allow for alterations in the delivery profile over time . such microchips and microprocessors and related circuitry are known in the art and can be easily adapted to control an electric motor for use in the present devices . examples of such electrical control mechanisms and telemetry systems are described , e . g ., in u . s . pat . nos . 5 , 049 , 141 and 4 , 265 , 241 . the power supply for this controller could be battery 49 , or an additional , separate battery . fig1 and 11 show a cylindrical implantable device designed in much the same way and with essentially the same components as the elongated device of fig6 to 9 . three devices were made following this design . each device was made with a stainless steel or transparent polysulfone ® housing 12 having an external diameter of about 3 cm and a height of 1 . 43 cm , and containing a bobbin 24 having a diameter of about 1 . 8 cm . watch movement f . e . 6230 and watch battery penata 377 ( spain ) were used in these devices . the motor wheel has a diameter of 4 . 4 mm , and the motor runs at 1 hz , delivering about 1 . 1 mm of filament per hour . the housing was filled with dow corning silicon oil 344 to prevent entry of water into the device . in addition , exit tube 36 was made of flexible tygon ™, and was filled with petroleum jelly to ensure that the filament can pass out of the device without allowing water to enter . as a further measure , a hollow stainless steel tube 36 &# 39 ; ( outer diameter of 0 . 5 mm ) was press - fit into the flexible exit tube 36 ( inner diameter 0 . 40 mm ) to form a more precise exit port through which the filament passes . three of these devices were loaded with 25 cm long filaments of hpmc or nylon and implanted intraperitoneally into rats in separate tests . in the first test , the device was removed after 168 hours of operation and had delivered 18 cm of nylon filament . in the second test , the device was removed after 144 hours of operation and had delivered 16 . 5 cm of nylon filament . in the third test , the device was removed after 120 . 5 hours of operation and had delivered 13 . 5 cm of hpmc filament . in each of the three tests , there were no problems associated with the surgical implantation , the housing remained watertight , the mechanism remained operational , and the device was not affected by implantation . these devices can deliver a wide variety of dosages depending on the nature of the solid filament , and the delivery rate . for example , a filament containing 50 % drug , e . g ., somatuline ™, and 50 % carrier , e . g ., hec , with an external diameter of 0 . 28 mm , contains an average of 0 . 25 mg / cm of the drug . thus , at a delivery rate of 1 . 2 mm / hr , a device containing this filament can deliver 0 . 03 mg / hr , or 0 . 7193 mg / day . at a rate of 0 . 4 mm / hr , this dosage can be precisely lowered to 0 . 01 mg / hr , or 0 . 2398 mg / day . fig1 shows a schematic in cross - section of a cylindrical implantable device in which the bobbin is hollow and the motor and electronics are in the center of the bobbin . this allows a more physiological shape , and a constant angle of the filament on the bobbin by fixing a point on the housing for the transit area and unwinding the filament between the housing and the top of the bobbin . in an alternative embodiment , the transit assembly can be designed to merely expose the filament or tape to the bodily fluids , and then to return the composition , now without any drug , to the device for collection on a take - up bobbin or spool . such a device is preferably used in situations in which the carrier material is not to be left in the patient . for example , the transit area can be designed as a compartment or external surface of the housing which is open to the body fluids . preferably , the compartment or surface comprises two openings , one to permit the filament or tape to exit the housing into the bodily fluids , and the second to permit the filament , now without a drug , to return into the housing . the two openings allow the filament to pass without allowing bodily fluids to enter the device . for example , the openings may be sealed with o - rings . fig1 and 14 show side and top ( in partial section ) schematic views of such a device that moves the filament 14 from a first reservoir , e . g ., a dispensing bobbin 24 , out of the device 10 through a first opening a in the housing 12 , along the surface of the housing , and then pulls the filament by means of wheels 34 and 35 through a second opening b back into the housing for collection in a second reservoir , e . g ., a space within the housing ( as shown in fig1 ) or on a pick - up bobbin . in another embodiment , the transit area comprises an opening which is smaller than the drug composition , which for this embodiment is preferably in the form of a flat tape rather than a cylindrical filament , and the composition merely passes by the opening to expose the composition to the external environment , and is then collected on a take - up bobbin . in another embodiment , the device is designed to be permanently implanted into a patient and be easily accessible , e . g ., implanted near the skin to facilitate the reloading of the bobbin with a needle . in this embodiment , a loaded reservoir and a pre - programmed control mechanism can be designed as part of a cartridge that can be easily inserted into a receiving chamber in the housing through a small opening in the skin . thus , the housing , motor , battery , and actuator mechanism all remain implanted within the patient , and only the drug reservoir and the optionally pre - programmed control mechanism are exchanged as required throughout extended therapy regimens . in an alternative embodiment , the battery is also included in the exchangeable cartridge . the solid drug compositions can also be dispensed in separate , single - dose injections from a small , light - weight pen - like filament injector that holds several days or weeks worth of drug dosages . when using this device , the patient is required to change only a needle before each injection , and there is no waste or need to refrigerate the solid drug composition . rather , patients can carry the device with them , only having to refill the device after several days or weeks . these size and storage factors provide substantial improvements over existing pen injectors for liquid drug formulations . in addition , the relatively low cost of the devices allows them to be made disposable . fig1 and 16 show two embodiments of such pen - like injection devices . pen - like device 110 includes a barrel - shaped housing 112 , which can be machined or molded from a suitable heat resistant , rigid material , e . g ., polyvinyl chloride , polycarbonate , teflon ®, polysulfone ® ( amoco ), or stainless steel . the housing may be transparent to facilitate the determination of whether filament 114 is properly moving though the device . the external dimensions of the housing can be about 10 cm in length and 1 cm in diameter . the housing encloses a reservoir for the solid drug composition filament . this reservoir can be , e . g ., an open compartment 124 ( fig1 ) or a removable bobbin 124 &# 39 ; ( fig1 ). typically , filament 114 is wrapped around the bobbin before the bobbin is inserted into the housing . in other embodiments , the bobbin is permanently installed in the housing and is loaded with drug filament . filament 114 is initially fed from the reservoir into an actuator 130 , which includes wheels 134 and 135 , and a manipulator wheel 133 . manipulator wheel 133 allows the user to rotate the wheels which contact and pull the filament from the reservoir and into feed tube 131 which leads to a transit area 137 in which the filament is cut and dispensed out delivery tube 136 . actuator 130 supports the wheels 134 and 135 and the manipulator wheel 133 . the wheels can be gear wheels or smooth - surfaced wheels or rollers , e . g ., of rubber or plastic , as long as they can contact and move the solid drug composition from the reservoir through the actuator and into the transit area . these wheels are attached to the actuator by gear pins and rotation of the wheels can be enhanced by washers , both in a conventional manner . the wheels rotate in opposite directions such that filament 114 is moved between them and towards feed tube 131 . preferably , the spacing between the two wheels is slightly less than the diameter of filament 114 . the wheels are rotated by manipulator wheel 133 , which engages wheel 134 . the manual rotation of manipulator wheel 133 causes wheel 134 to rotate , which in turn causes wheel 135 to rotate in the opposite direction , thereby causing the filament to move between wheels 134 and 135 . the manipulator wheel is preferably manufactured from rubber or plastic with gear teeth which engage gear teeth located on wheel 134 . the manipulator wheel protrudes through housing 112 to allow physical manipulation by the user . the user rotates the manipulator wheel such that the wheels rotate , thereby transporting a specific length of filament to feed tube 131 where it is subsequently cut and injected by microplunger 160 . in another embodiment , manipulator wheel 133 is replaced with a push button that engages the two drive wheels causing them to rotate a specific amount . device 110 also preferably includes a delivery counter 152 , which is connected to actuator 130 . the delivery counter measures the rotation of manipulator wheel 133 . preferably , the counter displays the amount of drug ( e . g ., in iu or mg ) delivered to feed tube 131 . a security control counter 154 is also attached to the actuator . this control displays the amount of drug present in the device at the beginning of each use . as manipulator wheel 133 is rotated , the counter records this information , thus indicating the remaining supply of drug in the reservoir . the security counter can also be designed to limit the maximum delivery of drug in each injection . the plunger mechanism for this device includes an external plunger 162 , microplunger 160 , guide tube 163 , plunger holder 164 , and repositioner 166 . external plunger 162 is preferably manufactured from a suitable rigid material , e . g ., plastic or stainless steel , and is free to move through housing 112 within plunger holder 164 . preferably , external plunger 162 includes a knob ( not shown ) which interacts with plunger holder 164 to prevent the plunger from completely exiting the housing . external plunger 162 includes thumb - rest 168 to easily press the plunger into the housing 112 . microplunger 160 is attached to external plunger 162 , and is preferably manufactured from a suitable rigid material , e . g ., stainless steel or plastic . microplunger 160 moves freely through guide tube 163 and delivery tube 136 . the guide and delivery tubes can be formed from a single tube , or from two separate tubes of equal internal diameter . the external diameter of the microplunger is preferably slightly less than the diameter of delivery and guide tubes , e . g ., about 0 . 5 mm , and preferably 0 . 2 to 0 . 35 mm . external plunger 160 protrudes from housing 112 approximately the combined length of delivery tube 136 and needle 170 . thus , when external plunger 162 is pressed into the housing , microplunger 160 moves into and through delivery tube 136 and needle 170 , and injects a precise length of filament 114 ( 114 &# 39 ; in fig1 b ) into the patient as described in greater detail below . preferably , the plunger system includes a repositioner 166 , e . g ., in the form of a spring . in one embodiment , repositioner 166 is preferably made of a rigid , yet flexible substance , e . g ., stainless steel . the spring should be able to be compressed when external force is applied to the external plunger 162 , and then re - expand when the force is removed . in another embodiment , to ensure complete delivery of drug filament 114 , repositioner 166 is activated only when microplunger 160 has reached the tip of needle 170 . the transit area 137 includes a feed tube 131 , a delivery tube 136 , a cutting mechanism 161 on the end of microplunger 160 opposite plunger 162 , and tip 172 , which encloses a portion of the delivery tube . with reference to fig1 a and 17b , feed tube 131 and guide tube 163 form the two arms of a &# 34 ; y &# 34 ; and delivery tube 136 forms the base of the &# 34 ; y &# 34 ;. all of these tubes are preferably manufactured from suitable rigid material , e . g ., stainless steel . by manually engaging manipulator wheel 133 , the solid drug composition filament 114 is moved from actuator 130 into feed tube 131 and then into delivery tube 136 . by depressing external plunger 162 , cutting mechanism 161 of microplunger 160 moves from guide tube 163 to position x in fig1 a . the cutting mechanism contacts filament 114 at position x , and subsequently cuts the filament at this position . microplunger 160 then proceeds to force the cut portion of the filament 114 &# 39 ; through delivery tube 136 and into needle 170 . fig1 shows an alternative embodiment of transit area 137 , in which delivery tube 136 has a funnel - shaped opening at position x , and feed tube 131 and guide tube 163 are curved . transit area 137 also includes tip 172 that encompasses the part of delivery tube 136 which is outside housing 112 . this tip may be machined or molded as part of the housing , and is preferably conical in shape to allow easy attachment to standard needles , e . g ., shaped like the conical end of a standard syringe . needle 170 is preferably a standard needle which includes a connector 171 . preferably , the internal shape of connector 171 is slightly smaller than the external shape of tip 172 such that needle 170 can be attached to tip 172 by frictional force . in other embodiments , connector 171 includes a locking mechanism allowing the firm connection of the needle to tip 172 , e . g ., a standard luer - lock mechanism . when attached , the receiving end of needle 170 should be directly in line with delivery tube 136 . the inner diameter of needle 170 is preferably the same as the inner diameter of delivery tube 136 , allowing filament portion 114 &# 39 ; easy transit from tube 136 , through needle 170 , and out into the patient . in other embodiments , tip 172 comprises a security mechanism that locks actuator 130 when needle 170 is not attached to the tip . preferably , the security mechanism makes it impossible to either rotate manipulator wheel 133 or depress plunger 162 before the needle is attached . after the connection of needle 170 , the manipulator wheel 133 can be rotated and external plunger 162 is reactivated . once external plunger 162 has been depressed , manipulator wheel 133 cannot be rotated until a new needle 170 has been attached to tip 172 . fig1 shows another embodiment of the pen - like injector device , in which the filament is stored on a bobbin 124 &# 39 ;, rather than loosely in a reservoir compartment . otherwise , the separate parts and their functions are essentially the same as in the embodiment of fig1 , and are given the same reference numerals . a 0 . 3 mm diameter filament was fed into a pen injector having a guide and delivery tube of 0 . 38 mm internal diameter . the device was tested with two different plungers , one with an external diameter of 0 . 3 mm , and the second with a 0 . 35 external diameter . the device was set to cut the filament into lengths of precisely 12 . 0 mm . the table below shows the results of these experiments . table______________________________________0 , 30 mm plunger 0 , 35 mm plungern ° length ( mm ) weight ( mg ) length ( mm ) weight ( mg ) ______________________________________1 11 . 50 0 . 2497 12 . 00 0 . 28252 12 . 00 0 . 2580 12 . 00 0 . 27433 11 . 50 0 . 2550 12 . 00 0 . 27284 12 . 00 0 . 2693 12 . 00 0 . 27475 12 . 00 0 . 2629 12 . 00 0 . 27016 12 . 00 0 . 2604 12 . 50 0 . 2798mean 11 . 83 0 . 2592 12 . 08 0 . 2757sd 0 . 25 0 . 0067 0 . 2041 0 . 0046rsd 2 . 18 % 2 . 59 % 1 . 69 % 1 . 67 % ______________________________________ as shown in the table , the 0 . 35 mm plunger delivered a more accurate dosage , and provides the necessary precision to dispense 12 . 0 ± 0 . 5 mm long segments of filament that provide 0 . 2757 ± 0 . 0068 mg of , e . g ., somatuline ™ in a composition of 50 % somatuline ™ acetate , and 50 % hec , as described above . it is to be understood that while the invention has been described in conjunction with the detailed description thereof , that the foregoing description is intended to illustrate and not limit the scope of the invention , which is defined by the scope of the appended claims . other aspects , advantages , and modifications within the scope of the invention will be apparent to those skilled in the art to which the invention pertains . for example , the micro - mechanical delivery devices can be used to deliver active ingredients other than drugs , and can be used to deliver precise quantities of active ingredients , e . g ., fertilizers , air fresheners , or nutrients for plants or animals , in any environment , e . g ., in air or in a liquid environment , according to an adjustable delivery profile as described above .
the invention features an implantable device for the automatic delivery of an active ingredient according to an adjustable delivery profile . the device includes a housing ; a reservoir operatively connected to the housing and arranged to store a solid composition including the active ingredient ; an actuator arranged within the housing to move the solid composition from the reservoir to a transit area , wherein the solid composition exits the housing at the transit area ; a controller that acts on the actuator to adjust movement of the solid composition out of the housing according to the adjustable delivery profile ; and a power source arranged to provide energy to the actuator and the controller . the solid composition can be an elongate , solid composition comprising a drug , and up to 90 % of a carrier , wherein the composition has a cross - section of less than 0 . 5 mm , and wherein the drug and the carrier are selected and compounded in a proportion such that the drug is immediately released from the carrier upon contact with a liquid .