referring initially to fig1 a , a device 10 for injecting a fluid medicament 13 into a wall 23 of a living blood vessel 11 in accordance with the method of the present invention is shown positioned in an upper body , blood vessel 11 of a patient 12 . it is to be appreciated that the present method can be used in arteries and other vessels throughout the body of the patient 12 . fig1 b shows the wall 23 of an arterial blood vessel 11 having three layers of importance for the present invention , the intima 35 , the media 37 and the adventitia 39 . as shown in fig1 c , the intima 35 surrounds the lumen 21 of the blood vessel 11 . importantly , as provided in detail below , the device 10 when used in accordance with the method provided herein , allows for a substantially circumferential dispersion of the fluid medicament 13 within the wall 23 of the blood vessel 11 , as shown in fig1 c . further , in accordance with the present method , a circumferential dispersion of fluid medicament 13 can be made within one of the layers 35 , 37 , 39 of wall 23 of the blood vessel 11 . referring to fig2 and 3a , a first version of a device 10 suitable for the method of the present invention includes a multi - lumen catheter 14 , an expanding member 15 mounted thereon , a tubular sleeve 18 and a plurality of dispensers 20 . although fig2 and 3a show the expanding member 15 as an inflatable balloon 16 , any expanding member known in the art may be used . the balloon 16 is inflatable and deflatable between a first , substantially deflated configuration and a second , substantially expanded configuration . the balloon 16 , while in the second configuration , can be anywhere from partially inflated to fully inflated depending upon the size of the blood vessel 11 . the balloon 16 and tubular sleeve 18 can be made of a number of materials including polyethylene terephthalate ( pet ). as shown in fig2 , the tubular balloon 16 defines a longitudinal axis 17 . further , fig2 indicates that the tubular sleeve 18 surrounds a substantial portion of the balloon 16 , and that a plurality of dispensers 20 are mounted onto the tubular sleeve 18 . of these , the number of dispensers 20 illustrated is only exemplary . importantly for the present method , all dispensers 20 are positioned in a single plane 19 that , as shown , is oriented substantially normal to the longitudinal axis 17 . also , it is preferable for the present method that the dispensers 20 be equally spaced around the axis 17 . a more complete appreciation of the structural cooperation between the balloon 16 , the tubular sleeve 18 and the dispensers 20 is provided by fig3 a wherein , it will be seen that a distal end 22 of tubular sleeve 18 is attached directly to an outer surface 25 of balloon 16 . by cross - referencing fig2 and 3a it can be seen that the tubular sleeve 18 substantially surrounds and encloses the balloon 16 and that a proximal end 24 of tubular sleeve 18 extends proximally from and beyond the balloon 16 over catheter 14 . the tubular sleeve 18 cooperates with the outer surface 25 of the balloon 16 to define a portion of a fluid passageway 26 . the proximal end 24 can be connected to an outer lumen 27 ( not shown in fig3 a ) of the catheter 14 to complete the fluid passageway 26 . fig3 a further shows that the distal end 28 of balloon 16 is affixed to the catheter 14 , and that the proximal end 30 of the balloon 16 attaches onto the catheter 14 to create an inflation chamber 32 in the interior of the balloon 16 . a balloon port 34 provides fluid access into the inflation chamber 32 . for purposes of the present invention , the balloon port 34 can be connected in fluid communication with a balloon lumen ( not shown ) of the catheter 14 . fig3 a also shows that catheter 14 is formed with an inner lumen 36 which is dimensioned to receive a guidewire 38 therethrough . as discussed previously , the wall 23 of the blood vessel 11 includes multiple layers . to facilitate the present discussion , some of the layers , namely , the intima layer 35 , the media layer 37 , and the adventitia layer 39 are illustrated in fig1 b and again in fig3 b . importantly , when the device 10 is used in accordance with the present method , the depth of penetration of each dispenser 20 can be precisely controlled by controlling the length 41 ( shown in fig5 a ) of each dispenser 20 . in accordance with the method of the present invention , the dispensers 20 extend a length 41 of between approximately 0 . 005 inches and approximately 0 . 02 inches from the tubular sleeve 18 when the balloon 16 is inflated . however , those skilled in the pertinent art will recognize that these distances are merely exemplary . thus , the device 10 is able to deliver the fluid medicament 13 to a desired , target layer in the wall 23 of the blood vessel 11 . for example , as illustrated in fig3 b , the dispenser 20 penetrates through the intima layer 35 and precisely delivers the fluid medicament 13 to the media layer 37 , i . e . the target layer in this example . it is to be appreciated that a shorter dispenser 20 could be utilized to deliver the fluid medicament 13 to the intima layer 35 . additionally , in accordance with the method of the present invention , the device 10 can be used to simultaneously release the fluid medicament 13 within a target layer and dilate the lumen 21 of the blood vessel 11 . referring now to fig4 a , each dispenser 20 includes a base plate 40 and a tubular protrusion 42 having an attachment end 44 and a penetrating section 46 . further , it is seen that the attachment end 44 of the tubular protrusion 42 affixes to and is an integral part of the base plate 40 . preferably , the dispenser 20 is made of nickel and the tubular protrusion 42 is formed by punching out the base plate 40 . in the dispenser embodiment illustrated in fig4 a , the penetrating section 46 is defined by an opening which is opposite the base plate 40 . the tubular protrusion 42 defines a fluid channel 48 which extends through the dispenser 20 . the penetrating section 46 of the dispenser 20 shown in fig4 a is substantially annular shaped . fig4 b shows another embodiment of the dispenser 20 . in this embodiment , each tubular protrusion 42 is substantially conical shaped as shown in fig4 b . like the embodiment shown in fig4 a , the dispenser 20 shown in fig4 b is preferably made of nickel and is formed with a fluid channel 48 which extends through the dispenser 20 . fig5 a , 5 b and 5 c illustrate additional , alternative embodiments of the dispenser 20 . in the embodiments illustrated in fig5 a , 5 b and 5 c , the tubular protrusion 42 is substantially conical shaped . however , in fig5 a , the penetrating section 46 is defined by an opening which extends through the side of the tubular protrusion 42 . somewhat similarly , in fig5 b , the penetrating section 46 is defined by a pair of openings which extend through the side of each tubular protrusion 42 . this feature inhibits plugging of the penetrating section 46 during insertion into the wall 23 of the blood vessel 11 . in fig5 c , the tubular protrusion 42 is made of a porous material . thus , the porous material defines the penetrating section 46 of each dispenser 20 . in the embodiment shown in fig5 c , the fluid medicament 13 is forced through the pores 49 of the porous tubular protrusion 42 . referring now to fig3 a , the dispensers 20 are mounted on the tubular sleeve 18 so that the fluid channel 48 of each respective dispenser 20 is aligned with a hole 52 in the tubular sleeve 18 . this is done to establish fluid communication between the particular dispenser 20 and the fluid passageway 26 . as a practical matter , it may be preferable in the construction of the device 10 to first mount the dispenser 20 on the tubular sleeve 18 , which can be done in any manner well known in the pertinent art , such as by bonding , and then pierce a hole 52 in the tubular sleeve 18 through the dispenser 20 . an alternative structure for a device 10 suitable for use in the present method is shown in fig6 . as shown , the alternative device 10 includes a multi - lumen catheter 14 formed to accommodate a guidewire 38 , a balloon 16 , a plurality of dispensers 20 and a plurality of tubular channels 64 mounted on the outer surface 25 of the balloon 16 . each tubular channel 64 has a smaller diameter than the balloon 16 and is positioned to be substantially parallel with a longitudinal axis 65 of the balloon 16 . fig6 further shows that mounted on the surface of each tubular channel 64 is a dispenser 20 . the dispensers 20 are positioned on the surface of tubular channel 64 so that when balloon 16 is inflated , the dispensers 20 move outwardly from the longitudinal axis 65 in a radial direction . importantly for the present method , all dispensers 20 are positioned in a single plane 67 that is oriented substantially normal to the longitudinal axis 65 of the balloon 16 . further , it is preferable for the present method that the dispensers 20 be equally spaced around the longitudinal axis 65 . referring now to fig7 , the cross - sectional view of the alternative device 10 shows the tubular channel 64 in more detail . more specifically , a distal end 66 of tubular channel 64 is sealed to create a portion of the fluid passageway 26 which connects the dispensers 20 to the fluid source 60 . referring to fig6 and 7 , it is to be appreciated that the proximal end 68 of the tubular channel 64 is in fluid communication with the outer lumen 27 of the catheter 14 . in turn , the outer lumen 27 is connected in fluid communication with the fluid pump 58 and the fluid medicament source 60 . still referring to fig7 , the dispensers 20 are shown mounted on the surface of the tubular channel 64 . as fig7 further shows in detail , a base plate 40 of a dispenser 20 is mounted on the tubular channel 64 over a corresponding hole 70 . from this view , it can be appreciated that any number of tubular channels 64 could be mounted on the external surface of balloon 16 . fig8 shows yet another version of a device 10 suitable for the method of the present invention . in this version of the device 10 , the expanding member 15 includes a multi - lumen catheter 80 and a grommet 82 . both the multi - lumen catheter 80 and the grommet 82 are disposed about the same longitudinal axis 97 with the grommet 82 positioned distally , and separated from , the distal end 88 of the multi - lumen catheter 80 . a mechanism is provided to move the grommet 82 translationally along the longitudinal axis 97 . for example , referring to fig8 , a push - pull wire 84 , is shown connected to the grommet 82 . the push - pull wire 84 extends through one of the lumens of the multi - lumen catheter 80 allowing the push - pull wire 84 to move translationally in line with the longitudinal axis 97 . the translational movement of the push - pull wire 84 causes the grommet 82 to undergo a similar translational displacement . further , this version of the device 10 can be used in combination with the guidewire 38 , as shown in fig8 . specifically , the push - pull wire 84 may be formed with an internal lumen , allowing the catheter 80 and push - pull wire 84 to pass over the guidewire 38 . in the version of the device 10 shown : in fig8 , a plurality of hollow , flexible tubes 86 are attached between the grommet 82 and the multi - lumen catheter 80 . each of the flexible tubes 86 includes a distal end 88 , a proximal end 90 and a central region 92 . the proximal end 90 of each tube 86 is joined to the multi - lumen catheter 80 . the distal end 88 of each tube 86 is joined to the grommet 82 . preferably , the tubes 86 are distributed radially around the multi - lumen catheter 80 and grommet 82 in a manner substantially as shown in fig8 . referring now to fig9 - 11 , it may be seen that each flexible tube 86 is formed with a lumen 94 . the lumen 94 of each flexible tube 86 passes through the multi - lumen catheter 80 allowing fluid medicament 13 to be passed through multi - lumen catheter 80 and into flexible tubes 86 . the lumen 94 of each flexible tube 86 passes separately through multi - lumen catheter 80 allowing a different fluid medicament 13 to be passed into each flexible tube 86 . alternatively , the lumen 94 of each flexible tube 86 may be attached to one or more common lumens within the multi - lumen catheter 80 . referring to fig8 and 9 , it is shown that a dispenser 20 is attached to the central region 92 of each flexible tube 86 . each flexible tube 86 is formed with a hole 96 which correspond to a respective dispenser 20 . functionally , each hole 96 connects the fluid channel 48 of a respective dispenser 20 to lumen 94 allowing the fluid pump 58 to pump fluid medicaments 13 from the fluid source 60 into lumen 94 to be expelled through the dispensers 20 . importantly for the present method , all dispensers 20 are positioned in a single plane 95 oriented normal to the longitudinal axis 97 defined by the expanding member 15 . further , it is preferable for the present method that the dispensers 20 are equally spaced around the longitudinal axis 97 . referring now to fig9 and 10 , it is shown that the device 10 is movable between the first , contracted configuration ( shown in fig9 ) and the second , expanded configuration ( shown in fig1 ). specifically , it may be seen that the grommet 82 and the multi - lumen catheter 80 are distanced by a first separation distance 98 . the device 10 shown in fig9 also has a first overall width designated 100 . in comparison , the grommet 82 and the multi - lumen catheter 80 shown in fig1 are distanced by a second separation distance 102 which is smaller than the first separation distance 98 of fig9 . the device 10 , shown in fig1 also has a second overall width 104 which is greater than the first overall width 100 shown in fig9 . the movement between the first , contracted configuration shown in fig9 and the second , expanded configuration shown in fig1 is accomplished by the translational movement of the grommet 82 along the longitudinal axis 97 . specifically , as the push - pull wire 84 causes the grommet 82 to move towards the multi - lumen catheter 80 , each of the flexible tubes 86 bows outwardly away from the longitudinal axis 97 . in this manner , the push - pull wire 84 may be used to move the grommet 82 translationally to cause the flexible tubes 86 to alternately bow , as seen in fig1 , and straighten , as seen in fig9 . in some cases , it will be preferable to fabricate the flexible tubes 86 from a resilient material and shape the flexible tubes 86 to be initially biased in either a bowed or straight configuration . fig1 a - 12f show the process whereby the fluid medicament 13 is pumped from each dispenser 20 into the intima layer 35 of an exemplary blood vessel 11 and then allowed to disperse . fig1 a - 12f further show that the fluid medicament 13 can be pumped into a target layer , in this case the intima 35 , and allowed to disperse until a circumferential dispersion of fluid medicament 13 is achieved . first , as shown in fig1 a , the dispenser 20 is positioned adjacent to the target area of the blood vessel 11 . next , as shown in fig1 b and 12c , the expanding member 15 is expanded , forcing the dispenser 20 to penetrate the target layer ( in this case , the intima 35 ). preferably , as illustrated in fig1 c , the dispensers 20 are circumferentially spaced to create a plurality of spaced apart medicinal deliveries 106 . fig1 d and 12e show the medicinal deliveries 106 which are confined to the intima layer 35 . fig1 f and 12g show the subsequent dispersion of the fluid medicament 13 around a circumference of the wall 23 of the blood vessel 11 , creating a circumferential dispersion . the pumping rate required to achieve the desired circumferential dispersion depends upon the viscosity of the fluid medicament 13 utilized . typically , between approximately 400 microliters and 700 microliters of the fluid medicament 13 is dispensed during a period of between approximately five and forty - five seconds to create the desired medicinal delivery 106 that will result in a circumferential dispersion . however , it should be recognized that the amounts and time frames provided herein are merely exemplary . it is also to be appreciated that the medicinal dispersion rate will be affected by the body &# 39 ; s response ( inflammation ) to the tissue injury caused by the present method . further , the spacing required to create a plurality of spaced apart medicinal deliveries 106 which subsequently disperse the fluid medicament 13 along the treatment area 54 will also vary according to the fluid medicament 13 utilized . it is contemplated for the present method that the dispensers 20 are to be spaced a circumferential distance 108 of between approximately 1 millimeter and 6 millimeters , roughly 70 degrees and 140 degrees apart . the composition of the fluid medicament 13 to be injected into the wall 23 of the blood vessel 11 depends upon the treatment being performed and the physical characteristics of the patient 12 . more specifically , the fluid medicament 13 can be designed to treat a stenosis or disease de novo , inhibit a restenosis by minimizing the effects of a previous intravascular procedure and / or inhibit a stenosis in a blood vessel 11 . for example , to inhibit a restenosis , the fluid medicament 13 can contain anti - proliferative agents which inhibit the proliferation of smooth muscle cell growth in the vessel in certain pathological conditions . these fluids selectively kill rapidly dividing cells and can be utilized to inhibit the proliferation of smooth tissue growth . suitable fluids can include anti - proliferative agents such as methotrexate , prednisone , adriamycin , mitomycin c , protein synthesis inhibitors , toxin fragments such as pseudomonas , exotoxin ( pe ) or ricin a ( ra ) toxin , and radioactive isotopes 112 such as 111 indium , 90 yttrium , 67 gallium , 99m tc ( technetium 99 ), 205 thallium , and 32 p ( phosphorous 32 ) radiopharmaceutical . it is believed that the present method is uniquely suited to safely deliver toxic fluid medicaments 13 into the wall 23 of the blood vessel 11 while minimizing the amount of fluid medicament 13 which is washed away into the blood stream . alternatively , for example , a fluid medicament 13 which stimulates the production of collateral vessels can be delivered by the present method . these fluid medicaments 13 provide preventative treatment for the patient 12 by creating new collateral vessels in the event the original blood vessel 11 develops a stenosis . a fluid medicament 13 which includes an angiogenis factor can be utilized for this purpose . fig1 a and 13b , illustrate the delivery and dispersion of a fluid medicament 13 that includes a radioactive isotope 112 which can reduce and inhibit tissue and / or cell growth of the wall 23 of the blood vessel 11 . because the radioactive isotopes 112 are injected directly in the wall 23 of the blood vessel 11 and are symmetrically injected around the circumference of the wall 23 of the blood vessel 11 , relatively low energy radioactive isotopes 112 having a relatively short half life can be utilized . these relatively low energy radioactive isotopes 112 should cause minimal trauma to the patient 12 . the present method provided herein is uniquely suited to safely deliver a radioactive isotope 112 to only the treatment area 54 of the wall 23 of the blood vessel 11 , while minimizing the amount of radioactive isotope 112 which is washed away into the blood stream . additionally , the radioactive isotope 112 can be encapsulated within a suitable carrier such as amino - mannose modified liposome , which is rapidly absorbed into the smooth muscle cells of the intima layer 35 . the exact dose of radiation to be delivered to the wall 23 of the blood vessel 11 can be varied to suit the needs of the patient 12 . it is presently believed that a tissue absorbed dose of between approximately 8 - 40 gray will be utilized to inhibit restenosis . the exact amount of fluid medicament 13 and type of fluid medicament 13 injected into the wall 23 of the blood vessel 11 , can be varied to account for fluid medicament 13 washed into the blood stream and / or account for the active life of the fluid medicament 13 . referring to fig1 a and 14b , it is shown that a precipitation process can be used to minimize the amount of fluid medicament 13 which is washed away into the blood stream . specifically , a portion of the fluid medicament 13 can be precipitated at approximately the ph level of the wall 23 of the blood vessel 11 . typically , the vessel ph is approximately 7 . a fluid medicament 13 containing a precipitator 114 , and having a fluid ph level of less than approximately 6 or greater than approximately 8 can be utilized . after the fluid medicament 13 and precipitator 114 are dispensed into the wall 23 of the blood vessel 11 , the fluid medicament ph level will approach 7 , and a portion of the fluid medicament 13 may precipitate . for this embodiment , the fluid medicament 13 could include a precipitator 114 , an active component 115 attached to or incorporated within the precipitator 114 and a carrier component 117 which carries the precipitator 114 and the active component 115 . the active component 115 is the portion of the fluid medicament 13 which is designed to treat the patient 12 . in this example , the precipitator 114 could precipitate in the wall 23 of the blood vessel 11 while the carrier component 117 gets washed away into the blood stream . because the active component 115 is attached to or incorporated within the precipitator 114 , this ensures that the bulk of the active component 115 of the fluid medicament 13 remains in the wall 23 of the blood vessel 11 and minimizes the amount of the active component 115 of the fluid medicament 13 which is washed away into the blood stream . in this embodiment , the active component 115 of the fluid medicament 13 , for example , can include an anti - proliferative agent as outlined above . alternatively , the precipitator 114 and the active component 115 can be a radionuclide or radiopharmaceutical precipitate , such as gold colloidal , i . e . 198 au and 199 au , and / or an inorganic precipitate such as organo - metallic precipitate . additionally , the active component 115 of the fluid medicament 13 can be designed to have a slow , time - release formulation so that active component 115 is released to the wall 23 of the blood vessel 11 over an extended period of time . stated another way , the active component 115 can biodegrade slowly over a period of time to release the active component of fluid medicament 13 into the wall 23 of the blood vessel 11 over an extended period of time . a biodegradable polymer may be used to provide a control release formulation to the active component 115 . alternatively , referring to fig1 a and 15b , the fluid medicament 13 may include a binder 116 , the active component 115 and the carrier component 117 . the binder 116 is secured to the active component 115 of the fluid medicament 13 . the binder 116 is adapted to bind , attach and / or crosslink to at least a portion of the wall 23 of the blood vessel 11 . for example , the binder 116 could include a ligand which binds to a portion of the wall 23 of the blood vessel 11 such as collagen or the smooth muscle cell component of the wall 23 of the blood vessel 11 . because the binder 116 is secured to the active component 115 , this ensures that the bulk of the active component 115 of the fluid medicament 13 remains in the wall 23 of the blood vessel 11 and minimizes the amount of the active component 115 of the fluid medicament 13 which is washed away into the blood stream . examples of ligands capable of binding to the arterial wall components include pdgf receptors , adhesive molecules including , but not limited to certain molecules of the integrin family , and receptors on activated platelets such as thrombin receptors . another suitable type of ligand is sold under the name ceretec ® by amersham located in arlington heights , ill . alternatively , for example , phosphorous tridentate which binds to collagen can be utilized . in yet an alternative embodiment , the binder 116 can have a direct affinity to form ionic bonds , covalent bonds or van der waal attractions with the wall 23 of the blood vessel 11 or some component thereof . alternatively , as illustrated in fig1 a - 16c , the fluid medicament 13 can be used for gene therapy on the wall 23 of the blood vessel 11 . in this embodiment , the fluid medicament 13 can include a suitable viral vector 118 which is adapted to infect a cell 120 and replace , modulate , inhibit or enhance one of the cell genes 122 within the cell 120 . for example , the fluid medicament 13 could include a retroviral , adenoviral vectors or adenovirus associated vectors ( aav ) carrying the appropriate dna payload for appropriate gene switching . alternatively , for example , naked dna or polycation - condensed dna could be utilized for gene therapy . the method of the present invention allows for the use of fluid medicaments 13 which genetically alter the treatment area 54 of the wall 23 of the blood vessel 11 without effecting the rest of the body . still other fluid medicaments 13 which could be utilized with the method of the present invention include antibodies such as receptor site monoclonal antibodies , a toxic agent such as saponin , a genetic material such as dna , a cellular material such as endothelial cells and / or medicaments such as heparin . the examples provided herein are merely examples of fluid medicaments 13 which may be useful with the present invention . those skilled in the art will recognize that additional fluid medicaments 13 will be developed as medical technology improves . additionally , those skilled in the art will recognize that the present invention can be utilized for applications other than inhibiting a restenosis . for example , with extended dispensers 20 , the method of the present invention could deliver fluid medicaments 13 from the blood vessel 11 to specific organs . an example of the operation of the balloon 16 version of the expanding member 15 can best be visualized with initial reference to fig1 - 3 . first , the guidewire 38 is positioned into the blood vessel 11 of the patient 12 . this is done to establish a mechanical pathway through the blood vessel 11 to the treatment area 54 where the fluid medicament 13 is to be released . next , the balloon 16 , which is attached to the catheter 14 , is moved over the guidewire 38 to the treatment area 54 . the balloon 16 is at its first configuration during movement over the guidewire 38 in the blood vessel 11 . once the balloon 16 is properly positioned proximate the treatment area 54 , an inflator 56 is activated to inflate the balloon 16 to its second configuration . as shown in fig2 , the inflator 56 is connected to the proximal ( extracorporeal ) end 29 of the catheter 14 . referring back to fig3 a and 3b , it will be appreciated that , as the balloon 16 is inflated , the expanding balloon 16 urges against the tubular sleeve 18 and causes the tubular sleeve 18 to likewise expand . consequently , the dispensers 20 mounted on the tubular sleeve 18 move radially from the longitudinal axis 17 and embed into the treatment area 54 . further , the balloon 16 can be used to simultaneously dilate the lumen 21 of the blood vessel 11 . with the dispensers 20 embedded into the treatment area 54 , the fluid pump 58 shown in fig2 is activated to pump a fluid medicament 13 from the fluid medicament source 60 into the fluid passageway 26 . importantly , this pumping action also causes any fluid medicament 13 which has already been pumped into the fluid passageway 26 to be expelled through the fluid channels 48 of dispensers 20 and into the tissue of treatment area 54 . alternatively , the fluid pump 58 could be activated prior to embedding the dispensers 20 into the wall 23 of the blood vessel 11 and a valve 62 could be used to prevent the flow of fluid medicament 13 until the dispensers 20 are embedded in the treatment area 54 . the valve 62 can then be opened when the dispensers 20 penetrate into the treatment area 54 so that injection occurs substantially simultaneously with the embedding of the dispensers 20 in the treatment area 54 . alternatively , the injection of the fluid medicament 13 could happen after a time delay by waiting to open the valve 62 for at least about one second to about twenty seconds . further , one or more fluid medicaments 13 can be released at different time intervals in the wall 23 of the blood vessel 11 . after the fluid medicament 13 from the fluid medicament source 60 has been dispensed into the treatment area 54 , the balloon 16 can be deflated to the first configuration by reversing the inflator 56 . this action will cause the balloon 16 to collapse and withdraw the dispensers 20 from the treatment area 54 . the entire device 10 can then be withdrawn from the patient 12 over the guidewire 38 . the embodiment shown in fig6 utilizes a plurality of individual , tubular channels 64 . with this embodiment , it is possible to either maintain fluid communication with , or fluid isolation between , each tubular channel 64 . for example , fluid communication between each tubular channel 64 can be established by fluidly connecting each tubular channel 64 together within one outer lumen 27 of the catheter 14 so that each tubular channel 64 is supplied fluid medicament 13 from the same fluid pump 58 . alternatively , fluid isolation may be maintained between each tubular channel 64 by providing each tubular channel 64 with a corresponding and independent outer lumen 27 and establishing its own fluid connection to a corresponding and independent fluid pump 58 . consequently , it is possible to inject a variety of alternate fluid medicaments 13 simultaneously by using a plurality of tubular channels 64 which are each connected to a separate fluid pump 58 . while the particular method for delivering medication into an arterial wall for prevention of restenosis as herein shown and disclosed in detail is fully capable of obtaining the objects and providing the advantages herein before stated , it is to be understood that it is merely illustrative of the presently preferred embodiments of the invention and that no limitations are intended to the details of the constructions or design herein shown other than as defined in the appended claims . the present invention is not limited to all dispensers being located on a single plane . in some embodiments , a device of the present invention has multiple dispensers that are located at different points along the length of the medical device , such as on different planes . for example , fig1 shows a device 100 that is similar to device 10 of fig2 except that there are multiple dispensers 20 located along the length of tubular sleeve 18 ( e . g ., on multiple planes ). the cross - sectional view of device 100 along line 103 - 103 would appear similar to fig3 a and 3b except that there would be multiple dispensers 20 . for example , fig1 shows a device 110 that is similar to device 10 of fig6 except that there are multiple dispensers 20 located along the length of tubular sleeve 18 ( e . g ., on multiple planes ). the cross - sectional view of device 110 along line 107 - 107 would appear similar to fig7 except that there would be multiple dispensers 20 . for example , fig1 shows a device 120 that is similar to device 10 of fig8 except that there are multiple dispensers 20 located along the length of flexible tubes 86 ( e . g ., on multiple planes ). the cross - sectional view of device 120 along line 109 - 109 would appear similar to fig9 , 10 , and 11 except that there would be multiple dispensers 20 .
a method for preventing a restenosis within a vessel wall requires a medicament be delivered at predetermined locations into the vessel wall and allowed to subsequently disperse in a predetermined pattern . to deliver the medicament , a catheter with an expanding member is advanced into the vasculature of a patient until the expanding member is located as desired . the expanding member is then expanded to force dispensers into the vessel wall to the proper depth . a medicament is then pumped through the dispensers to create a plurality of equally spaced , localized medicinal deliveries which subsequently disperse to medicate an annulus shaped volume within the vessel wall .