fig1 is an anterior view illustration of the kidneys and major arteries and veins supporting the kidneys . the right kidney 1 and left kidney 2 are bean - shaped organs , each approximately the size of a tightly clenched fist . they lie on the posterior abdominal wall behind the peritoneum and on either side of the vertebral column while the superior pole of each kidney is protected by the rib cage . a fibrous connective tissue renal capsule 3 surrounds each kidney and around the capsule is a dense deposit of adipose tissue , the renal fat pad ( not shown ), which protects the kidney and supporting vasculature . on the medial side of each kidney is a relatively small area called the helium 4 where the renal artery and the nerves enter and the renal vein and the ureter ( not shown ) exit . the right renal vein 5 and left renal vein 6 branches off the inferior vena cava 7 and enters the renal sinus 8 of each kidney . renal veins are blood vessels that carry deoxygenated blood out of the kidney to the inferior vena cava 7 . fig2 is a posterior view illustration of the kidneys and major arteries and veins supporting the kidneys . the right renal artery 9 and left renal artery 10 branches off the abdominal aorta 11 and enter the renal sinus 8 of each kidney . the renal arteries carry a large portion of total blood flow to the kidneys . up to a third of total cardiac output can pass through the renal arteries to be filtered by the kidneys . fig3 is an illustration of the renal artery 9 including renal nerves . fig3 a is sliced cross - section of the renal artery and fig3 b is a sliced longitudinal section of the renal artery showing the vessel lumen 12 and vessel wall layers . the tunica intima 13 or inner vessel lumen surface layer is a thin membrane that mainly consists of endothelium and lamina propria . the tunica media 14 or middle layer consists of smooth muscle tissue , elastic and collagen fibers . at the outer border of the tunica media an external elastic membrane 15 separates the tunica media from the outer layer , the tunica adventitia 16 . the tunica adventitia 16 is composed of connective tissue , which varies from dense connective tissue that is near the tunica media 14 and contains large amounts of collagen to loose connective tissue that merges with the connective tissue surrounding the blood vessel . the sympathetic nerve innervation of the kidney is achieved through a dense network of postganglionic neurons that innervate the kidney . renal nerves 17 located in the tunica adventitia 16 run in a relatively longitudinal direction alongside the renal artery 9 and enter the hilus 4 of the kidney 1 . fig4 a is a partial longitudinal view of the needle element 18 . the hypodermic needle 19 is a typically rigid or semi - ride longitudinal tubular structure with a proximal end leading into the delivery catheter body ( not shown ) and a sharp pointed distal end 20 to aid with insertion into vessel wall . implant 21 ( shown with phantom lines ) is stored within the needle lumen 22 . proximal end of the needle is mechanically attached to a rigid element 23 within the catheter body and extends the length to the proximal end of the catheter body . a holding rod 24 is disposed within the catheter body and extends the length to the proximal end of the catheter body . hypodermic needle 19 and holding rod 24 can be advanced or retracted by the operator by various means including wires , hand held mechanisms and handles with activation mechanism . in use , catheter body is positioned within targeted vessel lumen 12 and maintained in a fixed positioned by the operator . needle element 18 containing implant 21 is advanced from distal end of catheter and pierced and inserted into the vessel wall while both the hypodermic needle 19 and holding rod 24 are mechanically coupled . once the needle element 18 is in the preferred location in the vessel wall , hypodermic needle 19 and holding rod 24 are decoupled and hypodermic needle 19 withdrawn from vessel wall by pulling the rigid element 23 proximally while holding the catheter body and holding rod 24 in a relatively fixed position ( fig4 b ). this operation ejects the implant 21 without the need for relative motion between the implant 21 and injection site after the operator has positioned the catheter for use . once hypodermic needle 19 if fully withdrawn , needle element 18 is removed from vessel injection site leaving implant 21 in targeted location within vessel wall ( fig4 c ). it may be desirable to control the insertion depth of the needles to accurately target the renal nerves and prevent any undesired damage to deeper tissues . various techniques and mechanisms can be employed to control the insertion depth of the needle into the vessel wall such as adding mechanical stoppers to the hypodermic needle 19 . for example , fig4 d shows a hypodermic needle 19 with a rigid or semi - rigid circular disk 25 mechanically attached at a point proximal from the distal end of hypodermic needle . in use , as the needle element 18 is advanced into the vessel wall , advancement is arrested once the circular disk 25 engages the vessel wall , thus preventing deep penetration of the needle element 18 . depth of penetration of needle element can be 200 microns to several centimeters depending upon needle geometry , vessel wall insertion angle , and targeted tissue location . fig5 a is a partial longitudinal view of the needle element 18 containing multiple implants . implants 21 ( shown with phantom lines ) are stored within the needle lumen 22 . device with this embodiment allows for multiple implants in one injection location or distribution of multiple implants and injection locations of vessel wall using the same needle element 18 . in use , hypodermic needle 19 is withdrawn a fixed distance to detach the first implant 21 but continue to house the remaining implants 21 within the needle lumen 22 as shown in fig5 b - 5 c . insertion and implant ejection is repeated in different locations of the vessel lumen using the same needle element 18 until treatment is complete or the implants 21 are exhausted . one advantage of this embodiment is the requirement of only one catheter to complete treatment on both right and left renal arteries . implant 21 is composed of a solid material , preferably bioactive . after placement into vessel wall , implant creates a tissue response that disrupts and remodels the local tissue containing nerves to suppress or eliminate nerve tissue activity temporarily or permanently . implants can be either non - degradable ( permanent ) or biodegradable ( e . g . absorbable surgical sutures ) which will gradually break down and be absorbed by the body after implantation . any suitable implant material , both organic and inorganic , as well as combinations thereof may be used . the material of the implant may be solid , braided or woven from a single material or a combination of materials . one class of material suitable for this application is sclerosants . a sclerosant is an irritant that elicits local tissue inflammation and subsequent fibrosis ( scar ) to form . sclerosants are currently employed for treatment of various diseases including varicose veins , hemorrhoids , esophageal varices , pleural effusion and morton &# 39 ; s neuroma . the preferred sclerosing implant would have no systemic toxicity and be non - allergenic . it would be effective only above some threshold of bioactivity , so that its effects could be precisely localized . it would be strong enough to sclerose the targeted tissue yet it would produce no local tissue injury if extruded into the vessel lumen 12 . examples of sclerosing materials include laureth 9 ( polidocanol ), morrhuate sodium , sodium tetradecyl sulfate , phenol , quinine , ethanolamine oleate , bleomycin , povidone iodine , tetracycline , doxycycline , sodium chloride ( salt ) and talc . sclerosant can be manufactured in a solid pellet form or be a component of the implant . another class of materials suitable for this application includes neurotoxins . a neurotoxin a substance that damages , destroys , or impairs the functioning of nerve tissue . examples include glutamate , botulinum toxin and tetanus toxin . neurotoxin may be manufactured in a solid pellet form or be a component of the implant . other materials suitable for the implant 21 include polymers that cause a tissue reaction resulting in renal nerve denervation . examples of polymers that elicit an inflammatory response resulting in tissue fibrosis and renal nerve denervation include non - cured and fully cured cyanoacrylate ( 2 - octyl cyanoacrylate ), dacron ™ fibers and meshes ( polyethylene terephthalate ), absorbable surgical suture materials such as polyglycolic acid , polylactic acid , and polydioxanone , non - absorbable surgical suture materials such as nylon , polyester , and polypropylene . additional organic materials sufficient for the implant 21 include surgical suture materials silk , gut ( collagen ) and chromic gut . relatively less tissue responsive polymer materials coated or impregnated with bioactive components that cause renal denervation can also be employed . examples of these materials include porous materials such as sintered high density polyethylene , gortex ™ ( expanded polytetrafluoroethylene ) and porous silicone . any of the aforementioned sclerosants and neurotoxin materials may also be suitable as coatings and impregnations . hydrogels , which are non - expanded solid materials ex - vivo and expand in size in - vivo may also be suitable for this application and include for example poly ( hydroxyethylmathacrylate ), polyacrylamides , n - vinyl - 2 - pyrrolidone , methacrylic acid , methyl methacrylate and maleic anhydride . other materials suitable for the implant 21 include metals that cause a tissue reaction resulting in renal nerve denervation . examples of these include 316l stainless steel , cobalt based alloys ( e . g . mp35n , and elgiloy ) and titanium alloys ( e . g . nitinol ). the implants may have a straight or curved cylindrical type shape . alternatively , they can have the shape adjusted after implantation . they may also have shape memory properties ( such as implants composed of nitinol ) which allows for their shape to assume a predetermined shape after implantation . use of implants made of materials which have shape memory properties permit the implant to assume a preset shape after insertion . alternatively , certain conditions may be applied , such as application of heat , cold , light or a magnetic field that will allow the material to assume a desired fixed or modified shape after implantation . the necessary condition will depend on the intrinsic properties of the shape memory material chosen to produce the implant 21 . implant 21 may be compressed into needle lumen 22 so that after injection , implant expands to its pre - compression dimension or shapes which assists with preventing implant migration and extrusion . edema or tissue swelling from the implant 21 bioactivity as well as the injury to the tissue caused by the needle element 18 vessel wall insertion may also assist with holding implant 21 in position . implant 21 shapes may vary and include spherical , cuboidal and cylindrical . with a cylindrical shape being preferred , length can range from 100 hundred microns to 4 centimeters and radius can range from 10 microns to 5 millimeters . implant 21 may also employ barbs , protrusions , roughened surfaces and / or in - situ shape changes to assist with retention . it may be desirable to examine implant 21 location post insertion to confirm proper placement . in certain aspects , the implant can further include a radio - opaque , echogenic material , or mri responsive material to aid in visualization of the device under ultrasound , fluoroscopy , and / or magnetic resonance imaging . the radio - opaque or mri visible material may be in the form of one or more markers ( e . g . bands of materials that are disposed on either end of the implant ). fig6 is an illustration of the distal end of a delivery catheter assembly containing a single needle element used for renal denervation according to an embodiment of the present invention . in the sliced longitudinal view of fig6 a , a delivery catheter assembly 26 includes an elongated catheter body 27 extending longitudinally between a proximal end ( not shown ) and a distal end 28 . delivery catheter assembly 26 has a longitudinal length of approximately 70 centimeters with a range of 20 - 100 centimeters and outside diameter of approximately 0 . 079 inches ( 6 french catheter gauge ) with a range of 0 . 039 - 0 . 131 inches ( 3 to 10 french catheter gauge ). a needle element 18 containing implants are slidably located in a catheter lumen 29 . fig6 b is a distal end view of the catheter assembly showing the opening 30 of catheter lumen 29 located at twelve o &# 39 ; clock . fig6 c - 6 d illustrate distal advancement of needle element 18 through catheter lumen 29 . upon exit of catheter lumen opening 30 , needle element 18 deflects from longitudinal axis approximately 20 - 70 degrees . needle element 18 deflection may be accomplished by physical deflection of the needle element 18 through the curved channel catheter lumen 29 or needle element 18 may have a preformed curved shape that is constrained in the catheter lumen 29 in a relatively straight configuration and then allowed to form into its preformed curved angle upon exit of lumen opening 30 . in other embodiments not shown , needle elements 18 can also exit from any location on the lateral , circumferential surface of the catheter body 27 . hypodermic needle 19 materials include metals such as stainless steel , shape memory alloys such as nitinol and rigid plastics such as liquid crystal polymers , polyimides and polyetheretherketone . fig6 e - 6 f illustrate proximal retraction of the needle element 18 back into delivery catheter assembly 26 after placement of implant 21 into vessel wall ( not shown ). in the single needle element 18 , delivery catheter embodiment there contains multiple implants 21 within the needle element 18 . in use , delivery catheter assembly 26 is inserted into a blood vessel or the like with needle element 18 fully retracted in catheter body 27 as shown in fig6 a and 6 b . once in position , needle element 18 is advanced out of the catheter body 27 and into the vessel wall where one or more implants 18 are deposited ( fig6 c - 6 d ). needle element 18 is then retracted back into the catheter body 27 ( fig6 e - 6 f ) and the delivery catheter distal end 28 is maneuvered axially and / or longitudinally within the renal vessel lumen 12 for the next implant placement procedure . implant placement and distal catheter 28 maneuvering procedures are repeated until an adequate number of implants 21 are deposited within the vessel wall to create a remodeled zone that captures a full loop of tissue perpendicular to the longitudinal axis of the vessel that results in a circumferential block of nerve impulses and renal denervation . fig7 is an illustration of the distal end of a delivery catheter assembly 26 similar to the delivery catheter assembly 26 of fig6 . they differ primarily in the quantity of needle elements 18 . in fig6 , the needle element exits a single catheter lumen 29 shown at twelve o &# 39 ; clock . as shown in fig7 b , delivery catheter assembly 26 contains four catheter lumen openings 30 , 30 a shown at twelve o &# 39 ; clock , 30 b shown at three o &# 39 ; clock , 30 c shown and six o &# 39 ; clock and 30 d shown at nine o &# 39 ; clock . needle elements 18 are advanced and implants 21 deposited in vessel wall as previously described for delivery catheter assembly 26 of fig7 . needle elements 18 can be advanced concurrently as shown in fig7 c and 7 d or in series ( not shown ). fig7 illustrates one of many ways to incorporate needle elements 18 to a delivery catheter assembly 26 and is not meant to limit the possible needle element 18 configurations and quantities incorporated to said delivery catheter assembly 26 . fig8 is an illustration of a renal artery 9 clinically treated using the delivery catheter assembly 26 of fig7 . in use , the delivery catheter assembly 26 is inserted into the proximal opening 31 of renal artery for treatment . fig8 a is a cross - sectional view and fig8 b is a perspective longitudinal view of the renal artery 9 with four implants 21 deposited within the tunica adventitia 16 or vessel wall . implants 21 are located in proximity to renal nerves 17 which run in a relatively longitudinal direction alongside the renal artery 9 within the tunica adventitia 16 . in one embodiment , delivery catheter assembly 26 of fig7 contains multiple implants 21 in the needle elements 18 as shown in fig5 . needle elements 18 of this embodiment are positioned circumferentially within discrete segments of the catheter body 27 perpendicular to the longitudinal axis of the delivery catheter assembly 26 . after first delivery of implants 21 using this embodiment , catheter distal end 28 is axially rotated approximately 45 degrees and second implant procedure is completed resulting in eight implants 21 placed circumferentially in vessel wall ( fig8 c - 8 d ). alternatively , using the same embodiment , after first delivery of four implants 21 , the delivery catheter distal end 28 is axially rotated approximately 45 degrees , moved longitudinally approximately one centimeter and second implant procedure is completed . resulting in eight implants 21 placed staggered from a longitudinal view ( fig8 f ) but forming a loop circumferentially from a cross - sectional view ( fig8 e ). fig8 g and 8 h illustrate the initiation of a tissue response 32 surrounding the implants 21 . disruption and healing of the tissue continues and eventually leads to a permanent remodeling of the tissue , identified as the remodeled zone 33 in fig8 i . the remodeled zones 33 span several open arc segments around the longitudinal axis , but the zones span a substantially closed loop around the longitudinal axis as illustrated in fig8 i , creating an effective blockage of nerve activity . fig9 is an illustration of the distal end of a delivery catheter assembly 26 similar to the delivery catheter assembly 26 of fig7 . embodiments differ primarily in the spiral shape of the needle elements 18 . needle elements 18 containing implants 21 are slidably located in catheter lumens 29 . fig9 b is a distal end view of the catheter assembly showing the openings 30 of catheter lumen 29 . fig9 c - 9 d illustrate distal advancement of needle elements 18 through catheter lumens 29 . upon exit of catheter lumen openings 30 , needle elements 18 deflects from longitudinal axis to a laterally outward spiral shape . needle elements 18 have a preformed curved shape that is constrained in the catheter lumen in a relatively straight configuration and then allowed to form into its preformed spiral shape upon exit of catheter lumens 29 . hypodermic needle 19 and / or holding rod 24 of needle element 18 may be manufactured with any of the shape memory metals such as nitinol . fig1 is an illustration of a renal artery 9 clinically treated using the delivery catheter assembly 26 of fig9 . similarly to device and method descriptions in fig7 and 8 , fig1 illustrates the implant 21 deposition locations within the tunica adventitia 16 . implant 21 placements lead to remodeled zones 33 that span several open arc segments around the longitudinal axis , but remodeled zones 33 span a substantially closed loop around the longitudinal axis as illustrated in fig1 h , creating an effective blockage of renal nerve activity . fig1 is an illustration of the distal end of a delivery catheter assembly 26 comprising a coil element assembly used for renal denervation according to an embodiment of the present invention . fig1 a is a sliced longitudinal section of the renal artery 9 with vessel lumen 12 , tunica adventitia 16 and renal nerves 17 . placed within the vessel lumen 12 is a delivery catheter assembly 26 which includes an elongated catheter body 27 extending longitudinally between a proximal end ( not shown ) and a distal end 28 . a catheter lumen 29 , as shown in the cross - sectional view of the catheter distal end 28 in fig1 b , houses a coil element assembly 34 in a constrained and collapsed configuration ( coil element assembly not shown in fig1 a and 11 b ). fig1 c illustrates the coil element assembly 34 in an expanded configuration once released from the catheter lumen 29 . coil element assembly 34 has a proximal end connected to the catheter body 27 and a distal end 35 . coil element assembly 34 expansion ceases once significant resistance occurs between coil element assembly 34 and the tunica intima 13 or inner vessel lumen surface . coil element assembly 34 is a hollow hypo - tube with an internal diameter large enough to slidably contain needle elements 18 . needle elements are projected laterally outward through holes in the walls of the coil element assembly 34 into the vessel wall for implant 21 placement ( fig1 e and 11 f ). fig1 is an illustration of the distal end of a delivery catheter assembly 26 comprising a balloon element assembly 36 used for renal denervation according to an embodiment of the present invention . fig1 a is a sliced longitudinal section of the renal artery 9 with delivery catheter assembly 26 placed within the vessel lumen 12 . fig1 b is a distal end view of the delivery catheter assembly 26 . fig1 a and 12 b illustrate a delivery catheter assembly 26 that includes an elongated body 27 extending longitudinally between a proximal end ( not shown ) and a distal end 28 with catheter lumen 29 extending the length of catheter body 27 . housed within the catheter lumen 29 is a deflated and collapsed balloon element assembly 36 ( not shown in fig1 a and 12 b ). balloon element assembly 36 illustrated in fig1 c - 12 h , is similar in design to the balloons manufactured for coronary angioplasty catheters . balloon element 37 has a proximal surface 38 connected to an inflation tube 39 and a distal surface 40 . inflation tube 39 comprises an elongated body extending longitudinally between proximal end ( not shown ) and a distal end within length of catheter lumen 29 . balloon element assembly 36 is movable between a collapsed configuration and an expanded configuration . as shown in fig1 e - 12 h , one possible configuration includes an elongated spherical shaped balloon element 37 when inflated . balloon element may be manufactured with a relatively thin walled compliant or noncompliant plastic . examples of materials used to manufacture the balloon element 37 include polyethylene , polyethylene terephthalate , nylon and silicone elastomers . tubular elements 41 with an elongated body extending longitudinally between a proximal end ( not shown ) and a distal end with an internal diameter large enough to slidably contain needle elements 18 are attached to the proximal balloon surface 38 . balloon element assembly 36 may be inflated and deflated similarly to techniques used for angioplasty , for example by use of a pneumatic indeflator attached to the proximal end of inflation tube 39 . in use , balloon element assembly 36 , is advanced distally out of catheter lumen 29 and placed at targeted treatment site within vessel lumen 12 ( fig1 c ). compliant balloon element assembly 36 is inflated and ceases expansion once significant resistance occurs between balloon element assembly 36 and the tunica intima 13 or inner vessel lumen surface ( fig1 e ). needle elements 18 are projected laterally outward through distal end openings of the tubular elements 41 into the vessel wall for implant placement as described previously . fig1 is an illustration of the distal end of a delivery catheter assembly 26 similar to the delivery catheter assembly 26 of fig1 . embodiments differ primarily in the spiral shape of the balloon element 37 and needle elements 18 . as illustrated in fig1 c , balloon element 37 is a noncompliant balloon that is twisted in its deflated and collapsed configuration and tubular elements 41 slidably containing needle elements 18 are attached to the proximal balloon surface 38 in a non - twisted , straight configuration . as illustrated in fig1 e , balloon element 37 unfurls into an elongated spherical shape upon inflation and expansion . unfurling action of the balloon element 37 causes tubular elements 41 to form into a laterally outward spiral configuration . fig1 g and 38 h illustrate distal advancement of needle elements 18 through tubular elements 41 . upon exit of distal end openings of the tubular elements 41 , needle elements 18 deflects to a laterally outward spiral shape . a similar device to the delivery catheter assembly 26 of fig1 is illustrated in fig1 . balloon assembly element 36 is replaced with a malecot element assembly 42 . malecot element assembly includes a plurality of wings 43 ( four shown in illustration ) which may be oriented generally longitudinally . each wing 43 has a distal end 43 and a proximal end 45 and an intermediate segment 46 . tubular elements 41 with an elongated body extending longitudinally between a proximal end ( not shown ) and a distal end with an internal diameter large enough to slidably contain needle elements 18 are attached to the wing proximal end 45 . malecot element assembly 42 is movable between a collapsed arrangement ( fig1 c and 14 d ) and an expanded arrangement ( fig1 e and 14 f ) with the intermediate segments 46 of the wings 43 in the expanded arrangement moving laterally outward relative to the distal ends 44 and proximal ends 45 of the wings 43 with respect to the collapsed arrangement of fig1 c and 14 d . malecot element assembly 42 can be expanded on collapsed by various means . one example involves manufacturing wings with a memory metallic alloy ( e . g . nitinol ) which have a preformed expanded shape that is constrained in the catheter lumen 29 and then allowed to recover to preformed shape upon exit of the catheter lumen 29 . another example involves mechanical expansion employing pull wire . pull wire ( not shown ) is an elongated body extending longitudinally between a proximal end and a distal end , slidably contained within catheter lumen 29 . distal end of pull wire is attached to distal wing ends 44 and proximal wing ends 45 are fixed to the catheter body 27 . malecot element assembly 42 expansion occurs when pull wire is moved in a proximal and longitudinal direction relative to the catheter body 27 causing proximal wing ends 45 and distal wing ends 44 to move closer together resulting in laterally outward expansion of intermediate wings 46 . in use , the delivery catheter assembly 26 is inserted into a blood vessel in the collapsed arrangement ( fig1 c ). malecot element assembly 42 is expanded and ceases expansion once significant resistance occurs between intermediate wings 46 and the tunica intima 13 or inner vessel lumen surface ( fig1 e ). needle elements 18 are projected laterally outward through distal end openings of the tubular elements 41 into the vessel wall for implant placement ( fig1 g ) as previously described . having described this invention and methods with regards to specific embodiments , it is to be understood that the description is not meant as a limitation since further modifications may suggest themselves or be apparent to those skilled in the art . for example , variations to the above descriptions including the quantity of needle , balloon , coil and malecot assemblies and their relative positioning on the delivery catheter assembly can be easily incorporated . the application is intended to cover all such modifications and variations .
devices and methods that produce alterations of renal sympathetic nerve activity by use of tissue modifying implants . devices for percutaneous delivery of implants into a renal artery or vein wall employing various needle assembly arrangements to modify renal nerve activity .